M. R. Pinsky · L. Brochard · J. Mancebo · G. Hedenstierna (Eds.) Applied Physiology in Intensive Care Medicine M. R. Pinsky · L. Brochard · J. Mancebo G. hedenstierna (eds.)
Applied Physiology in Intensive Care Medicine second edition
With 155 Figures and 27 Tables
123 MichaeL R. Pinsky, MD LaURenT BRochaRD, MD University of Pittsburgh Medical center hôpital henri Mondor Dept. of critical care Medicine Dept. intensive care Medicine scaife hall 616 51 av. Maréchal Lattre de Tassigny 3550 Terrace Street 94010 créteil cX Pittsburgh, PA 15261 France Usa GÖRAN HEDENSTIERNA, MD JoRDi ManceBo, MD Uppsala University Hospital hospital de sant Pau Dept. clinical Physiology Dept. intensive care Medicine 751 85 Uppsala avda. s. antonio M. claret, 167 sweden 08025 Barcelona Spain
„ The articles in this book appeared in the journal “Intensive Care Medicine betwe en 2002 and February 2009.
ISBN 978-3-642-01768-1 e-ISBN 978-3-642-01769-8 DOI 10.1007/978-3-642-01769-8 Springer Dordrecht Heidelberg London New York
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Springer is part of Springer Science+Business Media (www.springer.com) Introduction
The practice of intensive care medicine is at the very forefront of titration of treatment and monitoring response. The substrate of this care is the critically ill patient who, by definition, is at the limits of his or her physiologic reserve. Such patients need immediate, aggressive but balanced life-altering interventions to minimize the detrimental aspects of acute illness and hasten recovery. Treatment decisions and response to therapy are usually assessed by measures of physiologic function, such as assessed by cardio-respiratory monitoring. however, how one uses such information is often unclear and rarely supported by prospective clinical trials. In reality, the bedside clinician is forced to rely primarily on physiologic principles in determining the best treatments and response to therapy. However, the physiologic foundation present in practicing physicians is uneven and occasionally supported more by habit or prior training than science.
A series of short papers published in intensive care Medicine since 2002 under the heading Physiologic Notes attempts to capture the essence of the physiologic perspectives that underpin both our understanding of disease and response to therapy. This present volume combines the complete list of these Physiologic notes up until February 2009 with the associated review articles over the same interval that also addressed these central issues. This volume was created to address this fundamental unevenness in our understanding of applied physiology and underscore what is known and how measures and monitoring interact with organ system function and response to therapy. This collection of physiologic perspectives and reviews, written by some of the most respected experts in the field, represent an up-to-date and invaluable compendium of practical bedside knowledge essential to the effective delivery of acute care medicine. Although this text can be read from cover to cover, the reader is encouraged to use this text as a reference source reading individual Physiologic Notes and Review articles as they pertain to specific clinical issues. In that way the relevant information will have immediate practical meaning and hopefully become incorporated into routine practice.
We hope that the reader finds these papers and reviews useful in their practice and enjoy reading them as much as we enjoyed editing the original articles that it comprises.
Michael R. Pinsky, MD Laurent Brochard, MD Jordi Mancebo, MD Göran Hedenstierna, MD Contents
Mechanisms of hypoxemia 1. Physiological Notes ...... 41 Robert Rodríguez-Roisin, Josep Roca
1.1 Pulmonary Pulse oximetry ...... 45 Amal Jubran 1.1.1 Respiratory Mechanics Effects of body temperature on blood gases ...... 49 Intrinsic (or auto-) positive end-expiratory pressure Andreas Bacher during controlled mechanical ventilation ...... 3 Laurent Brochard Venous oximetry ...... 53 Frank Bloos, Konrad Reinhart Intrinsic (or auto-) positive end-expiratory pressure Relation between PaO /F O ratio and FO: during spontaneous or assisted ventilation ...... 7 2 I 2 I 2 a mathematical description Laurent Brochard ...... 57 JÉRÔME Aboab, Bruno Louis, Björn Jonson, Laurent Brochard Work of breathing ...... 11 Belen Cabello, Jordi Mancebo Hypoxemia due to increased venous admixture: influence of cardiac output on oxygenation ...... 61 Interpretation of airway pressure waveforms ...... 15 JUKKA TAKALA Evans R. FernÁndez-PÉ rez, Rolf D. Hubmayr 1.2. Cardiovascular: Measurement of respiratory system resistance during mechanical ventilation ...... 17 Pulmonary vascular resistance: A meaningless CLAUDE GUERIN, JEAN-CHRISTOPHE RICHARD variable? ...... 65 Robert Naeije Understanding wasted/ineffective efforts in mechanically ventilated COPD patients Pulmonary artery occlusion pressure ...... 69 using the Campbell diagram ...... 21 Michael R. Pinsky THEODOROS VASSILAKOPOULOS Clinical significance of pulmonary artery occlusion 1.1.2 Gas exchange pressure ...... 73 Michael R. Pinsky Dead space ...... 25 Umberto Lucangelo, luis Blanch Pulmonary capillary pressure ...... 77 Jukka Takala The multiple inert gas elimination Ventricular interdependence: how does it impact technique (MIGET) ...... 29 PETER D. WAGNER on hemodynamic evaluation in clinical practice? . . . 81 François Jardin Alveolar ventilation and pulmonary blood flow: . . Cyclic changes in arterial pressure during the V /Q concept ...... 37 AT mechanical ventilation ...... 85 Enrico Calzia, Peter Radermacher François Jardin VIII Contents
1.3. Metabolism and Renal Function Noninvasive monitoring of peripheral perfusion . . . 169 Alexandre Lima, Jan Bakker Lactic acidosis ...... 89 Daniel De Backer Ultrasonographic examination of the venae cavae . . 181 Antoine Vieillard-Baron, François Jardin Defining renal failure: physiological principles . . . . . 93
Rinaldo Bellomo, John A. Kellum, Passive leg raising ...... 185 Claudio Ronco XAVIER MONNET AND JEAN-LOUIS TEBOUL Hypotension during intermittent hemodialysis: new insights into an old problem ...... 99 2.2. Physiological processes Frédérique Schortgen Sleep in the intensive care unit ...... 191 SAiram Parthasarathy, Martin J. Tobin 1.4. Cerebral Function Magnesium in critical illness: metabolism, Intracranial pressure. Part one: Historical overview assessment, and treatment ...... 201 and basic concepts ...... 105 J. Luis Noronha, George M. Matuschak Peter J. D. Andrews, Giuseppe Citerio Pulmonary endothelium in acute lung injury: Intracranial pressure. Part two: Clinical applications from basic science to the critically ill ...... 215 and technology ...... 109 stylianos E. Orfanos, Irene Mavrommati, Giuseppe Citerio, Peter J. D. Andrews Ioanna Korovesi, Charis Roussos Neuromonitoring in the intensive care unit. Pulmonary and cardiac sequelae of subarachnoid Part one: Intracranial pressure and cerebral haemorrhage: time for active management? . . . . . 229 blood flow monitoring ...... 113 ANUJ BHATIA, ARUN KUMAR GUPTA Carol S. A. Macmillan, Ian S. Grant, Peter J. D. Andrews Neuromonitoring in the intensive care unit. Part two: Cerebral oxygenation monitoring Permissive hypercapnia – role in protective lung and microdialysis ...... 123 ventilatory strategies ...... 241 ANUJ BHATIA, ARUN KUMAR GUPTA John G. Laffey, Donal l O’Croinin, Paul McLoughlin, Brian P. Kavanagh
2. Physiological Reviews Right ventricular function and positive pressure ventilation in clinical practice: from hemodynamic subsets to respirator settings ...... 251 2.1. Measurement techniques François Jardin, Antoine Vieillard-Baron Fluid responsiveness in mechanically ventilated patients: a review of indices used in intensive care . . 133 Acute right ventricular failure – from Karim Bendjelid, Jacques-André Romand pathophysiology to new treatments ...... 261 Alexandre Mebazaa, Peter Karpati, Different techniques to measure intra-abdominal Estelle Renaud, Lars Algotsson pressure (IAP): time for a critical re-appraisal . . . . . 143 Manu L. N. G. Malbrain Red blood cell rheology in sepsis ...... 273 Michael Piagnerelli, Tissue capnometry: does the answer lie Karim Zouaoui-Boudjeltia, under the tongue? ...... 159 Michel Vanhaeverbeek, Jean-Louis Vincent Alexandre Toledo Maciel, Jacques Creteur, Jean-Louis Vincent Contents IX
Stress-hyperglycemia, insulin and Elastic pressure-volume curves in acute lung injury immunomodulation in sepsis ...... 283 and acute respiratory distress syndrome ...... 367 Paul E. Marik, Murugan Ragavanh Björn Jonson
Hypothalamic-pituitary dysfunction in critically The concept of “baby lung” ...... 375 ill patients with traumatic and nontraumatic brain Luciano Gattinoni, Antonio Pesenti injury ...... 293 Ioanna Dimopoulou, Stylianos Tsagarakis The effects of anesthesia and muscle paralysis on the respiratory system ...... 385 Matching total body oxygen consumption and Göran Hedenstierna, Lennart Edmark delivery: a crucial objective? ...... 303 Pierre Squara Diaphragmatic fatigue during sepsis and septic shock ...... 395 Normalizing physiological variables in acute illness: Sophie Lanone, Camille Taillé, five reasons for caution ...... 313 Jorge Boczkowski, Michel Aubier Brian P. Kavanagh, L. Joanne Meyer The use of severity scores in the intensive care . . . . 403 Interpretation of the echocardiographic pressure Jean-Roger Le Gall gradient across a pulmonary artery band in the setting of a univentricular heart ...... 321 Oxygen transport—the oxygen delivery SHANE M. TIBBY, ANDREW DURWARD controversy ...... 409 jean-Louis Vincent, Daniel De Backer Ventilator-induced diaphragm dysfunction: the clinical relevance of animal models ...... 327 Organ dysfunction during sepsis ...... 417 THEODOROS VASSILAKOPOULOS Suveer Singh, Timothy W. Evans Understanding organ dysfunction Ventilator-induced lung injury: from the bench in hemophagocytic lymphohistiocytosis ...... 337 to the bedside CAROLINE CRÉPUT, LIONEL GALICIER, SOPHIE BUYSE ...... 429 Lorraine N. Tremblay, Arthur S. Slutsky ELIE AZOULAY Remembrance of Weaning Past: the Seminal Studies ...... 439 3. Seminal Studies in Intensive Care Martin J. Tobin
Manipulating afterload for the treatment of acute Interactions between respiration and systemic heart failure. A historical summary ...... 351 hemodynamics. Part I: basic concepts ...... 449 CLAUDE PERRET, JEAN-FRANÇOIS ENRICO FRANÇOIS FEIHL , ALAIN F. BROCCARD
Nosocomial pneumonia ...... 355 Interactions between respiration Waldemar G. Johanson, Lisa L. Dever and systemic hemodynamics. Part II: practical implications in critical care . . . .. 459 The introduction of positive endexpiratory FRANÇOIS FEIHL , ALAIN F. BROCCARD pressure into mechanical ventilation: a retrospective ...... 363 Subject Index ...... 467 Konrad J. Falke Contributors
Jérôme Aboab Karim Bendjelid Réanimation Médicale Surgical Intensive Care Division, Hôpital Henri Mondor Geneva University Hospitals Créteil, France 1211 Geneva 14, Switzerland
Lars Algotsson Anuj Bhatia Department of Anaesthesiology– Department of Anaesthesia, Heart-Lung Division Addenbrooke’s Hospital, University Hospital of Lund, Hills Road, CB2 2QQ Cambridge, UK 22185 Lund, Sweden Luis Blanch Peter J. D. Andrews Critical Care Center Department of Anaesthetics, Intensive Hospital de Sabadell Care and Pain Medicine Parc Taulis/n, 08208 Sabadell, Spain University of Edinburgh, Western General Hospital Crewe Road, EH4 2XU Edinburgh, Scotland, UK Frank Bloos Klinik für Anästhesiologie und Intensivtherapie Michel Aubier Klinikum der Friedrich-Schiller-Universität INSERM U 700 and IFR 02, Facult Xavier Bichat Erlanger Allee 101, 07747 Jena, Germany 16 rue Henri Huchard, 75018 Paris, France Jorge Boczkowski Elie Azoulay INSERM U 700 and IFR 02, Facult Xavier Bichat Department of Clinical Immunology, 16 rue Henri Huchard, 75018 Paris, France and Hôpital Saint-Louis, Medical ICU, AP--HP,-
University Paris-7 Diderot, UFR de Médecine, Alain F. Broccard 1 avenue Claude Vellefaux, 75010 Paris, France Medical Intensive Care Unit, Regions Hospital Pulmonary and Critical Care Division, Andreas Bacher Regions Hospital, St Paul, Department of Anesthesiology MN 55101-2595, USA and General Intensive Care Medical University of Vienna, AKH Laurent Brochard Währinger Gürtel 18–20, 1090 Vienna, Austria Réanimation Médicale Hôpital Henri Mondor, Jan Bakker Université Paris 12, INSERM Department of Intensive Care, Erasmus MC U651, 94010 Créteil, France University Medical Center Rotterdam P.O. Box 2040, 3000 CA Sophie Buyse Rotterdam, The Netherlands Department of Clinical Immunology, and Hôpital Saint-Louis, Medical ICU, Rinaldo Bellomo AP--HP, University Paris-7 Diderot, UFR de Médecine, Department of Intensive Care 1 avenue Claude Vellefaux, 75010 Paris, France and Division of Surgery Austin & Repatriation Medical Centre 3084 Heidelberg, Melbourne, Victoria, Australia XII Contributors
Belen Cabello Lennart Edmark hospital santa creu i sant Pau, Department of Anesthesia and Intensive Care servicio de Medicina intensiva Central Hospital av/ sant antoni Maria claret 167, 72335 Vasteras, Sweden cP 08025 Barcelona, spain Jean-François Enrico Enrico Calzia Former Chief of Intensive Care Unit sektion anästhesiologische Pathophysiologie Hôpital des Cadolles, und Verfahrensentwicklung Universitätsklinik Neuchâtel, Switzerland für anästhesiologie, Universität Ulm Parkstrasse 11, 89070 Ulm, Germany Timothy W. Evans Imperial College School of Medicine Giuseppe Citerio Department of Intensive Care Medicine neurorianimazione, Dipartimento Royal Brompton Hospital, London, UK di anestesia e Rianimazione nuovo ospedale san Gerardo Konrad J. Falke Via Donizetti 106, 20052 Monza, italy Klinik für Anaesthesiology und operative Intensivmedizin Berlin Caroline Créput Campus Virchow Klinikum,Charite, Department of Clinical Immunology, Berlin, Germany and Hôpital Saint-Louis, Medical ICU, AP--HP,- University Paris-7 Diderot, UFR de Médecine, François Feihl 1 avenue Claude Vellefaux, 75010 Paris, France Division of Clinical Pathophysiology, University Hospital (CHUV) and Lausanne University (UNIL), Jacques Creteur 1011 Lausanne, Switzerland Department of intensive care, erasme University hospital, Free University of Brussels Evans R. Fernández Pérez Route de Lennik 808, 1070 Brussels, Belgium Mayo Clinic College of Medicine Rochester, Mn 5 5905, Usa Daniel De Backer Department of intensive care, Lionel Galicier Department of Clinical Immunology, erasme University hospital and Hôpital Saint-Louis, Medical ICU, AP--HP,- Free University of Brussels University Paris-7 Diderot, UFR de Médecine, Route de Lennik 808, 1070 Brussels, Belgium 1 avenue Claude Vellefaux, 75010 Paris, France Lisa L. Dever UMDNJ-New Jersey Medical School, Jean-Roger Le Gall VA New Jersey Health Care System Department of Intensive Care Medicine 385 Tremont, East Orange, NJ 07018, USA Saint-Louis University Hospital, Paris, France
Ioanna Dimopoulou Luciano Gattinoni Second Department of Critical Care Medicine, Istituto di Anestesia e Rianimazione Attikon Hospital, Medical School National Fondazione IRCCS Ospedale Maggiore Policlinico and Kapodistrian University of Athens Mangiagalli, Regina Elena di 2 Pesmazoglou Street, 14561 Milano, Università degli Studi Kifissia, Athens, Greece Via Francesco Sforza 35, 20122 Milan, Italy
Andrew Durward Ian S. Grant Evelina Children’s Hospital, Guy’s and Department of Anaesthesia, Saint Thomas’ NHS Trust, University of Edinburgh, Paediatric Intensive Care Unit, Western General Hospital, Edinburgh, SE1 7EH London, UK Scotland, UK Contributors XIII
Claude Guerin John A. Kellum Hôpital de la Croix Rousse and Université de Lyon, Division of critical care Medicine, scaife hall Service de Réanimation Médicale, University of Pittsburgh Medial centre, 103 Grande Rue de la Croix Rousse, Terrace street, Pittsburgh, Pa 15260, Usa 69004 Lyon, France Ioanna Korovesi Arun Kumar Gupta Department of critical care & Pulmonary Department of Anaesthesia, Medicine and “M. simou” Laboratory Addenbrooke’s Hospital, Hills Road, Medical school, University of CB2 2QQ Cambridge, UK athens, evangelismos hospital and 45–47 ipsilandou st., 10675 athens, Greece Neuroscience Critical Care Unit, Addenbrooke’s Hospital, Hills Road, John G. Laffey CB2 2QQ Cambridge, UK Department of anaesthesia, University college hospital Göran Hedenstierna Galway and clinical sciences institute, clinical Physiology, Department of national University of ireland, Galway, ireland Medical sciences, University hospital Sophie Lanone 75185 Uppsala, sweden inseRM U 700 and iFR 02, Facult Xavier Bichat Rolf D. Hubmayr 16 rue henri huchard, 75018 Paris, France Mayo clinic college of Medicine Alexandre Lima Rochester, Mn 5 5905, Usa Department of intensive care, erasmus Mc François Jardin University Medical center Rotterdam hôpital ambroise Paré, P.o. Box 2040, 3000 ca service de Réanimation Médicale, Rotterdam, The netherlands 9 avenue charles de Gaulle, 92104 Boulogne, France Bruno Louis Inserm Unit 651 Waldemar G. Johanson † Department of Medecine Paris 12 UMDnJ-new Jersey Medical school Créteil, France 185 south orange, newark, nJ 07018, Usa Umberto Lucangelo Björn Jonson Department of Perioperative Medicine, Department of clinical Physiology Intensive Care and Emergency, Cattinara University hospital of Lund Hospital, Trieste University School of Medicine 22185 Lund, sweden 34139 Trieste, Italy
Amal Jubran Jordi Mancebo Division of Pulmonary and critical care Medicine Hospital Santa Creu i Sant Pau, edward hines Jr. Veterans affairs hospital Servicio de Medicina Intensiva Route 111 n, hines, iL, 60141, Usa Av/ Sant Antoni Maria Claret 167, CP 08025 Barcelona, Spain Peter Karpati Alexandre Toledo Maciel Department of anaesthesiology and critical care Medicine Department of Intensive Care, hopital Lariboisie`re, 2 Rue ambroise Pare Erasme University Hospital, Free 75475 Paris cedex 10, France University of Brussels Route de Lennik 808, 1070 Brussels, Belgium Brian P. Kavanagh Carol S. A. Macmillan Department of critical care Medicine, University of Dundee, Department of Anaesthesia hospital for sick children Ninewells Hospital, Dundee DD1 9SY, UK 555 University avenue, Toronto, onT, M5G 1X8, canada XIV Contributors
Manu L. N. G. Malbrain Robert Naeije Medical intensive care Unit, Department of Physiology, acZa campus stuivenberg Faculty of Medicine of the Free University Lange Beeldekensstraat 267, B- of Brussels, erasme campus 2060 antwerpen, Belgium 808 Route de Lennik, cP 604, 1070 Brussels, Belgium Paul E. Marik Department of critical care Medicine Luis J. Noronha University of Pittsburgh Medical center Division of Pulmonary, critical care 640a scaife hall, 3550 Terrace and occupational Medicine street, Pittsburgh, Pa, 15261, Usa Departments of internal Medicine and Pharmacological and Physiological science George M. Matuschak school of Medicine Division of Pulmonary, critical care saint Louis University, 3635 Vista ave., and occupational Medicine saint Louis, Mo 63110-0250, Usa Departments of internal Medicine and Pharmacological and Physiological science Donall O’Croinin school of Medicine Department of Physiology, saint Louis University, 3635 Vista ave., University college Dublin saint Louis, Mo 63110-0250, Usa Dublin, ireland
Irene Mavrommati Stylianos E. Orfanos Department of critical care & Pulmonary 2nd Department of Critical Care, Medicine and “M. simou” Laboratory University of Athens Medical Medical school, University of School, Attikon Hospital athens, evangelismos hospital 1, Rimini St., 12462 Haidari (Athens), Greece 45–47 ipsilandou st., 10675 athens, Greece Sairam Parthasarathy Paul McLoughlin Division of Pulmonary and Critical Department of Physiology, Care, Medicine Edward Hines Jr. University college Dublin Veterans Administrative Hospital, Loyola Dublin, ireland University of Chicago Stritch School of Medicine Route 111 N, Hines, IL 60141, USA Alexandre Mebazaa Department of anaesthesiology Michael Piagnerelli and critical care Medicine Department of Intensive Care, hopital Lariboisière, 2 Rue ambroise Pare Erasme University Hospital 75475 Paris cedex 10, France Free University of Brussels 808 route de Lennik, 1070 Brussels, Belgium L. Joanne Meyer Department of Medicine, Claude Perret st. Joseph’s hospital Former Chief of Intensive Care Department Toronto, canada University Hospital of Lausanne, Switzerland Ruelle des Halles 4, CH-1095 Lutry, Switzerland Xavier Monnet Hôpital de Bicêtre, AP-HP, Antonio Pesenti Service de réanimation médicale, Dipartimento di Medicina 78 rue du Général Leclerc, Perioperatoria e Terapia Intensiva 94270 Le Kremlin-Bicêtre, France A.O. Ospedale S.Gerardo and Monza, Università degli Studi Université Paris-Sud, Equipe d’accueil EA 4046, Milan-Bicocca, Italy Faculté de Médecine Paris-Sud, 94270 Le Kremlin-Bicêtre, France Contributors XV
Michael R. Pinsky Jacques-André Romand Department of critical care Medicine surgical intensive care Division, University of Pittsburgh Medical center, Geneva University hospitals 604 scaife, 3550 Terrace street, 1211 Geneva 14, switzerland Pittsburgh, Pa 15261, Usa Claudio Ronco Murugan Raghavan Divisione di nefrologia, ospedale san Bortolo conemaugh Memorial Medical center Via Ridolfi, 36100 Vicenza, italy Johnstown, Pennsylvania, Usa Frédérique Schortgen Peter Radermacher Réanimation Médicale et infectieuse sektion anästhesiologische Pathophysiologie hôpital Bichat-claude Bernard und Verfahrensentwicklung Universitätsklinik 75018 Paris, France für anästhesiologie, Universität Ulm Parkstrasse 11, 89070 Ulm, Germany Suveer Singh chelsea and Westminster hospital Konrad Reinhart Department of intensive care Medicine klinik für anästhesiologie und intensivtherapie 369 Fulham Road, sW10 9nh London, Uk klinikum der Friedrich-schiller-Universität erlanger allee 101, 07747 Jena, Germany Arthur S. Slutsky Queen Wing, st. Michael’s hospital Estelle Renaud 30 Bond st., Toronto, onT, M5B 1W8, canada Department of anaesthesiology and critical care Medicine Pierre Squara hopital Lariboisie`re, 2 Rue ambroise Pare ceRic clinique ambroise Pare 75475 Paris cedex 10, France 27 Boulevard Victor hugo, 92200 neuilly-sur-seine, France Jean-Christophe Richard Hôpital de la Croix Rousse and Université de Lyon, Camille Taillé Service de Réanimation Médicale, INSERM U 700 and IFR 02, Facult Xavier Bichat 103 Grande Rue de la Croix Rousse, 16 rue Henri Huchard, 75018 Paris, France 69004 Lyon, France Jukka Takala Charis Roussos Department of Intensive Care Medicine, University Hospital Bern (Inselspital), Department of critical care & Pulmonary University of Bern, 3010 Bern, Switzerland Medicine and “M. simou” Laboratory Medical school, University of athens, evangelismos hospital Jean-Louis Teboul Hôpital de Bicêtre, AP-HP, 45–47 ipsilandou st., 10675 athens, Greece Service de réanimation médicale, Josep Roca 78 rue du Général Leclerc, servei de Pneumologia, hospital clínic 94270 Le Kremlin-Bicêtre, France institut d’investigaciones Biomédiques and Université Paris-Sud, Equipe d’accueil EA 4046, ausgust Pi i sunyer, Universitat de Barcelona Villarroel 170, 08036 Barcelona, spain Faculté de Médecine Paris-Sud, 94270 Le Kremlin-Bicêtre, France Robert Rodríguez-Roisin servei de Pneumologia, hospital clínic Shane M. Tibby institut d’investigaciones Biomédiques Paediatric Intensive Care Unit, ausgust Pi i sunyer, Universitat de Barcelona Evelina Children’s Hospital, Villarroel 170, 08036 Barcelona, spain Guy’s and Saint Thomas’ NHS Trust, SE1 7EH London, UK XVi Contributors
Martin J. Tobin Antoine Vieillard-Baron Division of Pulmonary and critical care Medicine University hospital ambroise Paré, edward hines Jr. Va hospital, 111n assistance Publique hôpitaux de Paris 5th avenue and Roosevelt Road Medical intensive care Unit hines, illinois 60141, Usa 9 avenue charles de Gaulle, 92104 Boulogne cedex, France Lorraine N. Tremblay Department of surgery Jean-Louis Vincent sunnybrook and Women’s health sciences center Department of intensive care, Toronto, ont., canada erasme University hospital Free University of Brussels Stylianos Tsagarakis Route de Lennik 808, 1070 Brussels, Belgium Department of endocrinology, athens Polyclinic athens, Greece Peter D. Wagner Department of Medicine, Division of Physiology, Michel Vanhaeverbeek University of California, San Diego, 9500 Gilman Drive, experimental Medicine Laboratory, Dept. 0623A, La Jolla CA 92093-0623A, USA andré Vésale hospital Montigny-le-Tilleul, Belgium Karim Zouaoui-Boudjeltia experimental Medicine Laboratory, Theodoros Vassilakopoulos andré Vésale hospital Department of Critical Care and Pulmonary Services, Montigny-le-Tilleul, Belgium University of Athens Medical School, Evangelismos Hospital, 45--47 Ipsilandou Street, 10675 Athens, Greece and Critical Care Department, Evangelismos Hospital, 45--47 Ipsilandou Strasse, 10675 Athens, Greece
Laurent Brochard Intrinsic (or auto-) PEEP during controlled mechanical ventilation
tance times compliance (the reverse of elastance), and Vo is the end-inspiratory volume. In practical terms a time constant is the time required for the lungs to expire 63% of their initial volume. Thus the time needed passively to expire the inspired tidal volume is determined by the two main characteristics of the respiratory system: elastance and resistance. If expiration is interrupted before its nat- ural end, i.e., by occurrence of the next inspiration, end- expiratory lung volume is higher than the so-called re- Introduction laxation volume of the respiratory system, usually re- ferred to as functional residual capacity. As a result the Extrinsic positive end-expiratory pressure (PEEP) ap- alveolar pressure at the end of expiration is higher than plied to the patient at the airway opening is used artifi- zero (zero being the atmospheric pressure), as predicted cially to increase end-expiratory lung volume. Extrinsic by the relationship between lung volume and the elastic PEEP is increased or decreased in small increments in recoil pressure of the respiratory system. This process is ventilator-dependent patients because of its marked ef- called dynamic hyperinflation, and the positive end-expi- fects on cardiorespiratory status. Unintentional or un- ratory alveolar pressure associated with a higher than measured end-expiratory hyperinflation, called intrinsic resting lung volume, is called intrinsic or auto-PEEP. Im- or auto-PEEP, can also occur and have similarly marked portantly for the clinician, this pressure is not directly profound cardiorespiratory effects in ventilator-depen- measured at the airway opening and is thus not shown on dent patients during controlled mechanical ventilation. the pressure dial of the ventilator. What the ventilator Ventilatory settings can interact with the passive process measures is the pressure in the ventilator circuit. Because of expiration and generate intrinsic or auto-PEEP [1, 2]. the direction of the flow is still expiratory, the pressure measured by the ventilator at the end of expiration re- flects only the relationship between flow and the resis- What is intrinsic (or auto-) PEEP? tance of the expiratory line, above the set PEEP. It does not give the clinician any information about the real al- During passive expiration of the lungs the elastic forces veolar pressure. of the respiratory system are the driving forces and can be described by the relationship between lung volume and the elastic recoil pressure of the respiratory system. How one can suspect the presence The lower the elastic forces, or the higher the resistive of intrinsic (or auto-) PEEP forces, the longer will be the time needed to fully expire the inspired tidal volume. In a single-compartment The presence of a positive alveolar pressure higher than model of the lung in which the lung behaves as if it has a the atmospheric pressure or higher than the external single resistance and compliance, the volume at any PEEP set on the ventilator (which is a new “reference given time during expiration (V) is described by the pressure” for the lungs) can be identified by inspection Ðkt monoexponential equation, V=VoÐVe , where k is the of the expiratory flow-time curve. When the expiratory time constant of the equation and is the product of resis- time is sufficient for lung emptying, expiratory flow de-
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 3 DOI: 10.1007/978-3-642-01769-8_1, © Springer-Verlag Berlin Heidelberg 2009 4 L. Brochard
sure in the alveoli minus pressure at the airway opening) on which is based the equation, disappears. In the setting of expiratory flow-limitation, the expiratory time re- quired to minimize intrinsic PEEP is much longer than predicted by the time constant alone. By minimizing in- spired minute ventilation the clinician can minimize in- trinsic (auto-) PEEP.
. Can intrinsic (or auto-) PEEP be reliably measured? Fig. 1 Tracings of flow (V) and airway pressure (Paw) at the air- way opening during volume controlled (VC), pressure-controlled (PC), and pressure-controlled inverse ratio ventilation (PCIRV). In Since the reason for the presence of intrinsic PEEP is the first two situations the expiratory flow declines gradually to flow-dependent pressure gradients from the alveolus to zero; in the third case inspiration is lengthened by the inverse ratio the airway opening, occluding of the expiratory port of setting and expiration shortened; the expiratory flow is abruptly interrupted, indicating the presence of dynamic hyperinflation and the ventilator at the exact end of expiration causes air- intrinsic or auto-PEEP. (From Lessard et al. [3]) way pressure to equilibrate rapidly with alveolar pres- sure and reliably measure the end-expiratory alveolar pressure. This occlusion takes place at the exact time clines from a maximum to zero or to the set PEEP. An where the next inspiration should start and is now avail- interruption in this process results in an abrupt change in able on most modern ventilators (“expiratory hold or the slope of this curve, immediately continued by the pause”). If the patient is fully relaxed, this pressure mea- next inspiratory flow. In other words, the next “inspira- surement reflects the mean alveolar pressure at the end tion” starts during “expiration.” Since the ventilator, of expiration. Most of the time a plateau is reached after which cannot generate flow into the patient’s lungs until less than 1 s, but in the case of inhomogeneous lungs this the pressure at the airway opening exceeds the end-expi- pressure may require a few seconds to also reflect some ratory alveolar pressure, one way in which to measure very slow compartments. This airway occlusion pressure intrinsic or auto-PEEP is to determine the airway pres- may not be homogeneously present in the whole lung but sure at the exact time of inspiratory flow. One can mea- represents an average pressure of all regional levels of sure the intrinsic PEEP level by simultaneously record- end-expiration alveolar pressure. Usually the difference ing airway pressure and flow data using a high-speed between the expiratory pause airway pressure and the set tracing. Figure 1 illustrates how shortening the expirato- external PEEP is called intrinsic or auto-PEEP, while the ry phase generates such dynamic hyperinflation [3]. measured pressure is referred to as total PEEP.
Is the level of intrinsic (or auto-) PEEP predictable? Can the set external PEEP influence the total PEEP in the case of dynamic hyperinflation? If one assumes the respiratory system to be homogene- ous and behave as a single compartment, a monoexpo- A frequent confusion is the belief that external PEEP nential equation can be used. By simple mathematics it could be useful in reducing the level of dynamic hyper- takes three time constants (one being the product of re- inflation because it helps to reduce the value of auto- or sistance and compliance) to expire 96% of the inspired intrinsic PEEP. Obviously this is not the case. The effect tidal volume. Therefore any longer expiratory time mini- of external PEEP is to minimize the difference between mizes or fully avoids incomplete emptying. For instance, the alveolar and the ventilator proximal airway pressure. Ð1 Ð1 a resistance of 10 cmH2O.l .s and a compliance of This difference being called intrinsic or auto-PEEP, ex- Ð1 Ð1 100 ml.cmH2O (0.1 l.cm H2O ) results in a time con- ternal PEEP application results in a decreased intrinsic stant of 1 s. Thus 3 s represents the minimal expiratory or auto-PEEP. The level of dynamic hyperinflation, how- time needed to avoid intrinsic or auto-PEEP. Unfortu- ever, depends on the level of total PEEP and is either not nately, the diseased lungs are not only frequently inho- influenced by external PEEP when external PEEP is less mogeneous, making this calculation overly simplistic, than intrinsic PEEP or is even worsened if external but the presence of small airway collapse during expira- PEEP is set higher than the minimal level of regional in- tion, also referred to as expiratory flow limitation, makes trinsic PEEP. this even more complicated. Because of an abnormal structure of the small airways, when the pressure sur- rounding these conducts becomes higher than the pres- sure inside the airway, these small conducts collapse. The relationship between the “driving pressure” (pres- Intrinsic (or auto-) PEEP during controlled mechanical ventilation 5
References
1. Pepe PE, Marini JJ (1982) Occult posi- 2. Rossi A, Polese G, Brandi G, Conti G 3. Lessard M, Guérot E, Lorino H, Lemaire tive end-expiratory pressure in mechani- (1995) Intrinsic positive end-expiratory F, Brochard L (1994) Effects of pres- cally ventilated patients with airflow ob- pressure (PEEPi). Intensive Care Med sure-controlled with different I:E ratios struction: the auto-PEEP effect. Am Rev 21:522Ð536 versus volume-controlled ventilation on Respir Dis 216:166Ð169 respiratory mechanics, gas exchange, and hemodynamics in patients with adult respiratory distress syndrome. Anesthesiology 80:983Ð991 Laurent Brochard Intrinsic (or auto-) positive end-expiratory pressure during spontaneous or assisted ventilation
To what extent does intrinsic (or auto-) positive end-expiratory pressure influence work of breathing?
For air to enter the lungs, the pressure inside the chest has to be lower than the pressure at the mouth (spontane- ous breathing) or at the airway opening (assisted ventila- tion). In the case of intrinsic (or auto-) PEEP, by defini- tion, the end-expiratory alveolar pressure is higher than the pressure at the airway opening. When the patient ini- tiates the breath, there is an inevitable need to reduce air- way pressure to zero (spontaneous breathing) or to the value of end-expiratory pressure set on the ventilator (as- Introduction sisted ventilation) before any gas can flow into the lungs. For this reason, intrinsic or (auto-) PEEP has been de- scribed as an inspiratory threshold load. In patients with The mechanisms generating intrinsic or auto-positive chronic obstructive pulmonary disease (COPD) this load end-expiratory pressure (PEEP) during controlled me- has sometimes been measured to be the major cause of chanical ventilation in a relaxed patient also occur dur- increased work of breathing [3]. ing spontaneous breathing or when the patient triggers the ventilator during an assisted mode [1, 2]. These in- clude an increased time constant for passive exhalation During assisted ventilation, is the trigger sensitivity of the respiratory system, a short expiratory time result- important to reduce intrinsic (or auto-) positive ing from a relatively high respiratory rate and/or the end-expiratory pressure? presence of expiratory flow limitation. Whereas dynamic hyperinflation and intrinsic or auto-PEEP may have Because the problem of intrinsic or (auto-) PEEP has to haemodynamic consequences, this is not frequently a do with the onset of inspiration, one may reason that in- major concern in spontaneously breathing patients or creasing the inspiratory trigger sensitivity to initiate a during assisted ventilation because the spontaneous in- breath with a lower pressure or flow deflection should spiratory efforts result in a less positive or more negative reduce the work of breathing induced by hyperinflation. mean intrathoracic pressure than during controlled me- These systems are based on the detection of a small pres- chanical ventilation. The main consequence of dynamic sure drop relative to baseline (pressure-triggering hyperinflation during spontaneous and assisted ventila- system) or on the presence of a small inspiratory flow tion is the patient's increased effort to breathe and work (flow-triggering systems). Unfortunately, increasing the of breathing [1, 2]. trigger sensitivity induces only a small reduction in the total work of breathing. The reason for this lack of effect relates to the need for the inspiratory trigger to sense changes in airway pressure or in inspiratory flow. Thus, intrinsic PEEP needs to be counterbalanced first by the
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 7 DOI: 10.1007/978-3-642-01769-8_2, © Springer-Verlag Berlin Heidelberg 2009 8 L. Brochard effort of the inspiratory muscles, in order for this effort to generate a small pressure drop (in the presence of a closed circuit) or to initiate the inspiratory flow (in an open circuit) [4]. The consequence of intrinsic or (auto-) PEEP is that the inspiratory effort starts during expira- tion. This is easily identified by inspection of the expira- tory flow-time curve [1]. As a consequence, it cannot be detected by any of the commercially available trigger systems.
Can the set external positive end-expiratory pressure reduce dynamic hyperinflation and work of breathing?
Responses to these two questions are the same as during controlled mechanical ventilation in a relaxed patient [1]. Their consequences are, however, very different. Ex- ternal PEEP reduces the difference between the alveolar Fig. 1 Tracings of gastric (Pga), oesophageal (Poes) and airway and the ventilator proximal airway pressure, i.e., intrinsic (Paw) pressures, flow and diaphragmatic electromyographic activ- (or auto-) PEEP. The inspiratory threshold load resulting ity (EMGdi) during an assisted breath (pressure-support ventila- from intrinsic (or auto-) PEEP is thus reduced by addi- tion). The vertical lines help to delineate the different phases of tion of external PEEP. Thus, the total work of breathing the inspiratory effort. During phase 1, the flow is still expiratory: is reduced, especially in patients with high levels of in- the start of EMGdi and the abrupt decrease in both Pes and Pga all indicate that the patient performs an active inspiratory effort trinsic (or auto-) PEEP, such as those subjects with against intrinsic positive end-expiratory pressure (PEEP) at the COPD [5, 6]. same time that his/her expiratory muscles relax. Phase 2 is the Although external PEEP reduces work of breathing, it triggering of the ventilator and occurs once intrinsic (or auto-) does not minimise hyperinflation. The level of dynamic PEEP has been counterbalanced hyperinflation is not modified by external PEEP, unless this PEEP is set higher than the minimal level of region- al intrinsic PEEP, and then hyperinflation increases. In- their own inspiratory time [8]. Although some compen- creasing hyperinflation can aggravate the working condi- satory mechanism may exist, it will frequently be insuf- tions of the respiratory muscles by placing them at a me- ficient. Every setting influencing the ventilator inspirato- chanical disadvantage and can result in significant ry time may thus influence the level of dynamic hyperin- haemodynamic compromise by decreasing venous return flation. and increasing right ventricular outflow resistance. Hy- perinflation in excess of intrinsic (or auto-) PEEP occurs usually when the set PEEP is positioned at values above Is intrinsic (or auto-) positive end-expiratory 80% of the mean “static” intrinsic PEEP [7]. For this pressure always synonymous with dynamic reason, titration of external PEEP based on measuring hyperinflation? intrinsic (or auto-) PEEP would be desirable. Unfortu- nately, a reliable measurement of intrinsic (or auto-) In patients with spontaneous respiratory activity, recruit- PEEP in the spontaneously breathing subject is much ment of the expiratory muscles frequently participates in more difficult to obtain than in passive positive-pressure generating intrinsic (or auto-) PEEP independently of ventilation conditions. dynamic hyperinflation. In the case of airflow obstruc- tion, the main consequence of an activation of the expi- ratory muscles is to augment intrathoracic pressure, Can standard ventilatory settings influence intrinsic whereas their effects on expiratory flow may be very (or auto-) positive end-expiratory pressure? modest, especially in the case of airflow limitation, thus promoting small airways to collapse. The activation of During assisted ventilation, the patient is supposed to de- the expiratory muscles results from an increase in respi- termine the respiratory rate freely, and one may suppose ratory drive. Many patients with COPD already have a that he/she will govern his/her respiratory rate to control recruitment of their expiratory muscles at rest. This expi- expiratory time and minimise hyperinflation. Unfortu- ratory muscle recruitment results in a measurable in- nately, most patients will not be able to counteract fully crease in alveolar pressure. However, such expiratory the effects of a ventilator inspiratory time longer than muscle recruitment, although creating an intrinsic (or au- Intrinsic (or auto-) positive end-expiratory pressure during spontaneousas or assisted ventilation 9 to-) PEEP, does not contribute to the inspiratory thresh- sequently subtract the part due to expiratory muscle activ- old load and the increased work of breathing. Indeed, at ity determined from an abdominal pressure signal [9]. the same time that the inspiratory muscles start to de- The reasoning is as follows: any rise in abdominal pres- crease intrathoracic pressure, the expiratory muscles re- sure occurring during expiration is transmitted to the in- lax and their release almost immediately abolishes this trathoracic space and increases alveolar pressure. part of intrinsic (or auto-) PEEP due to the expiratory Intrinsic PEEP is measured from the abrupt drop ob- muscles [9]. This is illustrated in Fig. 1. served on the oesophageal pressure signal until flow be- comes inspiratory (phase 1 on Fig. 1). Part of this drop in oesophageal pressure is caused by the relaxation of the Can intrinsic (or auto-) positive end-expiratory expiratory muscles. This part needs to be subtracted pressure be reliably measured? from the oesophageal pressure drop, in order to evaluate a “corrected” intrinsic PEEP due to hyperinflation. Two The commonly applied end-expiratory airway occlusion main possibilities exist: to subtract the rise in gastric method that measures intrinsic (or auto-) PEEP in pa- pressure that occurred during the preceding expiration tients on controlled ventilation cannot be readily applied [9] or to subtract the concomitant decrease in gastric to the patient making spontaneous inspiratory efforts. For pressure at the onset of the effort [10]. Because the cor- example, it is not possible to determine which amount of rection of intrinsic (or auto-) PEEP for expiratory muscle measured positive airway occlusion pressure, if not all, is activity has not been used in early studies, one can hypo- due to expiratory muscle activity [9]. Setting the external thesise that the magnitude of intrinsic (or auto-) PEEP PEEP based on this measurement could induce consider- has often been overestimated. This combined oesophage- able mistakes by overestimating intrinsic (or auto-) PEEP. al and gastric pressure measuring technique requires the The only readily available and reliable method of measur- insertion of a nasogastric tube equipped with both ing intrinsic (or auto-) PEEP in the spontaneously breath- oesophageal and gastric balloon catheters. This tech- ing subject is to measure the drop in oesophageal pres- nique is often used for research purposes but cannot be sure occurring before flow becomes inspiratory, and sub- easily used at the bedside for routine clinical monitoring.
References
1. Brochard L (2002) Intrinsic (or auto-) 5. Smith TC, Marini JJ (1988) Impact of 8. Younes M, Kun J, Webster K, Roberts PEEP during controlled mechanical PEEP on lung mechanics and work of D (2002) Response of ventilator-de- ventilation. Intensive Care Med breathing in severe airflow obstruction. pendent patients to delayed opening of 28:1376Ð1378 J Appl Physiol 65:1488Ð1499 exhalation valve. Am J Respir Crit 2. Rossi A, Polese G, Brandi G, Conti G 6. Petrof BJ, Legaré M, Goldberg P, Care Med 166:21Ð30 (1995) Intrinsic positive end-expiratory Milic-Emili J, Gottfried SB (1990) 9. Lessard MR, Lofaso F, Brochard L pressure (PEEPi). Intensive Care Med Continuous positive airway pressure (1995) Expiratory muscle activity in- 21:522Ð536 reduces work of breathing and dyspnea creases intrinsic positive end-expirato- 3. Coussa ML, Guérin C, Eissa NT, during weaning from mechanical venti- ry pressure independently of dynamic Corbeil C, Chassé M, Braidy J, lation in severe chronic obstructive hyperinflation in mechanically ventilat- Matar N, Milic-Emili J (1993) Parti- pulmonary disease (COPD). Am Rev ed patients. Am J Respir Crit Care Med tioning of work of breathing in me- Respir Dis 141:281Ð289 151:562Ð569 chanically ventilated COPD patients. 7. Ranieri MV, Giuliani R, Cinnella G, 10. Appendini L, Patessio A, Zanaboni S, J Appl Physiol 75:1711Ð1719 Pesce C, Brienza N, Ippolito E, Carone M, Gukov B, Donner CF, 4. Ranieri VM, Mascia L, Petruzelli V, Pomo V, Fiore T, Gottried S, Brienza A Rossi A (1994) Physiologic effects of Bruno F, Brienza A, Giuliani R (1995) (1993) Physiologic effects of positive positive end-expiratory pressure and Inspiratory effort and measurement of end-expiratory pressure in patients mask pressure support during exacer- dynamic intrinsic PEEP in COPD pa- with chronic obstructive pulmonary bations of chronic obstructive pulmo- tients: effects of ventilator triggering sys- disease during acute ventilatory failure nary disease. Am J Respir Crit Care tems. Intensive Care Med 21:896Ð903 and controlled mechanical ventilation. Med 149:1069Ð1076 Am Rev Respir Dis 147:5Ð13 Belen Cabello Work of breathing Jordi Mancebo
Introduction muscles [4]. In general, the work performed during each respiratory cycle is mathematically expressed as The main goal of mechanical ventilation is to help restore WOB = Pressure × Volume, i.e. the area on a pres- gas exchange and reduce the work of breathing (WOB) sure–volume diagram. Esophageal pressure, which is eas- by assisting respiratory muscle activity. Knowing the de- ily measured, is usually taken as a surrogate for intratho- terminants of WOB is essential for the effective use of racic (pleural) pressure. The dynamic relation between mechanical ventilation and also to assess patient readiness pleural pressure and lung volume during breathing is re- for weaning. The active contraction of the respiratory mus- ferred to as the Campbell diagram [5] (Fig. 1). Esophageal cles causes the thoracic compartment to expand, inducing pressure swings during inspiration are needed to overcome pleural pressure to decrease. This negative pressure gener- two forces: the elastic forces of the lung parenchyma ated by the respiratory pump normally produces lung ex- and chest wall, and the resistive forces generated by the pansion and a decrease in alveolar pressure, causing air to movement of gas through the airways. One can calculate flow into the lung. This driving pressure can be generated these two components (elastic and resistive) by comparing in three ways: entirely by the ventilator, as positive airway the difference between esophageal pressure during the pressure during passive inflation and controlled mechani- patient’s effort during the breath and the pressure value in cal ventilation; entirely by the patient’s respiratory muscles passive conditions, represented by the static volume–pres- during spontaneous unassisted breathing; or as a combina- sure curve of the relaxed chest wall. This passive volume– tion of the two, as in assisted mechanical ventilation. For pressure curve is a crucial component of the Campbell positive-pressure ventilation to reduce WOB, there needs diagram. It is calculated from the values of esophageal to be synchronous and smooth interaction between the ven- pressure obtained over lung volume when the airways are tilator and the respiratory muscles [1, 2, 3]. This note will closed and the muscles are completely relaxed. Unfortu- concentrate on how to calculate the part of WOB gener- nately, as this is difficult to do (because it requires passive ated by the patient’s respiratory muscles, especially during inflation and often muscle paralysis), a theoretical value assisted ventilation. for the slope of this curve is frequently used. However, if a patient is passively ventilated and an esophageal balloon is placed, a true value for the volume–pressure relationship Esophageal pressure and the Campbell diagram of the chest wall during passive tidal breathing can be ob- tained [6]. This passive pressure–volume relationship can Measuring WOB is a useful approach to calculate the be used as a reference value for subsequent calculations total expenditure of energy developed by the respiratory when the patient develops spontaneous inspiratory efforts.
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 11 DOI: 10.1007/978-3-642-01769-8_3, © Springer-Verlag Berlin Heidelberg 2009 12 B. Cabello and J. Mancebo
PEEPi can be quite high in patients with chronic obstructive pulmonary disease (COPD) and may represent a high proportion of the total WOB [9]. For example, a patient who displaces 0.5 l of tidal volume through a7-cmH2O pressure gradient will perform an amount of work of 0.35 J/cycle. If nothing else changes except that this patient develops 5 cmH2O of PEEPi, 0.25 J will be required to counterbalance this, meaning that the total WOB will be 0.60 J (0.35 + 0.25), which represents around 40% of the total work required for the inspiration. The PEEPi value is measured as the drop in esophageal pressure occurring during expiration when the inspiratory muscles start contraction, until the flow reaches the point of zero (see Fig. 1). In the case of ineffective respiratory efforts, that is, Fig. 1 Campbell’s diagram. Work of breathing measured by the muscle contraction without volume displacement, WOB esophageal pressure: resistive WOB (Wresist), elastic WOB (Welast), WOB related to active expiration (WOB expiratory)andWOBre- cannot be measured from the Campbell diagram, since lated to intrinsic PEEP (WPEEPi). Chest wall:thisthick line (the chest this calculation is based on volume displacement. In wall compliance) represents the pleural (esophageal) pressure ob- this situation, measurement of the pressure–time product tained when muscles are totally relaxed and lung volume increases above functional residual capacity, measured in static conditions (PTP) may more accurately reflect the energy expenditure of these muscles. The PTP is the product of the pressure developed by the respiratory muscles multiplied by the time of muscle contraction, expressed in cmH2Oper The WOB is normally expressed in joules. One joule is second. The relevant pressure is again the difference the energy needed to move 1 l of gas through a 10-cmH2O between the measured esophageal pressure and the static pressure gradient. The work per liter of ventilation (J/l) is relaxation curve of the chest wall. the work per cycle divided by the tidal volume (expressed Expiration normally occurs passively. However, the co- in liters). In a healthy subject the normal value is around existence of PEEPi and active expiration is common, espe- 0.35 J/l [7]. Lastly, WOB can be expressed in work per unit cially in COPD patients [10]. Positive expiratory swings of time, multiplying joules per cycle by the respiratory rate in gastric pressure are observed during active expiration as (expressed in breaths per minute) to obtain the power of a consequence of abdominal muscle recruitment. When the breathing (joules/minute). In a healthy subject the normal patient starts contracting the inspiratory muscles, the expi- value is around 2.4 J/min [7]. As illustrated by the Camp- ratory muscles also start to relax. The drop in esophageal bell diagram, two other phenomena affect the WOB: in- pressure used to estimate PEEPi is therefore also due to trinsic PEEP (positive end-expiratory pressure, or PEEPi) the relaxation of the expiratory muscles. To avoid overesti- and active expiration. mating the value of PEEPi, the abdominal pressure swing resulting from the active expiration must thus be subtracted from the initial drop in esophageal pressure [10]. PEEPi and active expiration The distending pressure of the lungs is called the transpul- Technical aspects of WOB calculation monary pressure and it can be estimated as the difference between airway and esophageal (pleural) pressure. At the Two other calculations can be obtained from pressure end of a normal expiration, alveolar and airway pressures and volume measurements: airway pressure WOB and are zero relative to atmosphere, and esophageal pressure transpulmonary pressure WOB. The airway pressure is negative, reflecting the resting transpulmonary pressure WOB displays the energy dissipated by the ventilator (around 5 cmH2O in normal conditions). However, in the to inflate the respiratory system. The transpulmonary presence of PEEPi, the alveolar pressure remains positive pressure WOB shows the energy needed to inflate the lung throughout expiration, because of either dynamic airway parenchyma and reflects the mechanical characteristics collapse or inadequate time to exhale [8]. This implies that of the pulmonary tissue. The limitation of these two some degree of dynamic hyperinflation does exist (lung measurements is that the amount of WOB performed by volume at end-expiration is higher than passive functional the patient’s respiratory muscles is ignored. residual capacity). Importantly, for lung volume to further The main tools used to measure the WOB are a double- increase in a patient with PEEPi, the inspiratory muscles lumen polyethylene gastro-esophageal catheter–balloon contract to an amount equal to PEEPi before any volume system and a pneumotachygraph. The catheter has an is displaced. esophageal and a gastric balloon, usually filled with Work of breathing 13
0.5 and 1 ml of air to measure the esophageal and gas- value. Furthermore, chest wall deformation can occur if tric pressures, respectively. Correct positioning of the levels of ventilation are high [13]. Lastly, it is difficult to esophageal balloon is assessed by an occlusion test: when determine what the optimal WOB level should be for each the airways are closed at the end of expiration and an patient on clinical grounds. active inspiration occurs, a drop in esophageal pressure occurs. In this scenario, there are no changes in lung volume and the decrease in esophageal pressure equals Conclusion the decrease in airway pressure (because in the absence of volume displacement, the transpulmonary pressure From the standpoint of clinical research, the measurement has to be nil) [11]. The catheter–balloon system should of WOB is extremely useful in the field of mechanical ven- be placed to obtain a ratio between airway pressure and tilation, having contributed to important progress in the esophageal pressure changes as close as possible to 1. management of patients for optimizing and understanding Also, the correct positioning of the gastric balloon needs the effects of ventilator settings such as trigger, external to be checked [12]. PEEP, peak inspiratory flow, etc. WOB has also been used to evaluate the physiological effects of a number of agents such as helium and bronchodilators [9, 14, 15, 16, 17, 18, Limitations 19]. Studies on WOB have given us greater insight into the pathophysiology of weaning failure [3] and have also con- The calculation of WOB has several limitations. The tributed to the progress made in the field of non-invasive first is that it requires insertion of a double-balloon mechanical ventilation [20, 21]. Bedside measurements of gastro-esophageal catheter system. The second is the WOB in clinical practice, however, should be reserved for validity of the esophageal pressure value. Since pleural individuals in whom assessment of this parameter can pro- pressure is influenced by gravity, it can be modified by vide further insight into the patient ability to breath and the the weight of the thoracic content and by the posture. In patient–ventilator interactions. the supine position, end-expiratory esophageal pressure is usually positive because of the weight of the heart and mediastinum on the esophagus. However, the amplitude of Acknowledgements. The authors wish to thank Carolyn Newey for her help in editing the manuscript. Belen Cabello is the recipient the changes in esophageal pressure is not usually affected. of a research grant from the Instituto de Salud Carlos III (expedi- The third limitation is that the theoretical value for chest ent CM04/00096, Ministerio de Sanidad) and the Institut de Recerca wall compliance is often used rather than a true measured Hospital de la Santa Creu i Sant Pau.
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14. Jaber S, Fodil R, Carlucci A, Bous- 17. Mancebo J, Albaladejo P, Touchard D, 20. Lellouche F, Maggiore SM, Deye N, sarsar M, Pigeot J, Lemaire F, Harf A, Bak E, Subirana M, Lemaire F, Taille S, Pigeot J, Harf A, Brochard L Lofaso F, Isabey D, Brochard L (2000) Harf A, Brochard L (2000) Airway (2002) Effect of the humidification Noninvasive ventilation with heli- occlusion pressure to titrate positive device on the work of breathing during um–oxygen in acute exacerbations end-expiratory pressure in patients with noninvasive ventilation. Intensive Care of chronic obstructive pulmonary dynamic hyperinflation. Anesthesiology Med 28:1582–1589 disease. Am J Respir Crit Care Med 93:81–90 21. L’Her E, Deye N, Lellouche F, Taille S, 161:1191–1200 18. Cinnella G, Conti G, Lofaso F, Demoule A, Fraticelli A, Mancebo J, 15. Tassaux D, Gainnier M, Battisti A, Jol- Lorino H, Harf A, Lemaire F, Brochard L (2005) Physiologic effects liet P (2005) Helium–oxygen decreases Brochard L (1996) Effects of as- of noninvasive ventilation during acute inspiratory effort and work of breathing sisted ventilation on the work of lung injury. Am J Respir Crit Care Med during pressure support in intubated breathing: volume-controlled versus 172:1112–1118 patients with chronic obstructive pul- pressure-controlled ventilation. Am J monary disease. Intensive Care Med Respir Crit Care Med 153:1025–1033 31:1501–1507 19. Aslanian P, El Atrous S, Isabey D, 16. Mancebo J, Amaro P, Lorino H, Valente E, Corsi D, Harf A, Lemaire F, Lemaire F, Harf A, Brochard L (1991) Brochard L (1998) Effects of flow Effects of albuterol inhalation on the triggering on breathing effort during work of breathing during weaning from partial ventilatory support. Am J Respir mechanical ventilation. Am Rev Respir Crit Care Med 157:135–143 Dis 144:95–100 Evans R. Fernández-Pérez Interpretation of airway pressure waveforms Rolf D. Hubmayr
Abstract Most mechanical ven- is important to appropriately scale tilators display tracings of airway the tracing so that nuances in time pressure (Paw) volume (V)and profiles may be appreciated. In this flow (V˙ ). In volume preset modes, short monograph, we offer three ex- Paw informs about the mechanical amples of how clinicians may use this properties of the respiratory system information for patient assessment and about the activity of respiratory and care. muscles acting on the system. When monitoring ventilator waveforms, it
The Paw waveform Pres must remain constant unless flow resistance changes volume and time. Consequently, the initial step change The interactions between a ventilator and a relaxed in Paw and its decay from Ppeak to Pplat are of similar intubated patient can be modeled as a piston connected magnitude. Fig. 1a demonstrates these features. Since, to a tube (flow-resistive element) and balloon (elastic in pneumatic systems, there are invariable delays in the element). Accordingly, at any instant in time (t), the pressure and flow transients, in practice the step changes pressure at the tube inlet reflects the sum of a resistive in pressure are never as sudden as they are depicted in pressure (Pres) and an elastic pressure (Pel)[1].Pres is Fig. 1a [2]. Nevertheless, the amplitude of transients can determined by the product of tube resistance with V˙ , while be easily estimated by extrapolating the tracing relative to Pel is determined by the product of balloon elastance the slope of the pressure ramp. Finally, while the principles (a measure of balloon stiffness) with volume [1]. In this that govern the interactions between pressure, volume and model, the resistive element reflects the properties of the flow apply to all modes of mechanical ventilation, the intubated airways, while the elastic element reflects those specific pressure waveforms depicted in Fig. 1 refer only of lungs and chest wall. When applied to volume preset to constant flow inflation (square wave) and look very ventilation with constant inspiratory V˙ and a short post- different when other flow profiles (e.g., decelerating, sine inflation pause, the resulting Paw tracing has three distinct wave) are used. Our use of square wave profiles in Fig. 1 components: (1) an initial step change proportional to should not be interpreted as an endorsement of a specific Pres; (2) a ramp that reflects the increase in Pel as the mode, but rather as the most convenient means to present lungs fill to their end-inflation volume; and (3) a sudden this information. decay from a pressure maximum (Ppeak) to a plateau The tracing in Fig. 1b differs in several important re- (Pplat) that reflects the elastic recoil (Pel)oftherelaxed spects: the Paw ramp is steeper and it is nonlinear with re- respiratory system at the volume at end-inflation. Since in spect to time. Since V˙ is constant the nonlinearity between this example flow is held constant throughout inflation, Paw and t means that the relationship between Paw and V
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 15 DOI: 10.1007/978-3-642-01769-8_4, © Springer-Verlag Berlin Heidelberg 2009 16 E.R. Fernández-Pérez and R.D. Hubmayr
ceeding their capacity. At the bedside, such an observation should raise concern for injurious ventilator settings [2]. The tracing in Fig. 1c is characterized by a larger- than-expected initial step change in Paw that exceeds the peak-to-plateau pressure difference. In an otherwise relaxed patient, such an observation should raise suspicion for dynamic hyperinflation and inadvertent PEEP (PEEPi). If Pel at end-expiration is greater than Paw at that time (i.e., PEEPi is present), then gas will flow in the expiratory direction. The step change in Paw during the subsequent inflation will therefore not only reflect Pres but also PEEPi that must be overcome to reverse flow at the tube en- trance [1]. Tracings like the one in Fig. 1c should therefore Fig. 1 Schematic illustration of the Paw profile with time during alert the clinician to the presence of dynamic hyperinfla- constant-flow, volume-cycle ventilation. a Passive respiratory sys- tion and provide an estimate of the extrinsic PEEP neces- tem with normal elastance and resistance. Work to overcome the sary to minimize the associated work of breathing. PEEPi resistive forces is represented by the black shaded area,andthe gray shaded area represents the work to overcome the elastic forces. is invariably associated with a sudden transient in expi- b Up-sloping of the Paw tracing representing increased respiratory ratory flow prior to ventilator-assisted lung inflation [3]. system elastance. c Paw tracing in the presence of inadvertent PEEP. However, this flow transient need not be associated with d scalloping of the Paw tracing generated by a large patient effort dynamic hyperinflation, because it is also seen in patients (Paw airway pressure, Pel elastic pressure, Ppeak pressure maxi- with increased respiratory effort and active expiration. mum, Pplat pressure plateau, PEEPi inadvertent PEEP, Pres resis- tive pressure) The tracing in Fig. 1d represents a significant departure from relaxation patters. There is no initial step change in Paw; the ramp is nonlinear, and the end-inspiratory pres- sure plateau is lower than expected. This tracing suggests must be nonlinear as well. Assuming identical ventilator that the inspiratory muscles are active throughout machine settings as in Fig. 1a the increased steepness of the ramp inflation and that their work represents a considerable frac- and its convexity to the time axis indicates a stiffening of tion of the work performed on the respiratory system. This the respiratory system with volume and time and suggests pattern should alert clinicians to the presence of a poten- that the lungs may be overinflated to volumes near or ex- tially fatiguing load.
References 1. de Chazal I, Hubmayr RD (2003) Novel 2. Grasso S, Terragni P, Mascia L, Fa- 3. Brochard L (2002) Intrinsic (or auto-) aspects of pulmonary mechanics in nelli V, Quintel M, Herrmann P, Heden- PEEP during controlled mechani- intensive care. Br J Anaesth 91: 81–91 stierna G, Slutsky AS, Ranieri VM cal ventilation. Intensive Care Med. (2004) Airway pressure-time curve 28:1376–1378 profile (stress index) detects tidal recruitment/hyperinflation in experi- mental acute lung injury. Crit Care Med 32:1018–1027 Claude Guerin Measurement of respiratory system resistance Jean-Christophe Richard during mechanical ventilation
Abstract Background: The measure- Conclusions: Although this method ment of respiratory system resistance assumes a homogeneous respiratory during mechanical ventilation is system, it has proven useful clinically important to ascertain the causes of to separate flow-dependence issues increase in airway pressure during such as bronchospasm or endotra- volume-controlled ventilation, which cheal tube obstruction from stiff may include airways resistance and lungs (acute lung injury) or decrease decreased respiratory system com- chest wall (abdominal distension) pliance. Discussion: Separation compliance. of total resistance from compli- ance of the respiratory system can Keywords Airway pressure · Mechan- be assessed by the end-inspiratory ical ventilation · Respiratory system hold maneuver that separates peak compliance · Respiratory system pressure from plateau pressure. resistance
Introduction be described by the equation of motion that reflects the sum of resistive (Pres) and elastic (Pel) forces at that Change in the resistance of the respiratory system to moment: gas flow (Rrs) commonly occurs in critically ill patients Paw(t) = PEEPt + Pres(t) + Pel(t) (1) and is manifest in mechanically ventilated patients on = PEEPt + V (t) × R + V(t) × E volume-controlled ventilation as an increase in airway pressure (Paw). Increases in Paw commonly occur with where V is inflation flow, R and E resistance and elastance many processes and can profoundly alter gas exchange of the respiratory system. Although Eq. 1 depicts the be- and cardiovascular function. Inspiratory gas flowing from havior of the respiratory system as a single-compartment the ventilator must overcome two primary components of model (Fig. 1a), this approach tends to describe respira- Rrs before it can distend the alveoli. These include airway tory function under most conditions. However, the model resistive forces needed to cause airflow associated with the described in Eq. 1 also assumes both R and E are constant endotracheal tube (ETT) and airways and elastic forces as V and V change, which is incorrect. For example, needed to distend the tissues associated with baseline airway resistance (Raw) decreases with increasing V [2]. positive end-expiratory pressure (PEEPt) and tidal volume More refined models have therefore been described (V) as they interact with the combined lung and chest (Fig. 1b) [3, 4]. In particular, such complex models are wall tissue elastance. In patients receiving noninvasive needed to take into account the V dependence of Rrs [5]. mechanical ventilation the upper airways are an important, An immediate practical implication of this is that any but difficult to assess [1] contributing factor to Rrs. At value of Rrs must be referred to the levels of V set on the any given time t during mechanical inflation Paw can ventilator.
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 17 DOI: 10.1007/978-3-642-01769-8_5, © Springer-Verlag Berlin Heidelberg 2009 18 C. Guerin and J.-C. Richard
sum of Rint, rs and ∆Rrs. Rint, rs mainly reflects airway resistance [8] and ∆Rrs dynamic pressure dissipation due to tissue viscoelastic properties in normal lung [4] and time-constant inequality in diseased lungs [9, 10]. The technique is easy to do by instructing the ventilator to perform an inspiratory hold maneuver of 3 s [11]. This diagnostic technique is often an automated function on many ventilators. The accuracy of the results requires patients to not be actively participating in inspiratory efforts and thus works best in those patients in synchrony with the ventilator, including those deeply sedated and/or paralyzed. The second method of assessing Rrs is based on the forced oscillation technique introduced 50 years ago [12]. This method determines the respiratory input imped- ance (Z), which is the response of the respiratory system to an external oscillatory stimulus at various respiratory Fig. 1 a Single-compartment model of respiratory system with frequencies usually between 0.5 and 20 Hz. Z is computed a standard resistance (dashpot R) and elastance (spring E). b Mul- as the ratio of the Fourier transform of Paw to the Fourier tiple-compartment model of respiratory system comprising the stan- transform of V . The resultant Z has two components, dard resistance (dashpot Rint) and the standard elastance (spring E), a “real” part that is related to Rrs and an imaginary both arranged serially, and the viscoelastic units which are arranged in parallel around E. The viscoelastic units comprise a dashpot and part, or reactance, which is related to elastance. This a spring that are arranged serially. c Interrupter technique during method can be used in patients receiving invasive [13] mechanical ventilation with constant flow inflation. From top to bot- or noninvasive mechanical ventilation [14] but requires tom, schematic drawing of airway pressure (Paw), flow and change additional equipment. Accordingly, it is not routinely used in lung volume against time. At the end of a baseline breath the airways are occluded for 5 s (second horizontal double arrow). After in most ICUs to assess Rrs even though it is accurate. occlusion the sudden pressure drop from maximal pressure (Pmax) to pressure at first zero flow (P1) is the pure resistive pressure drop (Pres). The slow decay from P1 to the plateau pressure (Pplat)isthe pressure dissipation into the viscoelastic units. The elastic pressure Airway and endotracheal tube resistance (Pel) is above the static elastic end-expiratory pressure (PEEPt) obtained from end-expiratory occlusion (first horizontal double In normal subjects under mechanical ventilation Rint, rs –1 –1 –1 arrow) amounts to 2.2 cmH2Ol s at V of 0.6 l s , whereas greater values have been measured in various diseased con- ditions [9, 10, 15, 16]. Rint, rs is V dependent, linearly in- creasing with V for a constant V, in both normals [4] and Techniques of measurement of Rrs in patients with lung disease [9, 10]. In the mechanically ventilated patient Paw is usually measured at the proxi- Although more complex methods exist, a simple bedside mal tip of the ETT. Thus the measured Rint, rs reflects approach to measuring Rrs and its components appears both Raw and ETT resistance. The pressure drop across to also be accurate. The first method is based on the the ETT depends highly on V and ETT size such that the rapid interruption of V at the airways while measuring higher the V and smaller the ETT size, the higher is ETT Paw downstream the location of occlusion as described flow resistance. This relationship can be described by the 80 years ago [6] and validated in mechanically ventilated model proposed by Rohrer [17] as: patients 40 years ago [7]. The occlusion is performed at end-inflation during constant V and V conditions. One Pres = K1 V’ + K2 V’2 (2) observes the resultant Paw behavior. This end-inspiratory hold maneuver results in the Paw rapidly decreasing from where K1 and K2 are constants. Although the physio- a peak Paw, called Pmax, at end-inspiration to P1 (Fig. 1c) logical meaning of K1 and K2 is not clear, the presence and then by a slow decay from P1 to plateau pressure of K2 underlines the nonlinear V dependence of Pres. (Pplat), as end-inspiratory lung volume is held constant. This nonlinear Pres-V relationship has been described Pplat represents the static elastic end-inspiratory recoil with other models based on the physical characteristics pressure of the respiratory system (Pel, st). By dividing of the conducts and of the gas (Reynolds number, Blasius (Pmax-P1) by the V immediately preceding the occlu- equation). Although beyond the scope of this note, it is sion, the interrupter resistance (Rint, rs) can be computed. important to bear in mind that V can change from laminar By dividing (P1-Pplat) by the same V the additional to fully turbulent, explaining this nonlinearity in the viscoelastic resistance (∆Rrs) can be obtained. Rrs is the Pres-V relationship. This has important consequences Measurement of respiratory system resistance during mechanical ventilation 19 for V delivery during inhaled therapy or justifies to component the dominate factor in increasing ∆Rrs [19]. change the nature of the gas such as helium in case of ∆Rrs also exhibits V dependence in both normals [4] highly turbulent conditions. Equation 2 is used in many and patients [9, 10]. However, unlike Rint, rs, ∆Rrs ventilators as an “automatic tube compensation mode” decreases progressively with increasing V [2]. Thus Rrs (ATC) during pressure support breathing to compensate depends on the respective contributions of Rint, rs and for the resulting additional work of breathing due to the ∆Rrs. From the clinical perspective Rrs is maximal at low ETT [18]. ATC may also use equation as Pres = V b where V and decreases with increasing V to a minimal value b, which depends on the size of the ETT tube, is usually that occurs at V of about 1 l s–1 in both COPD [10] and slightly lower than 2. ARDS [9, 20] patients.
Tissue resistance Clinical Implications The tissue resistance ∆Rrs is equal to or slightly greater Assessing Rrs during mechanical ventilation is important than Rint, rs. Tissue resistance has two components, lung in order to: (a) attribute to increased Rrs an increase in parenchyma and chest wall, which includes the diaphragm. Paw during volume-controlled mode or a decline in tidal In patients with chronic obstructive lung disease (COPD) volume during pressure-controlled mode, (b) identify the the contribution of chest wall to Rrs is modest [10], mechanism of increased Rrs as an increase in resistance whereas in patients with the acute respiratory distress of ETT or Raw or tissue resistance, (c) assess the effects syndrome (ARDS) the lung and chest wall contribution of bronchodilating agents, and (d) detect ETT obstruction. to ∆Rrs is highly variable and depends to a great degree Rrs can easily be measured with the interrupter technique on whether lung injury is the primary cause of ARDS in patients receiving invasive mechanical ventilation in (primary) or secondary. In secondary ARDS abdomi- ICU from the values of Pmax, Pplat, and V provided by nal distension often increases intra-abdominal pressure the ventilator. Clinicians must have in mind the V depen- limiting chest wall expansion making the chest wall dence of the values of Rrs when interpreting the results.
References 1. Jounieaux V, Aubert G, Dury M, Del- 6. Neegaard KV, Wirtz K (1927) Die 11. Barberis L, Manno E, Guerin C (2003) guste P, Rodenstein D (1995) Effects of Messung der Strömungswiderstände in Effect of end-inspiratory pause duration nasal positive-pressure hyperventilation den Atemwegen des Menschen, ins- on plateau pressure in mechanically on the glottis in normal awake subjects. besondere bei Asthma und Emphysem. ventilated patients. Intensive Care Med J Appl Physiol 79:176–185 Z Klin Med 105:51–82 29:130–134 2. Bates JH, Baconnier P, Milic-Emili J 7. Don HF, Robson JG (1965) The me- 12. DuBois AB, Brody AW, Lewis DH, (1988) A theoretical analysis of in- chanics of the respiratory system during Burgess BF (1956) Oscillation mechan- terrupter technique for measuring anesthesia. Anesthesiology 26:168–178 ics of lungs and chest in man. J Appl respiratory mechanics. J Appl Physiol 8. Bates JH, Brown KA, Kochi T (1989) Physiol 8:587–594 64:2204–2214 Respiratory mechanics in the nor- 13. Farre R, Ferrer M, Rotger M, Torres A, 3. Mount LE (1955) The ventilation-flow mal dog determined by expiratory Navajas D (1998) Respiratory me- resistance and compliance of rats lungs. flow interruption. J Appl Physiol chanics in ventilated COPD patients: J Physiol (Lond) 127:157–167 67:2276–2285 forced oscillations versus occlusion 4. D’Angelo E, Calderini E, Torri G, 9. Eissa NT, Ranieri VM, Corbeil C, techniques. Eur Respir J 12:170–176 Robatto FM, Bono D, Milic-Emili J Chasse M, Robatto FM, Braidy J, 14. Farre R, Gavela E, Rotger M, Ferrer M, (1989) Respiratory mechanics in anes- Milic-Emili J (1991) Analysis of behav- Roca J, Navajas D (2000) Noninvasive thetized paralyzed humans: effects of ior of the respiratory system in ARDS assessment of respiratory resistance in flow, volume, and time. J Appl Physiol patients: effects of flow, volume, and severe chronic respiratory patients with 67:2556–2564 time. J Appl Physiol 70:2719–2729 nasal CPAP. Eur Respir J 15:314–319 5. Bates JH, Rossi A, Milic-Emili J (1985) 10. Guerin C, Coussa ML, Eissa NT, Cor- 15. Conti G, Rocco M, Antonelli M, Analysis of the behavior of the respi- beil C, Chasse M, Braidy J, Matar N, Bufi M, Tarquini S, Lappa A, Gas- ratory system with constant inspiratory Milic-Emili J (1993) Lung and chest paretto A (1997) Respiratory system flow. J Appl Physiol 58:1840–1848 wall mechanics in mechanically ven- mechanics in the early phase of tilated COPD patients. J Appl Physiol acute respiratory failure due to severe 74:1570–1580 kyphoscoliosis. Intensive Care Med 23:539–544 20 C. Guerin and J.-C. Richard
16. Pelosi P, Croci M, Ravagnan I, Vi- 18. Elsasser S, Guttmann J, Stocker R, 20. Tantucci C, Corbeil C, Chasse M, Ro- cardi P, Gattinoni L (1996) Total Mols G, Priebe HJ, Haberthur C battoFM,NavaS,BraidyJ,MatarN, respiratory system, lung, and chest (2003) Accuracy of automatic tube Milic-Emili J (1992) Flow and volume wall mechanics in sedated-paralyzed compensation in new-generation me- dependence of respiratory system postoperative morbidly obese patients. chanical ventilators. Crit Care Med flow resistance in patients with adult Chest 109:144–151 31:2619–2626 respiratory distress syndrome. Am Rev 17. Rohrer F (1915) Der Strömungswider- 19. Gattinoni L, Pelosi P, Suter PM, Pe- Respir Dis 145:355–260 stand in den menschlichen Atemwegen doto A, Vercesi P, Lissoni A (1998) und der Einfluss der unregelmässigen Acute respiratory distress syndrome Verzweigung des Bronchialsystems caused by pulmonary and extrapul- auf den Atmungsverlauf in verschiede- monary disease. Different syndromes? nen Lungenbezirken. Pfluegers Arch Am J Respir Crit Care Med 158:3–11 Gesamte Physiol Menschen Tiere 162:225–299 Theodoros Vassilakopoulos Understanding wasted/ineffective efforts in mechanically ventilated COPD patients using the Campbell diagram
Introduction In normal subjects inspiration starts from the relaxation volume of the respiratory system (Vr), where the Pel(L) Wasted or ineffective efforts are inspiratory efforts that fail and Pel(cw) intersect (i. e., where the tendency of the lung to trigger the ventilator [1]. Nearly 25% of mechanically to recoil inward is equal to the tendency of the chest wall to ventilated patients exhibit ineffective efforts which are expand; Fig. 1a). Inspiratory muscle action results in pres- even more frequent in COPD patients [2]. The pathophys- sure development (Pinsp) on the left of the Pel(cw). Inspi- iology of wasted efforts can be illustratively presented ratory flow, and thus increases in volume (VL), take place using the Campbell diagram. on the left of the Pel(L) and coincide with the beginning of inspiratory muscle action. At any volume, the horizon- tal distance between the Pel(cw) and Pel(L) represents the Campbell diagram portion of inspiratory muscle action devoted to expanding the lung at this volume with open airways and the portion The Campbell diagram is constructed by plotting the on the left of the Pel(L) represents the pressure dissipated dynamic relation between pleural pressure (measured with to generate airflow. Inspiration ends on the Pel(L) (point of an esophageal balloon) and lung volume during breathing zero flow) and the inspiratory muscles relax [so that pres- in relation to the passive pressure-volume curves of the sure returns on the Pel(cw)]. Expiration is usually passive, lung Pel(L) and the chest wall Pel(cw) [3]. The Pel(cw) and the respiratory system returns to its relaxation volume is constructed by connecting the values taken by the on the Pel(cw); however, in patients with respiratory dis- esophageal pressure during passive inflation (i. e., with tress, such as mechanically ventilated COPD patients, ex- no respiratory muscle activity) at different lung volumes; piration is frequently active. In the case of active expira- thus, any change in esophageal pressure is referred to this tion, pressure develops on the right of the Pel(cw) due to line in the Campbell diagram in order to calculate the true activity of expiratory muscles (Pexp). This returns volume muscular pressure developed by the patient. back to the relaxation volume of the respiratory system.
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 21 DOI: 10.1007/978-3-642-01769-8_6, © Springer-Verlag Berlin Heidelberg 2009 22 T. Vassilakopoulos
Why are COPD patients prone increases in volume (VL). This inspiratory effort is called to develop wasted/ineffective efforts? ineffective or wasted.
In COPD patients with dynamic hyperinflation, inspira- tion starts from an increased end-expiratory lung volume (Fig. 1b). Inspiratory muscle action has to overcome the in- Is the Campbell diagram useful for estimating trinsic positive end expiratory pressure [PEEPi, horizontal the work of breathing during wasted efforts? distance between the Pel(L) and Pel(cw)] before it results in inspiratory flow and thus increases in volume (VL). In The Campbell diagram is useless to estimate inspiratory mechanically ventilated patients, inspiratory muscle action work of breathing when inspiratory triggering does not has to additionally overcome the trigger sensitivity (Ptr) of happen (i. e., during wasted efforts): work is physically the ventilator [horizontal distance between the Pel(L) and defined as the area subtended in a pressure/volume loop. Ptr] before it results in inspiratory flow and thus increases Since there is no inspiratory volume, the work is zero in volume (VL); thus, in mechanically ventilated COPD (albeit muscles, indeed, consume energy). The energy patients, inspiratory muscle action has to overcome PEEPi expenditure during non-triggered wasted inspiratory plus the trigger sensitivity (Ptr). efforts can be estimated by the pressure/time product: When the magnitude of inspiratory muscle action is the product of the pressure developed by the inspiratory less than the sum of PEEPi plus Ptr this inspiratory ef- muscles [difference between the measured esophageal fort (Fig. 1b, orange line) cannot trigger the ventilator, and pressure and the Pel(cw)] multiplied by the time of muscle consequently does not result in inspiratory flow and thus contraction (i. e., neural Ti).
Fig. 1 a In normal subjects inspiration starts from the relaxation vol- volume of the respiratory system. b In COPD patients with dynamic ume of the respiratory system, where the passive pressure-volume hyperinflation, inspiration starts from an increased end-expiratory curves of the lung [Pel(L)] and chest wall [Pel(cw)] intersect. Inspira- lung volume. Inspiratory muscle action has to overcome the intrinsic tory muscle action results in pressure development (Pinsp)ontheleft positive end expiratory pressure [PEEPi, red dashed line, horizontal of the pressure-volume curve of the chest wall [Pel(cw)]. Inspiratory distance between the Pel(L) and Pel(cw)] before it results in inspira- flow, and thus increases in volume (V L ) take place on the left of the tory flow and thus increases in volume. In mechanically ventilated pressure-volume curve of lung and coincide with the beginning of patients, inspiratory muscle action has to overcome PEEPi plus the inspiratory muscle action. Inspiration ends on the pressure-volume trigger sensitivity (Ptr) before it results in inspiratory flow and thus curve of the lung and the inspiratory muscles relax (so that pressure increases in volume (V L ). When the magnitude of inspiratory mus- returns on the pressure-volume curve of the chest wall). In the case cle action is less than the sum of PEEPi + Ptr this inspiratory effort shown, expiration is active so that pressure develops on the right of (orange line) cannot trigger the ventilator and consequently does not the pressure-volume curve of the chest wall due to activity of ex- result in inspiratory flow and thus increases in volume (V L ). This piratory muscles (Pexp). This returns volume back to the relaxation inspiratory effort is called ineffective or wasted Understanding wasted/ineffective efforts in mechanically ventilated COPD patients 23
How are ventilator settings affecting the incidence in the presence of respiratory muscle weakness [7]. The of wasted/ineffective efforts? following expiratory effort (Fig. 2a, blue curve) decreases the end expiratory lung volume. When the end expiratory Excessive ventilator support predisposes to ineffective ef- lung volume decreases to a level where the ensuing inspi- forts irrespective of the mode used [2, 4–7]. This is be- ratory effort exceeds PEEPi plus Ptr, the ventilator is trig- cause, in the case of COPD, excessive pressure or vol- gered again to deliver a machine breath (Fig. 2a, mauve ume delivered by the ventilator combined with the long curve). The breath-to-breath variability in breathing pat- time constant of the respiratory system (which retards lung tern contributes to the variability in the end-expiratory lung emptying) and/or a short imposed expiratory time (in case volume and thus to the frequency of ineffective efforts [7]. of volume or pressure control) results in further increased Alternatively, during assist control mechanical venti- end-expiratory lung volume before the next inspiratory ef- lation, prolonged imposed inspiratory time (machine Ti) fort begins (Fig. 2a, green curve). At the same time, ex- greater than the patient’s neural Ti results in a situation cessive ventilator assistance reduces inspiratory muscle ef- where the ventilator is inflating the patient long after the in- fort, via either a phenomenon called neuromechanical in- spiratory muscles have stopped their contraction, i. e., dur- hibition (the main mechanism most likely being the Her- ing the neural expiration [6, 9]. During pressure support ing–Breuer reflex) [8], and/or by producing alkalemia via ventilation, the expiratory trigger threshold (percentage of excessive CO2 reduction in patients with chronic bicarbon- peak inspiratory flow at which the ventilator cycles to ex- ate elevation, thus reducing the drive to breathe [2]. The piration) might be quite low, leading to pressure support ensuing inspiratory effort is inadequate to overcome PEEPi being delivered well beyond the patient’s neural Ti [10]. plus Ptr and thus, this inspiratory effort fails to trigger the In either case, the next inspiratory effort (controlled by ventilator (Fig. 2a, red line). This is of course exaggerated the patient’s respiratory controller) begins during the early
Fig. 2 a In the case of COPD presented, the first inspiratory effort the end-expiratory lung volume decreases to a level where the (orange curve) triggers the ventilator. In the next breath that trig- ensuing inspiratory effort exceeds PEEPi + Ptr, the ventilator is gered the ventilator, excessive ventilator assistance (either pressure triggered again to deliver a machine breath (mauve curve). b In the or volume) resulted in large tidal volume (green curve), which presence of increased end-expiratory lung volume (green curve), combined with the long time constant of the respiratory system addition of an amount of external PEEP lower than the intrinsic (which retards lung emptying) and/or a short imposed expiratory PEEP (red dotted lines) offers part of the pressure required to time (in case of volume or pressure control) led to further increased overcome PEEPi + Ptr. The inspiratory effort starts closer to the end-expiratory lung volume before the next inspiratory effort passive pressure-volume curve of the lung [Pel(L)]. The horizontal begins (green curve). The ensuing inspiratory effort is inadequate distance between this point and the passive pressure-volume curve to overcome PEEPi + Ptr due to the increased end expiratory lung of the chest wall [Pel(cw)] is the applied PEEP (PEEP external). volume; thus, this inspiratory effort fails to trigger the ventilator The inspiratory effort is now adequate to trigger the ventilator (wasted or ineffective effort, red line). The following expiratory (orange curve) effort (blue curve) decreases the end-expiratory lung volume. When 24 T. Vassilakopoulos phase of ventilator expiration, i. e., at an increased lung Another solution is the use of PEEP [1, 6]. The addi- volume [5]. This effort might not be sufficient to overcome tion of an amount of external PEEP lower than the intrinsic PEEPi plus Ptr, and thus this inspiratory effort also fails to PEEP (Fig. 2b, red dotted lines) offers part of the pressure trigger the ventilator. required to overcome PEEPi plus Ptr (Fig. 2b). The inspi- ratory effort starts closer to the Pel(L) [the horizontal dis- tance between this point and the [Pel(cw) being the applied How can wasted efforts be detected at the bedside? PEEP (PEEP external)]. The inspiratory effort is now ade- quate to trigger the ventilator (orange curve). Wasted efforts can be clinically detected when the breaths During assist control reducing machine Ti (or equiva- delivered by the ventilator (measured rate on the ventila- lently increasing the inspiratory flow) may prevent ventila- tor display) are less than the number of inspiratory efforts tor delivery beyond the patients’ neural Ti and will reduce of the patient (on clinical examination) at the same time wasted efforts. Similarly, during pressure support increas- interval (see ESM, slides 1 and 2). On modern ventilator ing the expiratory trigger threshold will stop the breath ear- screens, ineffective efforts can be detected as abrupt air- lier and will reduce wasted efforts [13]. way pressure drop simultaneous to an abrupt decrease in expiratory flow (from the flow trajectory established earlier during expiration) and not followed by a machine breath (see ESM, slide 2). Monitors that can automatically detect Conclusion wasted efforts are under clinical testing and will be become available in the future [11, 12]. Wasted efforts are a major cause of patient ventilator dyssynchrony that increase the energy expenditure of the respiratory muscles and may injure them. Understanding What ventilator adjustments should be done their pathophysiology is essential to properly adjust the in the presence of wasted/ineffective efforts? ventilator settings to attenuate or eliminate them. Wasted efforts should be searched before any change in ventilator The self-evident solution to reduce the frequency of wasted settings is implemented during assisted modes of mechani- efforts is to decrease the level of excessive ventilator assis- cal ventilation, since any ensuing increase in ventilator rate tance, thus reducing hyperinflation and the pathophysiol- might be caused by the attenuation of wasted efforts (the ogy presented above [4, 6, 7]; however, this might not be ventilator rate now approaching the patient’s respiratory always clinically feasible, since it might lead to respiratory controller rate) and not by the development of respiratory distress and to derangement of blood gases [6]. distress with the new settings.
References 1. Fernandez R, Benito S, Blanch L, 6. Nava S, Bruschi C, Rubini F, Palo A, 10. Beck J, Gottfried SB, Navalesi P, Net A (1988) Intrinsic PEEP: a cause Iotti G, Braschi A (1995) Respira- Skrobik Y, Comtois N, Rossini M, of inspiratory muscle ineffectivity. tory response and inspiratory effort Sinderby C (2001) Electrical activity Intensive Care Med 15:51–52 during pressure support ventilation of the diaphragm during pressure 2. Thille AW, Rodriguez P, Cabello B, in COPD patients. Intensive Care support ventilation in acute respira- Lellouche F, Brochard L (2006) Patient- Med 21:871–879 tory failure. Am J Respir Crit Care ventilator asynchrony during assisted 7. Chao DC, Scheinhorn DJ, Stearn- Med 164:419–424 mechanical ventilation. Intensive Care Hassenpflug M (1997) Patient- 11. Younes M, Brochard L, Grasso S, Kun J, Med 32:1515–1522 ventilator trigger asynchrony in Mancebo J, Ranieri M, Richard JC, 3. Cabello B, Mancebo J (2006) prolonged mechanical ventilation. Younes H (2007) A method for Work of breathing. Intensive Care Chest 112:1592–1599 monitoring and improving patient: Med 32:1311–1314 8. Dempsey JA, Skatrud JB (2001) Apnea ventilator interaction. Intensive Care 4. Leung P, Jubran A, Tobin MJ (1997) following mechanical ventilation may Med 33:1337–1346 Comparison of assisted ventilator be caused by nonchemical neurome- 12. Mulqueeny Q, Ceriana P, Carlucci A, modes on triggering, patient effort, chanical influences. Am J Respir Crit Fanfulla F, Delmastro M, Nava S (2007) and dyspnea. Am J Respir Crit Care Care Med 163:1297–1298 Automatic detection of ineffective Med 155:1940–1948 9. Parthasarathy S, Jubran A, Tobin MJ triggering and double triggering during 5. Tobin MJ, Jubran A, Laghi F (2001) (1998) Cycling of inspiratory and expi- mechanical ventilation. Intensive Care Patient-ventilator interaction. Am J ratory muscle groups with the ventilator Med 33:2014–2018 Respir Crit Care Med 163:1059–1063 in airflow limitation. Am J Respir Crit 13. Tassaux D, Gainnier M, Battisti A, Care Med 158:1471–1478 Jolliet P (2005) Impact of expiratory trigger setting on delayed cycling and inspiratory muscle workload. Am J Respir Crit Care Med 172:1283–1289 U. Lucangelo Dead space L. Blanch
alveolar Vd (Vdalv). Mechanical ventilation, if present, adds additional Vd as part of the ventilator equipment (endotracheal tubes, humidification devices, and connec- tors). This instrumental dead space is considered to be part of the Vdaw. Physiologic dead space (Vdphys)is comprised of Vdaw (instrumental and anatomic dead space) and Vdalv and it is usually reported in mechanical ventilation as the portion of tidal volume (Vt) or minute ventilation that does not participate in gas exchange [1, 2]. A device that measures partial pressures (PCO2)or fractions (FCO2)ofCO2 during the breathing cycle is called a capnograph. The equation to transform FCO2 into PCO2 is PCO2 = FCO2 multiplied by the difference between barometric pressure minus water-vapour pres- sure. Time-based capnography expresses the CO2 signal as a function of time and from this plot mean expiratory Introduction (Douglas bag method) or end-expiratory (end-tidal) CO2 values can be obtained. The integration of the volume Dead space is that part of the tidal volume that does not signal using an accurate flow sensor (pneumotachograph) participate in gas exchange. Although the concept of and CO2 signal (with a very fast CO2 sensor) is known as pulmonary dead space was introduced more than a volumetric capnography. Combined with the measure- hundred years ago, current knowledge and technical ment of arterial PCO2 (PaCO2) it provides a precise advances have only recently lead to the adoption of dead quantification of the ratio of Vdphys to Vt. The three space measurement as a potentially useful bedside clinical phases of a volumetric capnogram are shown in Fig. 1 tool. and Fig. 2. The combination of airflow and mainstream capnography monitoring allows calculation of breath by breath CO2 production and pulmonary dead space. Concept of dead space Therefore, the use of volumetric capnography is clinically more profitable than time-based capnography. The homogeneity between ventilation and perfusion determines normal gas exchange. The concept of dead space accounts for those lung areas that are ventilated but Measurement of dead space using CO2 not perfused. The volume of dead space (Vd) reflects the as a tracer gas sum of two separate components of lung volume: 1) the nose, pharynx, and conduction airways do not contribute Bohr originally defined Vd/Vt [2] as: Vd/Vt = (FACO2– to gas exchange and are often referred to as anatomical FECO2)/FACO2, where FACO2 and FECO2 are fractions of Vd or herein as airway Vd (Vdaw); 2) well-ventilated CO2 in alveolar gas and in mixed expired gas, respec- alveoli but receiving minimal blood flow comprise the tively. End-tidal CO2 is used to approximate FACO2,
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 25 DOI: 10.1007/978-3-642-01769-8_7, © Springer-Verlag Berlin Heidelberg 2009 26 U. Lucangelo and L. Blanch
Fig. 1 A Single-breath expiratory volumetric capnogram recorded in a healthy patient receiving controlled mechanical ventilation. Dead-space components are shown graphically and equations are depicted and explained in the text. Phase I is the CO2 free volume which corresponds to Vdaw. Phase II represents the transition Fig. 2 A Single-breath expiratory volumetric capnogram recorded between airway and progressive emptying of alveoli. Phase III in a chronic obstructive pulmonary disease patient receiving represents alveolar gas. PaCO2 is arterial PCO2; PetCO2 is end-tidal controlled mechanical ventilation. The three phases of the volu- PCO2. Drawings adapted from [2]; B Single-breath expiratory metric capnogram are depicted. The transition from phase II to III is carbon dioxide volume (VCO2) plotted as a function of exhaled less evident due to heterogeneity of ventilation and perfusion ratios. tidal volume. The alternative method to measure airway dead space Dead-space components are shown graphically and equations are (Vdaw) described by Langley et al. [3] is graphically shown in a depicted and explained in the text. PaCO2 is arterial PCO2; PetCO2 healthy patient receiving controlled mechanical ventilation is end-tidal PCO2. Drawings adapted from [2]; B Single-breath expiratory carbon dioxide volume (VCO2) plotted as a function of exhaled tidal volume. The alternative method to measure airway assuming end-tidal and alveolar CO fractions are iden- dead space (Vdaw) described by Langley et al. [3] is graphically 2 shown in a chronic obstructive pulmonary disease patient receiving tical. Physiologic dead space calculated from the Enghoff controlled mechanical ventilation modification of the Bohr equation uses PaCO2 with the assumption that PaCO2 is similar to alveolar PCO2 [2], such that: Vdphys/Vt = (PaCO2–PECO2)/PaCO2, where a vertical line traced so as to have equal p and q areas. PECO2 is the partial pressure of CO2 in mixed expired gas Airway dead space is then measured from the beginning and is equal to the mean expired CO2 fraction multiplied of expiration to the point where the vertical line crosses by the difference between the atmospheric pressure and the volume axis [1]. By tracing a line parallel to the the water-vapour pressure. Since Vd /Vt measures the phys volume axis and equal to the PaCO2, it is possible to fraction of each tidal breath that is wasted on both Vdalv determine the readings from areas y and z, which and Vdaw, the Vdaw must be subtracted from Vdphys/Vt to respectively represent the values of alveolar and airway obtain the Vdalv/Vt. Vdphys/Vt is the most commonly and dead space. Referring these values to the Vt, it is possible commercially (volumetric capnographs) formula used to to single out several Vd components [2]: estimate pulmonary dead space at the bedside. Additional methods mostly used in research to calcu- Vdphys=Vt¼ðY þ ZÞ=ðX þ Y þ ZÞ late all the Vd components are shown in Fig. 1A and Vdalv=Vt¼Y=ðX þ Y þ ZÞ Fig. 2A. Fowler [1] introduced a procedure for measuring Vdaw=Vt¼Z=ðX þ Y þ ZÞ Vdaw based on the geometric method of equivalent areas (p = q), obtained by crossing the back extrapolation of phase III of the expired CO2 concentration over time with Dead space 27
An alternative method to measure airway dead space may increase ventilator dead space and induce hypercap- introduced by Langley et al. [3] is based on determination nia during low Vt or low minute ventilation. Vdaw of the VCO2 value, which corresponds to the area calculations include the ventilator dead space. Because inscribed within the CO2 versus volume curve (indicated the anatomic dead space remains relatively constant as Vt in Fig. 1A and Fig. 2A as X area). Figure 1B and Fig. 2B is reduced, very low Vt is associated with a high Vd/Vt are examples of Vdaw calculation using the Langley et al. ratio [1, 2, 7, 8, 9]. [3] method. Briefly, VCO2 is plotted versus expired Positive end-expiratory pressure (PEEP) is used to breath volume. Thereafter, Vdaw can be calculated from increase lung volume and to improve oxygenation in the value obtained on the volume axis by back extrap- patients with acute lung injury. Vdalv is large in acute lung olation from the first linear part of the VCO2 versus injury and does not vary systematically with PEEP. volume curve. However, when the effect of PEEP is to recruit collapsed Although these indexes are clinically useful, they are lung units resulting in an improvement of oxygenation, always bound to visual criteria for the definition of phase Vdalv may decrease, and alveolar recruitment is associated III of the expired capnogram. Often, the geometric with decreased arterial minus end-tidal CO2 difference [4, analysis establishing the separation between the phase II 5, 6]. Conversely, PEEP-induced overdistension may and phase III is hardly seen and the rate of CO2 raising of increase Vdalv and widen this difference [7]. the phase III is nonlinear in patients with lung inhomo- In patients with sudden pulmonary vascular occlusion geneities (Fig. 2A). due to pulmonary embolism, the resultant high VA/QT mismatch produces an increase in Vdalv. The association of a normal D-dimer assay result plus a normal Vdalv is a Utility of dead space in different clinical scenarios highly sensitive screening test to rule out the diagnosis of pulmonary embolism [9]. The CO2 tension difference between pulmonary capillary blood and alveolar gas is usually small in normal subjects and end-tidal PCO2 is close to alveolar and arterial PCO2. Dead space and outcome prediction Physiologic dead space is the primary determinant of the difference between arterial and end-tidal PCO2 (DPCO2) Characteristic features of acute lung injury are alveolar in patients with a normal cardio-respiratory system. and capillary endothelial cell injuries that result in Patients with cardiopulmonary diseases have altered alterations of pulmonary microcirculation. Consequently, ventilation to perfusion (VA/QT) ratios producing abnor- adequate pulmonary ventilation and blood flow across the malities of Vd, as well as in intrapulmonary shunt, and lungs are compromised and Vdphys/Vt increases. A high the latter may also affect the DPCO2.ADPCO2 beyond dead-space fraction represents an impaired ability to 5 mmHg is attributed to abnormalities in Vdphys/Vt and/or excrete CO2 due to any kind of VA/QT mismatch [7]. by an increase in venous admixture (the fraction of the Nuckton et al. [10] demonstrated that a high Vdphys/Vt cardiac output that passes through the lungs without was independently associated with an increased risk of taking oxygen) or both. The increase in Vdphys/Vt seen in death in patients diagnosed with acute respiratory distress normal patients when anaesthetised may be attributed to syndrome. muscle paralysis, which causes a reduction of functional residual capacity and alters the normal distribution of ventilation and perfusion across the lung [2, 4, 5, 6]. Conclusions Ventilation to regions having little or no blood flow (low alveolar PCO2) affects pulmonary dead space. In The advanced technology combination of airway flow patients with airflow obstruction, inhomogeneities in monitoring and mainstream capnography allows breath- ventilation are responsible for the increase in Vd. Shunt by-breath bedside calculation of pulmonary Vd and CO2 increase VDphys/Vt as the mixed venous PCO2 from elimination. For these reasons, the use of volumetric shunted blood elevates the PaCO2, increasing VDphys/Vt capnography is clinically more useful than time capnog- by the fraction that PaCO2 exceeds the nonshunted raphy. Measurement of dead-space fraction early in the pulmonary capillary PCO2 [7]. Vdalv is increased by course of acute respiratory failure may provide clinicians shock states, systemic and pulmonary hypotension, ob- with important physiologic and prognostic information. struction of pulmonary vessels (massive pulmonary em- Further studies are warranted to assess whether the bolus and microthrombosis), even in the absence of a continuous measurement of different derived capnograph- subsequent decrease in ventilation and low cardiac output. ic indices is useful for risk identification and stratifica- Vdaw is increased by lung overdistension and additional tion, and to track the effect of a therapeutic intervention ventilatory apparatus dead space. Endotracheal tubes, heat during the course of disease in critically ill patients. and moisture exchangers, and other common connectors 28 U. Lucangelo and L. Blanch
References
1. Fowler WS (1948) Lung function stud- 5. Blanch L, Lucangelo U, Lopez-Aguilar 8. Feihl F (2003) Respiratory dead space ies II: the respiratory dead-space. Am J J, Fernandez R, Romero P (1999) Vol- and survival in the acute respiratory Physiol 154:405–410 umetric capnography in patients with distress syndrome. In: Gullo A (ed) 2. Fletcher R, Jonson B, Cumming G, acute lung injury: effects of positive Anesthesia pain intensive care and Brew J (1981) The concept of dead end-expiratory pressure. Eur Respir J emergency medicine, vol. 1. Springer, space with special reference to the 13:1048–1054 Berlin Heidelberg New York, pp 275– single breath test for carbon dioxide. Br 6. Beydon L, Uttman L, Rawal R, Jonson 287 J Anesth 53:77–88 B (2002) Effects of positive end-expi- 9. Kline JA, Israel EG, Michelson EA, 3. Langley F, Even P, Duroux P, Nicolas ratory pressure on dead space and its O’Neil BJ, Plewa MC, Portelli DC RL, Cumming G (1975) Ventilatory partitions in acute lung injury. Intensive (2001) Diagnostic accuracy of a bedside consequences of unilateral pulmonary Care Med 28:1239–1245 D-dimer assay and alveolar dead space artery occlusion. In: Distribution des 7. Coffey RL, Albert RK, Robertson HT measurement for rapid exclusion of exchanges gaseaux pulmonaires. (1983) Mechanisms of physiological pulmonary embolism. JAMA 285:761– INSERM, 1976. WF D613. Paris, dead space response to PEEP after acute 768 France, pp 209–212 oleic acid lung injury. J Appl Physiol 10. Nuckton TJ, Alonso JA, Kallet RH, 4. Blanch L, Fernandez R, Benito S, 55:1550–1557 Daniel BM, Pittet JF, Eisner MD, Mancebo J, Net A (1987) Effect of Matthay A (2002) Pulmonary dead- PEEP on the arterial minus end-tidal space fraction as a risk factor for death carbon dioxide gradient. Chest 92:451– in the acute respiratory distress syn- 454 drome. N Eng J Med 346:1281–1286 Peter D. Wagner The multiple inert gas elimination technique (MIGET)
Abstract This brief review centers its information content is explained, on the multiple inert gas elimination and its limitations are described. It is technique (MIGET). This technique, noted that in addition to quantifying developed in the 1970s, measures ventilation/perfusion inequality and the pulmonary exchange of a set of pulmonary shunting, MIGET can six different inert gases dissolved identify and quantify diffusion limi- together in saline (or dextrose) and tation of O2 exchange, when present, infused intravenously. It then uses as well as explain the contributions of those measurements to compute the extrapulmonary influences such as in- distribution of ventilation/perfusion spired O2 concentration, ventilation, ratios that best explains the exchange cardiac output, Hb concentration/P50, of the six gases simultaneously. body temperature and acid/base MIGET is based on the very same state on arterial oxygenation. An mass-conservation principles un- overview of the technical details of derlying the classic work of Rahn implementing MIGET is given, and and Fenn and of Riley and cowork- the review ends with potential future ers in the 1950s, which defines the applications. relationship between the ventila- tion/perfusion ratio and the alveolar Keywords Ventilation/perfusion in- and capillary partial pressures of equality · Shunt · Alveolar–capillary any gas. After a brief history of diffusion limitation · Hypoxemia · MIGET, its principles are laid out, Hypercapnia · Inert gases
Introduction rameters, while readily available and clinically useful, of- fer quite limited information and are open to misinterpre- Most patients cared for in the ICU have inefficient pul- tation when the underlying assumptions and requirements monary gas exchange, causing hypoxemia and requiring are not met. For the most part, the four causes of hypox- increased inspired O2 levels to sustain O2 availability to emia are difficult to distinguish in any given patient using tissues. Most medical students know that hypoxemia may these tools. Intensivists also know that in addition to the be caused by one or more of four different physiologi- above four causes of hypoxemia, so-called extrapulmonary cal processes [1]: (1) Hypoventilation, (2) diffusion lim- factors can greatly modulate arterial PO2. These factors itation, (3) ventilation/perfusion inequality, and (4) shunt are, in addition to FIO2, total ventilation, cardiac output, (right to left). Most residents know that hypoxemia can metabolic rate, Hb concentration, Hb P50, body tempera- be assessed by any of five common parameters: (1) ar- ture, and acid/base status. terial PO2 (and PCO2) itself, (2) arterial PO2/FIO2 ratio, The multiple inert gas elimination technique (3) alveolar–arterial PO2 difference, (4) venous admixture (MIGET) [2–5] was introduced in the early 1970s as (also termed physiological shunt), and (5) physiological a way to overcome many of the limitations imposed by the dead space. Most intensivists know that these several pa- classical methods mentioned above. This short review will
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 29 DOI: 10.1007/978-3-642-01769-8_8, © Springer-Verlag Berlin Heidelberg 2009 30 P.D. Wagner discuss the MIGET in terms of its history, its theoretical applies and looks like this: basis, its implementation, and its future, in that order. ˙ / ˙ = . × ×[ − ]/[ ]( ) VA Q 8 63 solubility PvIG PcIG PA IG 3
A brief history of the MIGET [because concentration = solubility × partial pressure In the late 1940s, 1950s and early 1960s, prior to the (Henry’s Law)]. Using this nomenclature, solubility is the availability of digital computation, three groups of inves- ratio of concentration to partial pressure, and is usually tigators developed the modern foundations of pulmonary expressed in ml (of the gas dissolved in blood) per dl (of gas exchange. Rahn and Fenn published their remarkable blood) per mmHg partial pressure (of the gas in blood). Now, if we assume that diffusion equilibration for an inert graphical analysis of the relationship between PO2,PCO2, and the ventilation perfusion ratio, VA/˙ Q˙ [6]; Riley and gas is complete, Pc IG =PAIG. Dropping the subscript IG λ coworkers developed the concepts of quantifying gas and recognizing that , the blood–gas partition coefficient × exchange disturbances by calculating venous admixture of the inert gas, =8.63 solubility, we have: and physiological dead space [7, 8], and Briscoe and King added to this new scientific domain by exploring the VA˙ /Q˙ = λ ×[Pv − PA]/[PA].(4) relationship between ventilation/perfusion inequality and diffusion limitation of O2 transport in the lung [9, 10]. Note that λ, in words, is the ratio of concentrations of The foundation of all of their efforts was one simple the gas in blood and (alveolar) gas, at equilibrium. Equa- principle: steady-state gas exchange in the lung obeyed tion 4 can be rearranged as follows: mass-conservation principles. Simple mass-conservation equations for O (and CO ) were written down for both 2 2 PA/Pv = λ/[λ + VA˙ /Q˙ ]=Pc /Pv.(5) disappearance of O2 from alveolar gas and its subsequent appearance in the pulmonary capillary blood. This led to the famous ventilation/perfusion equation, approximated This equation says that for an inert gas being eliminated from the blood by the lung, the fraction that is not elimi- for O2 as follows: nated (i.e., the fraction that is retained in the end-capillary ˙ ˙ VA/Q = 8.63 ×[Cc O2 − CvO2]/[PIO2 − PAO 2] (1) blood, Pc /Pv) is a simple function of the partition coeffi- cient (λ)andtheVA/˙ Q˙ ratio. and for CO2: The point of this exercise is to show that Eq. 5, which turns out to be the complete foundation of the MIGET, ˙ / ˙ = . ×[ − ]/[ ].() VA Q 8 63 CvCO2 Cc CO2 PACO2 2 is nothing more than the ventilation/perfusion equation of mass conservation applied to an inert gas. Seymour Here, Cc and Cv represent end-capillary and mixed Kety [11] and then Leon Farhi and his colleagues [12, 13] venous concentrations (ml/dl) while PI and PA represent used this equation extensively to understand inert gas inspired and alveolar partial pressures (mmHg). Note exchange in the lung, and Farhi et al. went on to propose that 7.5 mmHg = 1 kP. The constant 8.63 reconciles a method for characterizing the lung as a two-compartment the units and conventional conditions of expression distribution of ventilation and blood flow using measured (O and CO concentrations in ml/dl, STPD; VA˙ in 2 2 PA/Pv ratios for three gases forced to exchange across the l/min, BTPS, Q˙ in l/min. Its value is actually given by lungs [13]. 0.01 × 760 × [(273 + T)/273], where 760 is standard Before moving to MIGET itself, another advance must barometric pressure in mmHg (101.3 kP) and T is body be mentioned: Lenfant and coworkers developed an ap- temperature in °C, assumed here to be 37. proach to use the pattern of arterial PO response to in- What do these equations tell us? That local alveolar 2 creasing FIO to calculate a continuous distribution of ven- PO (and PCO ) is uniquely set by the local VA/˙ Q˙ ratio 2 2 2 tilation and blood flow [14, 15]. While an approach based – for a given set of “boundary conditions” (the inspired on PO has some attraction, there were too many concerns and venous blood composition and the particulars of the 2 to support its widespread use. However, it laid the ground- O and CO dissociation curves). 2 2 work for the concept of (essentially) continuous VA/˙ Qdis-˙ These rather simple equations are tantalizingly hard to tributions as the “holy grail” of gas exchange research. actually solve – that is, to come up with the actual PO2 for any VA/˙ Q˙ ratio – because the dissociation curve is so com- plex. The principles apply to all gases, however, and if gas exchange is examined for a gas whose transport in blood is Theoretical basis of the MIGET only by physically dissolving, the above equations become much simpler. Returning to inert gases, Eq. 5 is the basis of MIGET. It re- Suppose such a gas (we shall call it an inert gas) is be- flects precisely the same physiological principles of mass ing eliminated from the body (just as is CO2). Equation 2 conservation as for O2 and CO2. The multiple inert gas elimination technique (MIGET) 31
How does it work?
Suppose we introduce a foreign inert gas into the body by venous infusion of a solution of that gas, and we measure retention as measured from an arterial blood sample as the ratio Pa/Pv (arterial to mixed venous inert gas partial pres- sure ratio, termed R). Further suppose the lung is perfectly homogeneous. We have:
R = λ/[λ + VA˙ /Q˙ ].(6) where VA/˙ Q˙ is the ratio of alveolar ventilation to cardiac output. Figure 1 (upper panel) shows R (calculated from Eq. 6) plotted against the VA/˙ Q˙ ratio for gases of different λ.It shows that for any gas, R falls as VA/˙ Q˙ ratio rises. Look at a gas with λ = 0.01 as an example: When VA/˙ Qisless˙ than about 0.001, the gas is essentially fully retained in the blood. At even lower VA/˙ Q˙ ratios, retention therefore does not change and this gas cannot discriminate between VA/˙ Q˙ ratios of, say, 0.001 and any lower value. Similarly, elimination is essentially complete at VA/˙ Q˙ ratios of 0.1 or higher, and this gas will not discriminate among VA/˙ Q˙ ratios higher than 0.1. However, in the range 0.001 to 0.1, retention of this gas is very sensitive to VA/˙ Q˙ ratio, and is thus a good gas to use to identify alveoli with VA/˙ Q˙ ratios in that range. Similar arguments apply to all other gases. Figure 1 (lower panel) plots exactly the same data, but this time retention is plotted against λ, not VA/˙ Q.˙ The message here is that a gas of a particular λ is best suited to identifying alveoli whose VA/˙ Q˙ ratios approximate the value of λ.ForVA/˙ Q˙ ratios 10 times (or more) lower than λ, retention is essentially complete, and is ˙ ˙ essentially zero when VA/Q is 10 times (or more) higher Fig. 1 Upper panel: Inert gas retention (as defined in, and computed than λ. Thus, if several inert gases (whose λ vary over from, Eq. 5) as a function of the ventilation/perfusion ratio (VA/˙ Q).˙ several decades) are exchanged simultaneously and their Each line reflects a gas of indicated partition coefficient, λ. While ˙ ˙ retentions measured, we have the potential to determine retention falls as VA/Q increases, and is higher for more soluble ˙ ˙ gases at any given VA/˙ Q˙ ratio, the key point is that a given gas is what kinds of VA/Q regions are present in any given lung. sensitive to VA/˙ Q˙ in only a fairly narrow range (from VA/˙ Q=10˙ × Figure 2 captures this concept more clearly with three lower to 10× higher than λ for that gas). Lower panel: Identical data examples: the upper panel represents a perfectly homo- as for upper panel, but now plotting retention against λ (defining the ˙ geneous lung (with VA/˙ Q˙ ratio = 1), the middle panel retention/solubility relationship) for lung regions of indicated VA/˙ Q. λ a lung with 50% of its blood flow perfusing a region The major point is that a gas of given is most sensitive to VA/˙ Q˙ ratios from 10× lower to 10× higher than its λ whose VA/˙ Q˙ ratio is low, at 0.01 (the remaining 50% perfusing normal regions), and the lower panel a lung with 50% of its blood flow perfusing completely un- ventilated regions (i.e., shunt, VA/˙ Q˙ = 0). In each, the distribution of VA/˙ Q˙ ratios. The mathematics underlying arterial retention values that would result for six different this relationship is somewhat complex and cannot be laid inert gases (named in the upper panel) are shown by out in such a brief review as this, but has been presented the solid circles. The end-capillary/mixed venous ratios on several occasions [5, 16–18]. It entails searching for associated with each of the contributing regions are the distribution of blood flow and ventilation that best fits, shown by the dashed lines in each case. It is clear that according to least-squares principles, the measured set the shape and position of these “retention–solubility” of retentions of the six gases. It is conceptually similar curves vary widely according to the particular pattern to a simple two-variable linear regression between a set of VA/˙ Q˙ regions present. What this means is that from of two variables, X and Y, where the slope and intercept the measured pattern of retentions of such a set of six of a straight line are found that best fit the paired (X,Y) gases, it is possible to deduce the underlying pattern of data by minimizing the sum of squares between the 32 P.D. Wagner
Fig. 3 Retention (and excretion)/solubility curves for a normal lung (upper panel) and corresponding distributions of ventilation and blood flow (lower panel). The range of VA/˙ Q˙ in health is only about one decade (∼0.3 to ∼3) as shown actual Y values and those predicted from the regression equation. Figure 2 is limited to arterial retention of the six gases, as would be measured from samples of arterial blood. It is also possible to measure the mixed expired concentra- tions of the same six gases at the same time, and we have called the ratio of mixed expired to mixed venous concen- tration excretion, E. Just as retention, R, reflects the pattern of allocation of blood flow to regions of different VA/˙ Q˙ ratio, excretion reflects the pattern of distribution of ven- tilation to the same regions. In any given lung, the values Fig. 2 Three examples of retention/solubility relationships. Top of E and R for the lung as a whole must obey mass conser- panel: Retention values expected in a normal lung, indicating the vation, such that: six inert gases commonly used in MIGET. Importantly, the six gases are chosen to sample the full extent of the curve. Middle panel: ˙ = ˙ × = λ × ˙ ×[ − ] ( ) Retention/solubility curve in a lung with equally perfused regions VIG VE E QT 1 R 7 of both normal and greatly reduced VA/˙ Q˙ ratios. The shape and ˙ position are grossly different from the normal lung. Bottom panel: Here, VIG is the volume of each inert gas eliminated Retention/solubility curve in a lung with equally perfused regions of per minute, VE˙ is total minute ventilation and QT is to- both normal and zero VA/˙ Q˙ ratios. Note that when VA/˙ Q˙ = 0, this means an unventilated lung region, i.e., a shunt. The shape and tal pulmonary blood flow (cardiac output). In addition, in position is grossly different from that in both the normal lung and any gas-exchange unit [i.e., a collection of alveoli in which ˙ ˙ the lung with low VA/Q regions PO2 (and PCO2) is uniform], local alveolar ventilation and The multiple inert gas elimination technique (MIGET) 33 local blood flow define the VA/˙ Q˙ ratio, or as written here: and blood flow for three representative lungs: a normal lung; a lung with 10% shunt; and a lung with 33% of the VA˙ = Q˙ × VA˙ /Q˙ (8) cardiac output perfusing very poorly ventilated alveoli, re- spectively. In each case, anatomic dead space (at 30% of Equations 7 and 8 show that knowledge of retention tidal volume) is present. Such dead space serves to dilute implies knowledge of excretion and that knowing the expired inert gas concentrations, reducing excretion values distribution of blood flow, we know the distribution of for all gases by the same proportion (here, by 30%). ventilation. From a theoretical point of view, it means These figures take some getting used to, but the we could measure the VA/˙ Q˙ distribution either from the main point here is that different VA/˙ Q˙ patterns underlie excretions or the retentions – they are two reflections of different retention/excretion patterns, such that by mea- the same function. However, in using MIGET, we measure suring the latter we can deduce the characteristics of the both excretion and retention because together they provide former. two views of the distribution and improve its information content, much as a PA and lateral chest X-ray together are better than either alone, even though both are seeing the What is MIGET’s information content? same lung. Figures 3, 4 and 5 bring all of this together and show What MIGET obviously provides is the quantitative shape retentions, excretions, and the distributions of ventilation and position of the distributions of ventilation and blood
Fig. 4 Retention (and excretion)/solubility curves for a lung that Fig. 5 Upper panel: Retention (and excretion)/solubility curves contains a 10% shunt (in which VA/˙ Q˙ = 0) but is otherwise nor- for a lung in which 33% of the blood flow perfuses units with mal (upper panel) and corresponding distributions of ventilation and averylowVA/˙ Q˙ and the rest flows through units of normal VA/˙ Q.˙ blood flow (lower panel). Shunt is shown by the closed circle at Lower panel: Corresponding distributions of ventilation and blood VA/˙ Q˙ = 0. Such distributions commonly reflect atelectasis, pneumo- flow. This pattern is common in chronic airway obstruction from nia, pulmonary edema, or pneumothorax asthma or COPD 34 P.D. Wagner
flow with respect to VA/˙ Q˙ ratio, as shown in Figs. 3–5. ature [20]. Each forms a specific input to the MIGET soft- This pictorial representation can be reduced to a number ware such that desired changes in each can be read in and of parameters that summarize the modality, position, the consequences for arterial PO2 assessed. dispersion, and (a)symmetry of the two curves. These parameters complement the visual image and are useful in allowing statistical comparison of distributions under What are MIGET’s limitations? different conditions. Importantly, as Figs. 4 and 5 show, a special strength of MIGET is that it distinguishes regions MIGET can only approximate the true distribution of ˙ of low VA/˙ Q ratio from unventilated regions (shunt). VA/˙ Q˙ ratios in the lung. We estimate that the human ˙ Symmetrically, it also separates areas of high VA/˙ Q ratio lung consists of about 100,000 individual gas exchange from unperfused regions (which thus have infinitely high units (in essence, the acini) [21]. Thus, it is theoretically ˙ VA/˙ Q ratio). possible that 100,000 different VA/˙ Q˙ ratios could exist, MIGET allows additional insights into gas exchange, and using just six gases it would be impossible to identify however. First, the presence of diffusion limitation for O2 them individually – it would take 100,000 gases! This is can be identified. Second, the role of so-called extrapul- more of a theoretical than a practical concern, however, monary factors on arterial PO2 and PCO2 can be quanti- because just as with any distributed biological variable, by fied. the time you have 100,000 units the ensuing distribution is highly likely to be smooth and therefore basically definable by a small number of measurements. The other Diffusion limitation of O2 exchange major limitation is that caused by random experimental error. We use a smoothing algorithm [5] to control error All gases cross the pulmonary blood–gas barrier by diffu- effects. In other words, we enforce a measure of smooth- sion. If the end-capillary partial pressure of any exchang- ing just sufficient to stabilize results when measurements ing gas is not equal to its alveolar value in any homoge- are repeated (i.e., when sequential distributions would neous lung region, diffusion limitation is said to be present. vary only due to random error). What this does is limit For O , this may cause hypoxemia additional to that caused the resolution of MIGET—it is not possible to accurately 2 ˙ by any VA/˙ Q inequality that is present. The key point here recover a distribution that is very narrow. In numbers, any is that inert gases reach equilibration (between capillary distribution whose actual dispersion is < 0.3 cannot be blood and alveolar gas) about 10 times faster than does identified as such and will likely be depicted as having O2.EvenwhenO2 is diffusion-limited, inert gases are not. a dispersion at that limit. (This unit of dispersion is called As a result, MIGET’s inert gases faithfully indicate only “LOG SD” and is a dimensionless number that is the ˙ ˙ VA/Q inequality even when O2 is diffusion-limited. Under second moment (on a log scale) of the distribution about such circumstances, the actual arterial PO will be lower its mean). Normal subjects usually show log SD values 2 ˙ than that which MIGET would predict from VA/˙ Q inequal- of 0.4–0.6; moderate disease is reflected by log SD in ity alone. Such a difference, due to diffusion limitation of the range of 1.0; and severe disease such as acute lung O2, is exploited within the MIGET software by comput- injury and ARDS would show values of 1.5–2.5. Again, ing the O2 diffusing capacity that would have to exist to this limitation is more theoretical than practical as normal explain the additional hypoxemia [19]. subjects rarely show log SD values at the lower limit of 0.3. Finally, it needs to be mentioned that while the distri- butions recovered by MIGET describe the total functional Role of extrapulmonary factors in O2 exchange abnormality of the lung, there is no regional anatomical information available, just as is the case with the classical Arterial hypoxemia is classically considered due to one or indices of gas exchange – venous admixture, physiological ˙ ˙ more of four phenomena: VA/Q inequality, shunt, diffu- dead space and the alveolar–arterial PO2 difference. sion limitation, and hypoventilation [1]. What is less well appreciated is that so-called extrapulmonary factors play a modulating role, affecting the level of hypoxemia pro- Implementation of the MIGET duced by the above four factors. For example, if cardiac output suddenly falls in a patient with VA/˙ Q˙ inequality, Implementing MIGET is relatively straightforward: so too will arterial PO2 because of the concomitant re- duction in pulmonary arterial PO2. MIGET software al- 1. The six gases (Fig. 2) are dissolved in a sterile bag of lows the user to separate out the quantitative effects of saline or dextrose by bubbling gas (SF6, ethane, cyclo- such changes in extrapulmonary variables. The extrapul- propane) or injecting liquid (enflurane, ether, acetone) monary variables that can play a role are: FIO , metabolic into that bag in a sterile manner. ˙ 2 rate (VO2), total alveolar ventilation, cardiac output, Hb 2. This sterile solution is infused into any peripheral vein concentration and P50, acid/base status, and body temper- at a rate in ml/min equal to about 1/4 of the minute The multiple inert gas elimination technique (MIGET) 35
ventilation expressed in l/min. Thus, at rest the rate is blood gases, ventilation, cardiac output, inspired gas, about 2–3 ml/min. This rate of infusion produces con- acid/base status, and temperature conditions) are then centrations of each gas in the ppm range or lower. At read into the MIGET software. This software consists rest, the infusion should run about 20 min before sam- of two programs that are run in sequence. The first ples are collected to allow development of steady-state program simply takes all of the input data, computes inert gas exchange. During exercise, a steady state is the retention and excretion values for the sample, reached far more quickly, and by the time O2 uptake and creates an input data file for the second program, itself is stable, so too is inert gas exchange. which reads those data and performs the least-squares 3. When desired, samples are then collected: about analysis to come up with the VA/˙ Q˙ distributions 7–8 ml each of systemic and pulmonary arterial blood and their associated summary parameters mentioned (heparinized) and 20 ml of mixed expired gas, all in above. It also computes the arterial PO2 and PCO2 gas-tight, glass syringes. Samples for conventional expected to result from the VA/˙ Q˙ inequality estimated blood gases (PO2,PCO2,pH,O2 saturation, [Hb]) are from the inert gases, and, if requested, will compute taken simultaneously. We almost always take duplicate the O2 diffusing capacity when measured arterial PO2 samples for both conventional and inert gases to both is less than that estimated from VA/˙ Q˙ inequality. The estimate and reduce error variance. Note that should two programs could easily be merged into one, but pulmonary arterial blood not be available, it is just as great value is seen in looking at the data produced good to calculate the mixed venous inert gas levels. by the first program for obvious problems before However, this requires an estimate or measurement of submitting them to the second program. cardiac output so that the Fick principle can be used with measured arterial and expired inert gas values. 4. The inert gas concentrations are measured by gas chro- Conclusions: what does the future hold for MIGET? matography. Details can be found elsewhere [3, 22]. In brief, SF6 is measured by ECD (electron capture MIGET was initially developed in the early 1970s. It re- detector) while the other five gases are measured by mains in use in a small number of centers around the world, FID (flame ionization detector). Stainless-steel (1/8th but the flurry of research in its first 20 years has subsided as in., 6–12 ft long) columns packed with Poropak-T many of the key questions it was able to shed light on have 80/100 mesh are used to separate the gases, which been answered. It has never evolved from a research tool are eluted in a total of 4–5 min isothermally at about to a clinical test for two reasons: First, because of its oper- 150°C at a carrier flow rate (FID: helium; ECD: N2) ational complexity. However, some attempts are currently of around 30 ml/min. A constant-volume (1–2 ml) gas under way to simplify the method and make it usable by sample valve is used to introduce samples into the the non-expert. Second, it provides more information than column. Mixed expired gas from the subject is directly we can currently use clinically in patient management and injected into the chromatograph, but inert gases in therefore is difficult to justify. blood samples must first be extracted by equilibrating That said, there is one key domain in which MIGET the blood sample with N2 gas in a closed syringe [3], has not yet been rigorously evaluated as a clinical moni- and then introducing that gas to the chromatograph. toring tool: the intensive care unit. In this setting, patients Through principles of mass conservation, the original have often rapidly evolving lung disease, and extrapul- blood concentrations (prior to N2 equilibration) can monary factors such as ventilation, FIO2, cardiac output, then be calculated if the partition coefficients of the hemoglobin concentration, acid/base status, and body gases and the volumes of blood and gas in the syringe temperature can all change quickly. We all have experi- are measured. It is recommended that the partition ences with, or know of, patients with pre-existing heart coefficients of all six gases be measured in each sub- and lung disease undergoing unrelated surgery and having ject. This is done by (a) equilibrating a sample of the a difficult recovery. Post-operative atelectasis and/or lung inert gases between blood and N in a closed syringe, infection causing a shunt and low VA/˙ Q˙ regions; use of 2 ˙ ˙ (b) measuring their levels in that N2, (c) repeating the PEEP causing high VA/Q regions; post-operative bleeding equilibration process with a fresh sample of N2,and reducing hemoglobin concentration; worsening cardiac (d) measuring the new, equilibrated, inert gas levels function reducing cardiac output; fever; and the need in the N2. The ratio of the inert gas concentrations to elevate and frequently change FIO2 are all common from the two successive equilibrations reflects, and problems in this situation, and MIGET has the capability is thus used to calculate, the partition coefficient [3]. of separating and quantifying the effects on arterial PO2 While these measurements by chromatography are not of every one of these phenomena. Separating what is difficult, they are undeniably painstaking and must be evolving lung disease from the effects of changes in done with great care and accuracy. extrapulmonary variables could have great clinical value, 5. The inert gas concentrations and partition coefficients yet this is difficult to do using simpler, conventional tools. together with ancillary data (arterial/mixed venous It would be useful to design and implement a clinical 36 P.D. Wagner trial of MIGET as an evaluative tool guiding therapy it would help to answer the question of whether such in the ICU to answer the question of whether the large detailed physiological information was of clinical value amount of information MIGET provides would lead to in critically ill patients who have multiple abnormalities more rational therapy and thereby improve morbidity with complex interactions that together determine arterial or mortality. While this would require substantial effort, oxygenation.
References 1. West JB (2008) Pulmonary patho- 8. Riley RL, Cournand A (1951) Analysis 16. Wagner PD (1977) A general approach physiology – the essentials. Lippincott of factors affecting partial pressures of to evaluation of ventilation/perfusion Williams & Wilkins, Baltimore oxygen and carbon dioxide in gas and ratios in normal and abnormal lungs. 2. Wagner PD, Saltzman HA, West JB blood of lungs: theory. J Appl Physiol Physiologist 20:18–25 (1974) Measurement of continuous 4:77–101 17. Wagner PD (1981) Estimation of distri- distributions of ventilation–perfu- 9. Briscoe WA (1959) A method for butions of ventilation/perfusion ratios. sion ratios: theory. J Appl Physiol dealing with data concerning uneven Ann Biomed Eng 9:543–556 36:588–599 ventilation of the lung and its effects 18. Wagner PD (1982) Calculation of the 3. Wagner PD, Naumann PF, Laravuso RB on blood gas transfer. J Appl Physiol distribution of ventilation/perfusion (1974) Simultaneous measurement 14:291–298 ratios from inert gas elimination data. of eight foreign gases in blood by 10. King TKC, Briscoe WA (1967) Bohr Fed Proc 41:136–139 gas chromatography. J Appl Physiol integral isopleths in the study of blood 19. Hammond MD, Hempleman SC (1987) 36:600–605 gas exchange in the lung. J Appl Physiol Oxygen diffusing capacity estimates de- 4. Wagner PD, Laravuso RB, Uhl RR, 22:659–674 rived from measured VA/Q distributions West JB (1974) Continuous distribu- 11. Kety SS (1951) The theory and appli- in man. Respir Physiol 69:129–147 tions of ventilation–perfusion ratios in cations of the exchange of inert gas at 20. West JB (1969) Ventilation/perfusion normal subjects breathing air and 100% the lungs and tissues. Pharmacol Rev inequality and overall gas exchange in O2. J Clin Invest 54:54–68 3:1–41 computer models of the lung. Respir 5. Evans JW, Wagner PD (1977) Limits 12. Farhi LE (1967) Elimination of inert Physiol 7:88–110 on VA/Q distributions from analysis gas by the lungs. Respir Physiol 3:1–11 21. Young I, Mazzone RW, Wagner PD of experimental inert gas elimination. 13. Yokoyama T, Farhi LE (1967) The (1980) Identification of functional lung J Appl Physiol 42:889–898 study of ventilation/perfusion ratio unit in the dog by graded vascular 6. Rahn H, Fenn WO (1955) A graph- distribution in the anesthetized dog embolization. J Appl Physiol Respirat ical analysis of the respiratory gas by multiple inert gas washout. Respir Environ Exercise Physiol 49:132–141 exchange. American Physiological Physiol 3:166–176 22. Wagner PD, López FA (1984) Gas chro- Society, Washington, DC 14. Lenfant C (1963) Measurement of matography techniques in respiratory 7. Riley RL, Cournand A (1949) “Ideal” ventilation/perfusion distribution with physiology. In: Otis AB (ed) Techniques alveolar air and the analysis of ventila- alveolar-arterial differences. J Appl in the life sciences. Elsevier Ireland, Co tion/perfusion relationships in the lung. Physiol 18:1090–1094 Clare, Ireland, pp 403/1–403/24 J Appl Physiol 1:825–847 15. Lenfant C, Okubo T (1968) Distribution function of pulmonary blood flow and ventilation/perfusion ratio in man. J Appl Physiol 24:668–677 Enrico Calzia Alveolar ventilation and pulmonary blood flow: Peter Radermacher ˙ the V˙A/Q concept
region and the blood that bypasses the alveolar compart- ments (i.e., shunt), the gas composition in each alveolus will determine the arterial blood gas values in direct de- pendence on both ventilation and perfusion. In lung re- gions where ventilation exceeds perfusion, the alveolar gas partial pressures will approach the inspired ones. In contrast, if perfusion exceeds ventilation, the alveolar gas composition will more closely resemble the compo- ˙ sition of mixed venous blood. Consequently, at a V˙A/Q ratio near unity, O2 and CO2 gas exchange is optimally ˙ balanced. Since alveoli with such an optimal V˙A/Q ratio are the main contributors to the achievement of “normal” arterial blood gas values they are called “ideal” alveoli. ˙ At V˙A/Q ratios exceeding the ideal value the gas compo- sition of each alveolus will approach that of inspired gas, ˙ at lower V˙A/Q ratios that of mixed venous blood. In reali- ˙ ty, the V˙A/Q ratio is slightly less than unity, because the respiratory quotient, which is the ratio of O2 absorbed to Given a stable cardiac output (CO) and inspiratory oxy- CO2 excreted, is usually less than unity. gen concentration (FIO2), any gas exchange abnormality leading to hypoxia or hypercapnia may be explained solely on the basis of an altered distribution of the venti- 2. Graphic analysis of pulmonary gas exchange: ˙ lation and perfusion (V˙A/Q) regardless of the underlying the PO2-PCO2 diagram disease [1]. The effects of a ventilation–perfusion mismatch on gas exchange are graphically described by the PO2–PCO2 dia- 1. The alveolus is the functional unit of the lung gram first introduced by Rahn and Farhi (Fig. 1) [3]. Since the PO2 and PCO2 in each alveolus is determined by ˙ The alveolus and the surrounding capillaries represent the V˙A/Q ratio, a line through all PO2–PCO2 value pairs the functional lung gas exchange unit. Diffusive gas can be drawn connecting two endpoints of mixed venous transport across the alveolar–capillary membrane is very blood and inspired gas composition. Each point on this ˙ rapid [2]. Even under pathologic conditions gas ex- line represents V˙A/Q values from 0 (representing per- change at the alveolar level is not limited by diffusion fused but not ventilated alveoli, thus corresponding to across the gas–blood barrier, but mainly by the interplay shunt areas) to ∞ (representing ventilated but not per- between gas transport to (and from) the alveolar space fused alveoli, thus corresponding to dead space). Theo- (ventilation, V˙A) and blood flow across the alveolar cap- retically, the most efficient gas exchange should be ex- illaries (perfusion, Q˙ ). End-capillary gas partial pressures pected in a perfectly homogeneous lung, with an overall ˙ exactly reflect alveolar gas composition. Therefore, since V˙A/Q value near unity. However, even in healthy subjects arterial blood is the sum of the blood from each alveolar a limitation in gas exchange is imposed by the inhomo-
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 37 DOI: 10.1007/978-3-642-01769-8_9, © Springer-Verlag Berlin Heidelberg 2009 38 E. Calzia and P. Radermacher
where Qs/Qt=shunt fraction or venous admixture, CaO2=arterial blood O2 content, CcO2=end-capillary O2 content, and CvO2=mixed venous blood O2 content. Since capillary O2 content cannot be measured direct- ly, it is assumed to equal ideal alveolar O2 content (CAIO2), which is estimated by the ideal alveolar O2 par- tial pressure (PAIO2) obtained by the simplified alveolar gas equation (2)
where PAIO2=“ideal” alveolar O2 partial pressure, PIO2=inspired O2 partial pressure, PaCO2=arterial blood CO2 partial pressure, and RQ=respiratory quotient. The accuracy of these formulas is limited by mainly Fig. 1 The PO2-PCO2 diagram of Rahn and Farhi graphically ex- plains the theoretical concepts of ventilation/perfusion distribution three factors. First, the calculation of CcO2 from PAIO2 and pulmonary gas exchange. (From [13], with permission) assumes equilibration of alveolar and end-capillary gas and ignores the impact that changes in pH and PCO2 may have on gas exchange. Second, although PaCO2 is pre- sumed to equal PAICO2, this assumption is incorrect when ˙ ˙ geneous distribution of the VA/Q values, mainly as a re- shunt causes PCO2 to increase more than PAICO2. And fi- sult of gravitational forces. In normal physiologic states, nally, the respiratory exchange ratio (RQ) is assumed to however, this inhomogeneity is fairly moderate, but it be 0.8, but may actually vary between 1.0 and 0.7 based substantially increases with disease. on metabolic activity and diet. Despite these limitations, however, these formulae are remarkably accurate, allow- ing the estimation of right-to-left shunt in the clinical ˙ ˙ 3. VA/Q mismatch is quantified by the setting. three-compartment model of ideal alveoli, shunt, In contrast to shunts, gas exchange abnormalities due and dead space to increased dead space ventilation result in partial ex- clusion of inspired gas from gas exchange. Thus, expired ˙ Assuming a perfectly homogeneous V˙A/Q distribution gas partial pressures are maintained closer to the inspired and no shunt, alveolar (=end capillary) and arterial gas ones. Commonly, the dead space fraction is calculated by partial pressures should be equal. Consequently, any al- the Bohr equation veolar-to-arterial PO2 or PCO2 differences reflect inhomo- ˙ (3) geneous V˙A/Q distribution and are used to quantify the ˙ ˙ VA/Q mismatch. Conceptually, as suggested by Riley and where V /V =dead space fraction, PaCO =arterial blood Cournand [4], alveolar gas exchange can be simplified to D T 2 CO2 partial pressure, and PECO2=mid-expired CO2 partial occurring within three types of alveoli: those with pressure. ˙ ˙ ˙ matched VA/Q (ideal), those with no Q (dead space), and Although this three-compartment model is useful in ˙ those with no VA (shunt). This “three-compartment” sim- calculating shunt and dead space, clearly, gas exchange plification is attractive because it allows one to quantify units can have local ventilation to perfusion ratios any- gas exchange abnormalities by the proportion of gas ex- where from 0 to ∞, and not just 0, 1, and ∞. However, change units in each compartment. the three-compartment model forces parts of the lung to Although “ideal” alveolar zones contribute to mini- be in one of these three compartments. Under normal mizing alveolar-to-arterial differences, blood from shunt resting conditions, this assumption is not so far off of re- perfusion zones joins blood coming from alveolar re- ality, because most alveolar regions are characterized by gions with gas values identical to mixed venous ones, ˙ ∞ V˙A/Q-values between 1 and 0.8, or very near 0 and re- thus increasing both alveolar-to-arterial O2 differences spectively. Experimentally, one may measure the exact and arterial CO levels. An unappreciated result of in- ˙ 2 V˙A/Q distribution of the entire lung using the multiple in- creased shunt fraction is the increase in arterial PCO2 as ert gas technique. However, the utility of this approach mixed venous CO2 passes the alveoli and mixes with the to bedside assessment of gas exchange abnormalities is arterial blood. Based on these considerations, the amount low because of its impracticality. of right-to-left shunt can be derived from the calculated gas content in capillary, arterial, and mixed venous blood using the equation (1) Alveolar ventilation and pulmonary blood flow 39
4. Hypoxia and hypercapnia are caused with attention paid to avoiding dynamic hyperinflation ˙ ˙ by severe VA/Q mismatching minimize dead space [6]. Prone positioning of the patient and interspacing spontaneous ventilatory efforts by caus- ˙ ˙ Both oxygenation and CO2 homeostasis may be consider- ing diaphragmatic contraction improve VA/Q matching. ˙ ably impaired by V˙A/Q mismatch, although usually only When one takes into account the effects of systemic hypoxia is referred to as the result of increased venous ad- blood flow on gas exchange, the interactions become more mixture, while hypercapnia is generally considered the re- complex again. The interactions between intra- and extra- sult of increased dead space ventilation or hypoventilation. pulmonary factors, such as changes in cardiac output, sys- However, if minute ventilation is fixed, as is the case during temic oxygen uptake, and mixed venous O2 saturation, can controlled ventilation, then increasing shunt fraction will directly alter arterial oxygenation and CO2 content inde- ˙ cause hypercarbia. In the awake, spontaneously breathing pendent of changes in V˙A/Q. For example, although intra- subject, CO2 elimination may be sufficiently maintained venous vasodilators usually increase intrapulmonary shunt through chemoreceptor feedback even in the presence of in patients with adult respiratory distress syndrome or car- ˙ low V˙A/Q alveoli, so that arterial CO2 remains normal. In diogenic pulmonary edema, the associated increase in car- contrast, due to the narrow limits imposed by hemoglobin diac output, especially in the heart failure group, may off- O2 saturation, blood O2 content cannot be increased by hy- set the increased shunt by increasing mixed venous O2 sat- perventilation, and is therefore more susceptible to be de- uration [7]. Thus, the resultant change in arterial oxygen- creased by increasing venous admixture. Obviously, how- ation cannot be predicted ahead of time [8]. Furthermore, ever, substantial hypercapnia will also result from hugely some intravenous vasodilators may affect CO2 elimination increased venous admixture exceeding the limits of com- through several mechanisms. They may impair CO2 elimi- pensation, especially if venous admixture is almost com- nation by increasing shunt fraction or increasing blood pletely caused by true shunt (e.g., atelectatic regions). flow and CO2 delivery to the lungs; also, if cardiac output does not increase in response of the intravenous adminis- tration of vasodilators, the intrathoracic blood volume may 5. Clinical implications decrease, thus increasing the amount of hypoperfused areas especially in apical lung zones [9]. Giving vasodilators by Beneficial effects of different recommended recruitment inhalation should minimize shunt because only ventilated and ventilation strategies for patients receiving mechani- lung units will receive the vasodilating agent. Thus, inhala- ˙ cal ventilation are generally explained by their impact of tional vasodilating therapy should improve V˙A/Q matching. ventilation to perfusion matching [5], even though the This has been shown to occur in patients with gas ex- precise interplay between lung mechanics, hemodynam- change abnormalities when treated with nitric oxide (NO) ˙ ics, and V˙A/Q distribution is complex. Preventing alveo- inhalation or aerosolized prostacyclin [10, 11]. The under- lar collapse by the use of continuous positive airway lying pathology seems to be crucially important in regard pressure (CPAP) and positive end-expiratory pressure to the effects on arterial oxygenation. While patients with (PEEP) minimizes shunt, as do recruitment maneuvers, adult respiratory distress syndrome or right heart failure whereas vasodilator therapy, including aerosolized bron- improve their gas exchange, inhaled vasodilators may chodilator therapy, by increasing blood flow to potential- worsen arterial oxygenation by inhibiting hypoxic vaso- ly underventilated lung units increases shunt and arterial constriction in patients with chronic obstructive pulmonary ˙ desaturation. This is the cause of hypoxemia following disease, since V˙A/Q mismatch in hypoventilated areas rath- bronchodilator therapy in severe asthmatics. Pressure- er than true shunt is the predominant cause of arterial hyp- limited ventilation and smaller tidal volume ventilation oxemia in such cases [12].
References
1. Radermacher P, Cinotti L, Falke KJ 3. Fahri LE (1966) Ventilation-perfusion 6. Ralph DD, Robertson HT, Weaver NJ, (1988) Grundlagen der methodischen relationship and its role in alveolar gas Hlastala MP, Carrico CJ, Hudson LD Erfassung von Ventilations/Perfusions- exchange. In: Caro CG (ed) Advances (1985) Distribution of ventilation and Verteilungsstörungen. Anaesthesist in respiratory physiology. Arnold, perfusion during positive end-expirato- 37:36–42 London, pp 148–197 ry pressure in the adult respiratory dis- 2. Piiper J, Scheid P (1981) Model for 4. Riley RL, Cournand A (1951) Analysis tress syndrome. Am Rev Respir Dis capillary-alveolar equilibration with of factors affecting partial pressures of 131:54–60 special reference to O2 uptake in hyp- oxygen and carbon dioxide in gas and oxia. Respir Physiol 46:193–208 blood of lungs. 4:77–101 5. Pappert D, Rossaint R, Slama K, Grüning T, Falke KJ (1994) Influence of positioning on ventilation-perfusion rela- tionships in severe adult respiratory dis- tress syndrome. Chest 106:1511–1516 40 E. Calzia and P. Radermacher
7. Rossaint R, Hahn SM, Pappert D, 9. Radermacher P, Huet Y, Pluskwa F, 12. Wagner PD, Dantzker DR, Dueck R, Falke KJ, Radermacher P (1995) Influ- Hérigault R, Mal H, Teisseire B, Clausen JL, West JB (1977) Ventila- ence of mixed venous PO2 and inspired Lemaire F (1988) Comparison of tion-perfusion inequality in chronic ob- O2 fraction on intrapulmonary shunt in ketanserin and sodium nitroprusside in structive pulmonary disease. J Clin patients with severe ARDS. J Appl patients with severe ARDS. Anesthesi- Invest 59:203–216 Physiol 78:1531–1536 ology 68:152–157 13. Calzia E, Radermacher P (2002) 8. Radermacher P, Santak B, Wüst HJ, 10. Rossaint R, Falke KJ, Lopez F, Slama Klinische Bedeutung von Ventila- Tarnow J, Falke KJ (1990) Prostacyclin K, Pison U, Zapol WM (1993) Inhaled tions/Perfusions-Beziehungen. In: for the treatment of pulmonary distress nitric oxide for the adult respiratory Eckart J, Forst H, Burchardi H (eds) syndrome: effects on pulmonary capil- distress syndrome. N Engl J Med Intensivmedizin, vol 3. Ecomed, lary pressure and ventilation-perfusion 328:399–405 Landsberg, pp 17/1–17/8 distributions. Anesthesiology 11. Walmrath D, Schneider T, Pilch J, 72:238–244 Grimminger F, Seeger W (1993) Aero- solised prostacyclin in adult respiratory distress syndrome. Lancet 342:961–962 Robert Rodr guez-Roisin Mechanisms of hypoxemia Josep Roca
precise estimates of the distributions of alveolar ventila- tion and pulmonary perfusion (VA/Q) and their relation- ships, there is no need to change the FIO2 during mea- surements, hence avoiding variations in the pulmonary vascular tone, and it facilitates the unraveling of the ac- This research was supported by the Red Respira-ISCIII-RTIC-03/ tive interplay between intrapulmonary, namely VA/Q 11 and the Comissionat per a Universitats i Recerca de la imbalance, intrapulmonary shunt and limitation of alve- Generalitat de Catalunya (2001 SGR00386). R.R.-R. holds a career scientist award from the Generalitat de Catalunya. olar to end-capillary O2 diffusion, and extrapulmonary (i.e., FIO2, total ventilation, cardiac output and oxygen consumption) factors governing hypoxemia [2]. The cardinal gas exchange features under which the lung operates that uniquely determine the PO2 and PCO2 in each gas exchange unit of the lung are the VA/Q ratio, the composition of the inspired gas, and the mixed venous blood gas composition [3]. Each of these three factors may play key role influencing oxygenation. For example, the major mechanism of arterial hypoxemia in ALI/ARDS is intrapulmonary shunt (zero VA/Q ratios) induced by the Introduction presence of collapsed or flooded alveolar units, whereas in COPD the primary mechanism of hypoxemia is VA/Q A fundamental aspect of cardiopulmonary homeostasis is mismatching. the adequate delivery of oxygen to meet the metabolic demands of the body. Cardiac output, O2-carrying ca- pacity (i.e., hemoglobin concentration and quality), and Effect of breathing oxygen on oxygenation arterial PO2 (PaO2) determine O2 transport. Relevant to this discussion, arterial hypoxemia commonly occurs in In ALI/ARDS, as FIO2 increases, PaO2 increases as long patients with acute respiratory failure (ARF). If arterial as the amount of shunt is limited. The greater the degree hypoxemia is severe enough, it is not compatible with of shunt, the less PaO2 increases. In contrast, in COPD, in life. The two primary causes of ARF are acute lung injury which the prime mechanism of hypoxemia is VA/Q mis- (ALI)/acute respiratory distress syndrome (ARDS) and matching, the response to high FIO2 levels is broadly chronic obstructive lung disease (COPD). Although the similar irrespective of disease severity. With moderate treatment for arterial hypoxemia always includes in- VA/Q imbalance PaO2 increases almost linearly as FIO2 is creases in the fractional inspired O2 concentration (FIO2), increased. In severely acute COPD the degree of very low the degree to which patients’ PaO2 improves and the need VA/Q ratios resembles shunt; the increase in PaO2 in re- for adjuvant therapies differ markedly between these two sponse to increasing FIO2 is only slightly limited, be- groups of disease processes. The mechanisms by which coming less responsive to increases FIO2. arterial hypoxemia occurs in ALI/ARDS and COPD have Importantly, FIO2 can also alter VA/Q balance through been characterized using the multiple inert gas elimina- two additional mechanisms: hypoxic pulmonary vaso- tion technique (MIGET) approach [1]. MIGET provides constriction (HPV) and reabsorption atelectasis (RA).
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 41 DOI: 10.1007/978-3-642-01769-8_10, © Springer-Verlag Berlin Heidelberg 2009 1018 42 R.Rodríguez-Roisin and J. Roca
One of the main means by which the normal lung adjusts to low regional VA is to induce vasoconstriction of the associated pulmonary vasculature to redirect perfusion away from nonventilated or under ventilated alveolar units. Thus HPV minimizes VA/Q inequality, limiting the decrease in PaO2 that would have occurred if such re- distribution of blood flow had not occurred. One of the best VA/Q indicators of the presence of HPV, as measured by MIGET, is the behavior of the area with normal and low VA/Q ratios, reflected in the dispersion of pulmonary blood flow. In sequential measures one sees a significant increase in the latter VA/Q descriptor while breathing 100% O2. By contrast, shunt and the dispersion of alve- olar ventilation that incorporates areas with normal and high VA/Q ratios remain unchanged during HPV release. Breathing 100% O2 (FIO2=1.0) can induce intrapul- monary shunt because lung units with low inspired VA/Q ratios, termed “critical” VA/Q ratios, can result in absent expired ventilation because all the inflated gas is ab- sorbed. This results in alveolar denitrogenation, allowing complete gas resorption with atelectasis (RA) to develop spontaneously [4]. These critical VA/Q units are depen- dent on the FIO2, increasing both their potential area of collapse and rate of collapse considerably as FIO2 ap- proaches 1.0. Alternatively, these critical units may re- main open despite increasing FIO2 levels if functional residual capacity and tidal volume are increased, owing to alveolar interdependence. This is the rationale for using positive end-expiratory pressure (PEEP) and larger tidal volumes in patients with ALI/ARDS to prevent RA. Both RA and HPV and can be observed, respectively, in the responses of patients with ALI/ARDS and COPD Fig. 1 Index of oxygenation (PaO2/FIO2), intrapulmonary shunt (expressed as percentage of cardiac output), and dispersion of needing mechanical support who are given an FIO2 of 1.0 pulmonary blood flow (log SDQ, dimensionless) while breathing [5] (Fig. 1). Intrapulmonary shunt increases moderately 100% O2. In ALI/ARDS (open circles) both PaO2/FIO2 and log then remains stable for at least 30 min in ALI/ARDS SDQ remain essentially unchanged while shunt increases signifi- cantly, indicating RA; note that after reinstatement of maintenance patients given an FIO2 of 1.0. In contrast, in COPD pa- tients the dispersion of pulmonary blood flow, one of the FIO2 shunt still remains increased. In COPD exacerbation (closed squares) PaO2/FIO2 and log SDQ substantially increase while the most common VA/Q indicators in COPD, further in- very modest shunt unvaried, indicating HPV release (by permission creases to an FIO2 of 1.0 while the modest levels of in- from [5]) trapulmonary shunt remain unchanged, a response that strongly suggests HPV release. Both responses to pure O2 breathing are accompanied with increases in PaO2, which On the other hand, the changes observed in COPD during are much more prominent in patients with COPD. hyperoxia suggest that inhibition of HPV is the primary The increase in intrapulmonary shunt in ALI/ARDS is process. Interestingly, gas exchange abnormalities in both likely due to RA. If cardiac output increases as part of the entities take place in the absence of measurable changes sympathetic response to arterial hypoxemia, one may also in pulmonary hemodynamics, suggesting that regional see a parallel increase in mixed venous PO2 owing to blood flow redistribution can have relevant effects on gas increased O2 delivery. This can offset the increased shunt exchange despite minimal changes in pulmonary arterial fraction minimizing the decrease in PaO2. The deleterious pressure and blood flow. effects of RA on pulmonary gas exchange may be en- If VA were to decrease or dead space to increase, ar- hanced by the mechanical trigger imposed on peripheral terial PCO2 (PaCO2) would increase. Hyperoxia-induced airways by ventilator support. Indeed, the repeated increases in PaCO2 in response to FIO2 1.0 breathing are opening and closing of distal airways and/or the overex- more notable in ALI/ARDS than in COPD and can be pansion of closed alveolar units with abnormally high attributed almost completely to the parallel increases in shear stresses may result in more inflammatory lung dead space, with a marginal role of the Haldane effect changes, aggravating the initial mechanical stress injury. (i.e., decreasing PaO2 increases PaCO2 off-loading from 1019 Mechanisms of hypoxemia 43 hemoglobin). Conceivably, the increased dead space in- injurious increases in intrapulmonary shunt. Conceivably, dicates redistribution of pulmonary blood flow from high the alveolar recruitment induced by recruitment effi- VA/Q areas either to regions with no ventilated (shunt) ciently redistributes pulmonary blood flow to regions with alveolar units in ALI/ARDS or to those poorly ventilated alveolar units with normal VA/Q balance. A parallel with low VA/Q areas in COPD. This process, however, finding in protective lung ventilation is the significant has not been definitely characterized. An alternative and/ increase in physiological dead space, possibly related to or complementary mechanism in ALI/ARDS for the ob- the combined effects of a decreased alveolar ventilation served increase in PaCO2 could be overexpansion of re- and increased functional residual capacity. Thus the ap- maining normal lung zones provoked by RA, but in plication of a protective ventilator support combining low COPD by bronchodilation secondary to the hypercapnia. tidal volumes and high PEEP levels represent a beneficial ventilator strategy in ALI/ARDS both in terms of mini- mizing lung stress and augmenting gas exchange. Protective ventilator support Protective ventilator support with low tidal volume and Summary high PEEP levels has become the preferred approach to decrease the impact of ventilator-associated lung injury The primary mechanisms leading to arterial hypoxemia in [6]. This protective support causes a substantial im- ARF secondary to COPD exacerbations and ALI/ARDS provement in gas exchange by increasing PaO2 and de- are VA/Q imbalance and intrapulmonary shunt while the creasing intrapulmonary shunt. However, this strategy of conditions that uniquely determine the PO2 and PCO2 in increased PEEP and small tidal volumes is often accom- gas exchange units of the lung are the VA/Q ratio and the panied by hypercapnia. Hypercapnia induces both vaso- composition of inspired gas and mixed venous blood. This dilatation and increased cardiac output, both of which is why the extrapulmonary factors governing hypoxemia, increase intrapulmonary shunt and potentially impair ar- i.e., FIO2, total ventilation, cardiac output, and O2 con- terial oxygenation. The principal factor to explain the sumption, always need to be considered. The increase in observed reduction in shunt in protective lung ventilation intrapulmonary shunt characteristically shown in ALI/ is the recruitment of previously collapsed alveoli, as ARDS patients breathing high FIO2 levels is secondary to shown by the close correlation between the decreased the development of RA, whereas in COPD patients it is intrapulmonary shunt and the amount of PEEP-induced usually due to withdrawal of HPV, reflected by further lung volume recruitment. Furthermore, the parallel in- VA/Q worsening only without parallel increases in intra- crease in cardiac output caused by the hypercapnia-in- pulmonary shunt. duced vasodilatation does not induce any proportional
References
1. Glenny R, Wagner PD, Roca J, 3. West JB (1977) State of the art: 6. Mancini M, Zavala E, Mancebo J, Rodriguez-Roisin R (2000) Gas ex- Ventilation-perfusion relationships. Fernandez C, Barbera JA, Rossi A, change in health: rest, exercise, and Am Rev Respir Dis 116:919–943 Roca J, Rodriguez-Roisin R (2001) aging. In: Roca J, Rodriguez-Roisin R, 4. Dantzker DR, Wagner PD, West JB Mechanisms of pulmonary gas ex- Wagner PD (eds) Pulmonary and pe- (1975) Instability of lung units with low change improvement during a ripheral gas exchange in health and VA/Q ratios during O2 breathing. J Appl protective ventilatory strategy in disease. Dekker, New York, pp 121– Physiol 38:886–895 acute respiratory distress syndrome. 148 5. Santos C, Ferrer M, Roca J, Torres A, Am J Respir Crit Care Med 164: 2. Rodriguez-Roisin R, Wagner PD (1990) Hernandez C, Rodriguez-Roisin R 1448–1453 Clinical relevance of ventilation-perfu- (2000) Pulmonary gas exchange re- sion inequality determined by inert gas sponse to oxygen breathing in acute elimination. Eur Respir J 3:469–482 lung injury. Am J Respir Crit Care Med 161:26–31 Amal Jubran Pulse oximetry
clinicians distinguish an artifactual signal from the true signal (Fig. 1). The accuracy of commercially available oximeters in critically ill patients has been validated in several studies [3]. Compared with the measurement standard (multi- wavelength CO oximeter), pulse oximeters have a mean difference (bias) of less than 1% and a standard deviation (precision) of less than 2% when SaO2 is 90% or above [4]. While pulse oximetry is accurate in reflecting one- point measurements of SaO2, it does not reliably predict changes in SaO2 [4]. Moreover, the accuracy of pulse oximeters deteriorates when SaO2 falls to 80% or less. In critically ill patients, poor agreement between the oxim- Introduction eter and a CO oximeter has been observed, with bias the
Continuous monitoring of arterial blood saturation using pulse oximetry has become the standard of care in the ICU. With the proliferation of pulse oximeters, episodic hypoxemia is detected much more commonly than pre- viously suspected. By alerting the clinician to the pres- ence of hypoxemia, pulse oximeters can lead to a more rapid treatment of serious hypoxemia and possibly avoid serious complication. Moreover, pulse oximetry can re- duce arterial blood gas analysis and potentially decrease health care costs [1].
Principles of pulse oximetry
Pulse oximeters determine oxygen (O2) saturation by measuring light absorption of arterial blood at two spe- cific wavelengths, 660 nm (red) and 940 nm (infrared) [2]. The ratio of absorbencies at the wavelengths is then calibrated empirically against direct measurements of Fig. 1 Common pulsatile signals on a pulse oximeter. Top panel arterial blood oxygen saturation (SaO2), and the resulting Normal signal showing the sharp waveform with a clear dicrotic calibration curve is used to generate the pulse oximeter’s notch. Second panel Pulsatile signal during low perfusion showing a typical sine wave. Third panel Pulsatile signal with superimposed estimate of arterial saturation (SpO2). In addition to the noise artifact giving a jagged appearance. Lowest panel Pulsatile digital read-out of O2 saturation, most pulse oximeters signal during motion artifact showing an erratic waveform. (From display a plethysmographic waveform, which can help [1])
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 45 DOI: 10.1007/978-3-642-01769-8_11, © Springer-Verlag Berlin Heidelberg 2009 2018 46 A. Jubran ranging from 12% to 18%, and oximetry tends system- perfusion and motion, the ability to track changes in atically to underestimate SaO2 when it is 80% or less. SpO2 and reduce nuisance alarms was improved with this technology [3].
Limitations of pulse oximetry Interference from substances Oximeters have a number of limitations which may lead to inaccurate readings [1]; these are presented below. Dyshemoglobins
Pulse oximeters employ only two wavelengths of light Physiological limitations and thus can distinguish only two substances, oxyhemo- globin and reduced hemoglobin. Accordingly, elevated Oxyhemoglobin dissociation curve carboxyhemoglobin and methemoglobin levels can cause inaccurate oximetry readings [1]. Pulse oximeters measure SaO2, which is physiologically related to arterial oxygen tension (PaO2) according to the oxyhemoglobin dissociation curve. Because the dissoci- Intravenous dyes ation curve has a sigmoid shape, oximetry is relatively insensitive in detecting the development of hypoxemia in Intravenous dyes such as methylene blue, indocyanine patients with high baseline levels of PaO2. green, and indigo carmine can cause falsely low SpO2 readings, an effect that persists for up to 20 min.
Limitation in the signal processing Skin pigmentation and other pigments Ambient light Inaccurate oximetry readings have been observed in Although pulse oximeters correct for ambient light, pigmented patients. In critically ill patients, a bias of more falsely low SpO2 readings have been reported with fluo- than 4% has been observed to occur more frequently in rescent and xenon arc surgical lamps. Wrapping the probe black (27%) than in white patients (11%). Nail polish, if with an opaque shield can minimize this effect. blue, green, or black, causes inaccurate SpO2 readings; however, mounting the oximeter probe sideways allevi- ates the problem with nail polish. Acrylic nails do not Low perfusion interfere with readings.
Pulse oximetry depends on satisfactory arterial perfusion of the skin, and thus low cardiac output, vasoconstriction, Limited knowledge of technique or hypothermia can make it difficult for a sensor to dis- tinguish the true signal from background noise. In cardiac Many users have only a limited understanding of pulse surgery patients experiencing hypothermia and poor per- oximetry. One survey revealed that 30% of physicians fusion, only 2 of 20 oximeters (Criticare CSI 503, Datex and 93% of nurses thought that the oximeter measured Satlite) provide measurements within €4% of the CO PaO2. A more recent audit demonstrated that less than oximeter value. 50% of nurses and physicians were able to identify that motion artifact, arrhythmias, and nail polish can affect the accuracy of pulse oximeter [6]. Motion artifact
The occurrence of motion artifacts continues to be a Clinical applications significant source of error and false alarms. In 235 sur- gical patients managed in the ICU, 67% of pulse oxim- Detection of hypoxemia eter alarms were false [5]. An innovative technological approach, termed Masimo signal extraction technology, With the introduction of pulse oximetry hypoxemia (de- was introduced to extract the true signal from artifact due fined as an SpO2 value less than 90%) is detected more to noise and low perfusion. When tested in 50 postop- often in critically ill patients. Moreover, myocardial erative patients, the pulse oximeter’s alarm frequency ischemia (defined as angina or ST segment depression) in was decreased twofold with the new system vs. a con- postoperative patients is less common in patients moni- ventional oximeter. When tested under conditions of low tored with pulse oximetry than those without oximetry [7]. 2019 Pulse oximetry 47
Assessing pulmonary gas exchange was to be of definite benefit in the management of 7 of 20 patients, 5 of whom survived. Pulse oximeters measure SaO2, which is physiologically related to PaO2. In critically ill patients receiving me- chanical ventilation, changes in SpO2 may not accurately Screening test for cardiopulmonary disease reflect changes in PaO2 and may in fact be in an opposite direction to the change in PO2. Decisions in therapy made The potential usefulness of pulse oximetry as a screening on the basis of SpO2 alone can also differ from those tool for cardiopulmonary disease that could supplement or based on PO2. Accordingly, caution is required when supplant respiratory rate as a “pulmonary vital sign” was making decisions in critically ill patients based solely on investigated in patients managed in the emergency de- pulse oximetry. While pulse oximetry is a suitable way of partment [9]. An inverse but weak relationship (correla- measuring arterial oxygenation, it does not assess venti- tion coefficient 0.16) was observed between SpO2 and lation. Indeed, measurements of SpO2 have been shown to respiratory rate. Overall only one-third of patients with an be inaccurate in assessing abnormal pulmonary gas ex- SpO2 value below 90% would exhibit an increase in change, defined as an elevated alveolar-arterial O2 dif- respiratory rate. While pulse oximetry could be used as a ference [1]. screening tool for cardiopulmonary disease, there are no data to suggest that decisions based on SpO2 improve outcome over decisions based on respiratory rate. Titration of fractional inspired oxygen concentration
Pulse oximetry can assist with titration of fractional in- Screening for respiratory failure in asthma spired oxygen concentration (FIO2) in ventilator-depen- dent patients, although the appropriate SpO2 target de- Pulse oximetry has been evaluated as a means of pends on a patient’s pigmentation. In white patients, an screening for respiratory failure in patients with severe SpO2 target value of 92% predicts a satisfactory level of asthma [10]. Respiratory failure occurred in only 4% of oxygenation, whereas black patients required an SpO2 the patients with an SaO2 value higher than 92%. The target of 95%. In patients with severe acute respiratory investigators concluded that an SpO2 higher than 92% in distress syndrome, an SpO2 target of 88–90% is accept- this setting suggests that respiratory failure is unlikely and able in order to minimize oxygen toxicity. therefore arterial blood gas measurements are unneces- sary. Interestingly, this threshold value of 92% is the same target value that predicted reliably a satisfactory level of Blood pressure measurements oxygenation during titration of FIO2 in ventilator-depen- dent patients. In pulse oximeters that display a pulsatile waveform, systolic blood pressure can be measured by noting the reappearance of the pulsatile waveform during cuff de- Pulmonary embolus flation or the waveform disappearance during slow cuff inflation (Fig. 1). In healthy volunteers, good agreement In patients with documented pulmonary embolism the (i.e., bias <1.0 mmHg) was obtained when the average of room air SpO2 level may be an important predictor of oximetry based-systolic pressure estimates at the disap- death; mortality was found in one study to be 2% in pa- pearance and reappearance of the waveform were com- tients with pulse oximetry of 95% or higher vs. 20% with pared with Korotokoff sound pressures and noninvasive pulse oximetry less than 95% [11]. When the threshold equipment blood pressures. value was prospectively evaluated in 119 patients, 10 of whom developed hospital complications, SpO2 less than 95% had a sensitivity of 90%, specificity of 64%, and Cardiopulmonary arrest overall diagnostic accuracy of 67%. Although the number of patients with complications were low, these data sug- The usefulness of pulse oximetry as part of the first-line gest that pulse oximetry may be useful in predicting resuscitation equipment at the site of a cardiopulmonary outcome in patients with pulmonary embolus. arrest was assessed in 20 patients [8]. A signal in which In summary, pulse oximetry is probably one of the the pulse rate on the oximeter was correlated with the most important advances in respiratory monitoring. The electrocardiogram or chest compression rate was ob- major challenge facing pulse oximetry is whether this served in the three patients who suffered only a respira- technology can be incorporated effectively into diagnostic tory arrest and in only 4 of 17 patients who suffered a and management algorithms that improve the efficiency cardiac arrest. The physicians judged the pulse oximeter of clinical management in the ICU. 2020 48 A. Jubran
References
1. Jubran A (1998) Pulse oximetry. 5. Lutter NO, Urankar S, Kroeber S 8. Spitall MJ (1993) Evaluation of pulse In: Tobin MJ (ed) Principles and prac- (2002) False alarm rates of three third- oximetry during cardiopulmonary re- tice of intensive care monitoring. generation pulse oximeters in PACU, suscitation. Anaesthesia 48:701–703 McGraw-Hill, New York, pp 261–287 ICU and IABP patients. Anesth Analg 9. Mower WR, Sachs C, Nicklin EL, 2. Wukitisch MW, Peterson MT, Tobler 94:S69–S75 Safa P, Baraff LJ (1996) A comparison DR, Pologe JA (1988) Pulse oximetry: 6. Howell M (2002) Pulse oximetry: an of pulse oximetry and respiratory rate in analysis of theory, technology, and audit of nursing and medical staff un- patient screening. Respir Med 90:593– practice. J Clin Monit 4:290–301 derstanding. Br J Nurs 11:91–197 599 3. Emergency Care Research Institute 7. Moller JT, Pedersen T, Rasmussen LS, 10. Carruthers DM, Harrison BDW (1995) (2003) Next-generation pulse oximetry. Jensen PF, Pedersen BD, Ravlo O, Arterial blood gas analysis or oxygen Health Devices 32:49–103 Rasmussen NH, Espersen K, saturation in the assessment of acute 4. Van de Louw A, Cracco C, Cerf C, Harf Johannessen NW, Cooper JB (1993) asthma. Thorax 50:186–188 A, Duvaldestin P, Lemaire F, Brochard Randomized evaluation of pulse oxim- 11. Kline JA, Hernandez-Nino J, Newgard L (2001) Accuracy of pulse oximetry in etry in 20,802 patients. I. Design, de- CD, Cowles DN, Jackson RE, Courtney the intensive care unit. Intensive Care mography, pulse oximetry failure rate DM (2003) Use of pulse oximetry to Med 27:1606–1613 and overall complication rate. predict in-hospital complications in Anesthesiology 78:436–444 normotensive patients with pulmonary embolism. Am J Med 115:203–208 Andreas Bacher Effects of body temperature on blood gases
Abstract Background: Changes in and potentially harmful interpreta- body temperature have important tions and decisions in the clinical impact on measurements of blood setting. The following article eluci- gases. In blood gas analyzers the dates alterations in monitoring of samples are always kept constant at a blood gases and oxyhemoglobin sat- temperature of exactly 37 C during uration (SO2) that occur during the measurements, and therefore re- changes in body temperature. sults are not correct if body temper- ature differs from 37 C. Objective: Keywords Blood gas monitoring · Lack of knowledge of the effects of Oxyhemoglobin saturation · body temperature on results of blood Hypothermia · Hyperthermia gas monitoring may lead to wrong
Blood gas monitoring portion of CO2 again contributes to PCO2. The measured PCO2 of this blood sample is the same as at 37 C. Blood gases (oxygen and carbon dioxide) are usually re- Hypothermia reduces the metabolic rate and the rate of ported as partial pressures (gas tensions) since according CO2 production. To hold the arterial CO2 content constant to Henry’s law the partial pressure of a gas is proportional during cooling it is necessary to reduce CO2 elimination to its concentration at a given temperature and pressure. (i.e., by reducing minute ventilation in anesthetized pa- However, as temperature decreases, the solubility of oxy- tients) equivalently to the decrease in CO2 production. If gen and carbon dioxide in blood or any other fluid in- this is performed, arterial carbon dioxide tension (PaCO2) creases, which means that the relationship of partial pres- measured in a blood gas analyzer at 37 C remains at the sure to the total content of oxygen or carbon dioxide in same level as during normothermia. Blood gas analyzers the fluid changes. are usually equipped with algorithms that enable the true PaCO2 to be calculated at the actual body temperature (Fig. 1) [1]. True PaCO2 corrected for current body Carbon dioxide temperature is of course lower during hypothermia than the PaCO2 value measured at 37 C. The difference be- If blood containing a given amount of carbon dioxide at a tween these two values corresponds to the increase in CO2 certain tension (PCO2) at 37 C is cooled, with the pos- solubility during cooling. The concept of CO2 manage- sibility to equilibrate with air, the total content of CO2 in ment in which the PCO2 obtained by measurement at this blood sample remains constant, whereas PCO2 de- 37 C is kept constant at 40 mmHg regardless of current creases due to the increased proportion of dissolved CO2 body temperature is called alpha-stat. If the PCO2 value at lower temperature. Since the PCO2 of air or any in- corrected for current body temperature is held constant spired gas mixture is almost zero, no additional molecules during cooling at the same level as during normothermia of CO2 diffuse into the blood. If a blood sample is re- (37 C), the total amount of CO2 increases during hypo- warmed to 37 C in a blood gas analyzer under vacuum- thermia because of the constant PaCO2 and the increased sealed conditions, the previously increased dissolved pro- proportion of CO2 that is soluble in blood. In this case
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 49 DOI: 10.1007/978-3-642-01769-8_12, © Springer-Verlag Berlin Heidelberg 2009 25 50 A. Bacher
Fig. 1 Dashed line True (tem- perature corrected) PCO2 dur- ing changes in body tempera- ture. PCO2 measured at 37 C remains constant at 40 mmHg. Solid line PO2 measured at 37 C during changes in body temperature. True (temperature corrected) PO2 remains constant at 85 mmHg
CO2 elimination is not only reduced by the amount of proximately 159 mmHg. If an increased amount of O2 decreased CO2 production but additionally by the in- molecules dissolve in blood during cooling, PO2 does not creased amount of CO2 dissolved in blood during hypo- decrease as does PCO2 because O2 from the environment thermia. The latter concept of CO2 management is called and from alveolar gas diffuse into blood, and the PO2 pH-stat. values equilibrate between these two compartments. The O2 content in blood thus thereby increases. This sche- matic model is in fact representative of that which occurs pH in the alveoli and capillaries of the lungs. If we take a blood sample at hypothermia and put it into a blood gas pH varies with CO2 during variations in body tempera- analyzer, this sample is rewarmed to 37 C under vacuum- ture. If alpha-stat CO2 management is applied, pH that sealed conditions. The previously increased proportion of is not corrected for current body temperature remains dissolved O2 then contributes to PO2, which thereby in- constant. True pH increases since true PaCO2 has de- creases. Thus PO2 values that are not corrected for current creased during hypothermia. If pH-stat CO2 management body temperature are higher than during normothermia is applied, both true PaCO2 and true pH remain constant (Fig. 1) [1]. Temperature-corrected PO2 is equal to the during cooling, and pH that is not corrected for current values obtained during normothermia. body temperature decreases. The amount of true pH The clinical relevance of these effects is clear: When- change resulting from a change in body temperature may ever we measure arterial oxygen tension (PaO2) and do be calculated as follows: pHT=pH37 [0.0146+0.0065 not correct these values for current (hypothermic) body (pH37 7.4)](T 37), where pHT is true pH at current body temperature, true PaO2 does not increase during cooling, temperature, pH37 is pH at 37 C, and T is current body but the observed increase in measured PaO2 is due only to temperature ( C). the fact that body temperature and the temperature at which the sample is analyzed differ. Considering that the gradient between PaO2 and cellular (mitochondrial) PO2 Oxygen is the driving force that maintains normal O2 extraction by the tissue, it would be a mistake to adapt inspired The effects of temperature changes on oxygen tension oxygen fraction (FIO2) to the uncorrected, apparently (PO2) differ markedly from those on PCO2. The principal high values of PaO2 obtained during hypothermia. To effect that hypothermia leads to increased solubility of O2 maintain true PaO2 in the normal range the measured in blood is the same as for CO2. Therefore during hypo- PaO2 should always be corrected for current body tem- thermia one could expect a lower PO2 for a given amount perature in hypothermic patients. of oxygen. However, in contrast to CO2, the oxygen Apart from the effects of increased O2 solubility there content of room air or any inspired gas mixture and of is another effect that slightly affects PaO2 during hypo- alveolar gas is never zero. The PO2 of room air at stan- thermia. Since PaO2 is related to the alveolar oxygen dard atmospheric pressure (patm) of 760 mmHg is ap- tension (PAO2), true PaO2 might indeed increase a very 26 Effects of body temperature on blood gases 51
Table 1 An example of chang- BT 37 C BT 30 C es in blood gases during alpha- stat and pH-stat regimens as Alpha-stat body temperature (BT) de- PCO2 40 After rewarming to 37 C in blood gas analyzer 40 creases from 37 C to 30 C (mmHg) True value (corrected): 29 PO2 (mmHg) 85 After rewarming to 37 C in blood gas analyzer 117 True value (corrected) 85 pH 7.40 After rewarming to 37 C in blood gas analyzer 7.40 True value (corrected) 7.50 pH-stat PCO2 40 After rewarming to 37 C in blood gas analyzer 40 (mmHg) True value (corrected) 56 PO2 (mmHg) 85 After rewarming to 37 C in blood gas analyzer 117 True value (corrected): 85 pH 7.40 After rewarming to 37 C in blood gas analyzer 7.30 True value (corrected) 7.40
Fig. 2 Leftward shift of the oxyhemoglobin dissociation curve 2396.1674, a7= 67.104406). Oxygen tension is measured at current caused by hypothermia. Temperature (T) is 30 C for the dotted conditions of pH, PCO2, and T. Then it must be converted into a PO2 curve. The true carbon dioxide tension (PCO2)of27mmHgand that would be obtained at a pH of 7.40, a PCO2 of 40 mmHg, and T pH of 7.5 at 30 C correspond to a PCO2 of 40 mmHg and pH of of 37 C. The equation to convert the actual PO2 to this virtual PO2 2 0.0024 (37 T)+0.40 (pH 7.40)+0.06[log10 7.4 at 37 C. Oxyhemoglobin saturation (SO2)=100(a1PO2+a2PO2 + is: [PO virtual]=[PO actual] 10 3 4 2 3 4 2 2 a3PO2 +PO2 )/(a4+a5PO2+a6PO2 +a7PO2 +PO2 ). The seven co- (40) log10 (PCO2)]. Then the equation for the standard oxyhemoglobin efficients (a1–a7) were determined by a least-squares fitting of dissociation curve is again applied to predict actual SO2 the equation to paired values of PO2 and SO2 (a1= 8532.2289, a2=2121.4010, a3= 67.073989, a4=935960.87, a5= 31346.258, a6= small amount during moderate hypothermia if pulmonary 47 mmHg, at 30 C approx. 31 mmHg, and at 15 C ap- gas exchange conditions and the gradient between PaO2 prox. 12 mmHg. At FIO2 of 0.21, patm of 760 mmHg, and PAO2 (aADO2) remain constant. PAO2 depends on PaCO2 of 40 mmHg, and RQ of 0.8, PAO2 is 99.7 mmHg FIO2, patm, water vapor pressure (pH2O), PaCO2, and the at 37 C, 103.1 mmHg at 30 C, and 107.1 mmHg at 15 C. respiratory quotient (RQ=CO2 production rate/O2 con- Table 1 illustrates changes in blood gases during alpha- 1 sumption rate). PAO2=FIO2(patm-pH2O) PaCO2 RQ . stat and pH-stat regimens as body temperature decreases Water vapor pressure decreases exponentially with a from 37 C to 30 C. decrease in temperature. At 37 C pH2O is approx. 27 52 A. Bacher
Effects of hypothermia on SO2 Oxygen consumption (VO2) decreases during hypo- thermia. The relationship between cerebral VO2 and Arterial (SaO2), mixed venous (SvO2), and jugular bulb temperature has been well investigated [3, 4]. This is de- (SjvO2) oxyhemoglobin saturation are strongly affected termined by the factor Q10: Q10=cerebral VO2 at Tx/ by changes in body temperature. The curve of the rela- cerebral VO2 at Ty, whereTx Ty=10 C. Q10 is not con- tionship between SO2 and PO2, i.e., the oxyhemoglobin stant over the entire temperature range that is clinically dissociation curve, is S-shaped. Hypothermia, a decrease possible [3, 4]. In dogs Q10 is approx. 2.2 when in the intracellular concentration of 2,3-diphosphoglyc- T=37 27 C, approx. 4.5 when T=27 14 C, and approx. erate in erythrocytes, a decrease in PCO2, and an increase 2.2 when T=13 7 C [3, 4]. Cerebral VO2 at a given in pH cause a leftward shift of the oxyhemoglobin dis- temperature may be calculated as follows: VO2 at Ty= (Ty Tx)/10 sociation curve, which means that at a given PO2 the SO2 VO2 at Tx Q10 value is higher than under normal conditions. The corre- Because hypothermia leads to a leftward shift of the sponding SO2 to a given PO2 may be calculated with oxyhemoglobin dissociation curve and to a decrease in sufficient accuracy (Fig. 2) [2]. Due to the S-shape of the VO2, SvO2 should significantly increase during cooling, oxyhemoglobin dissociation curve changes in SO2 caused particularly if O2 delivery remains unchanged. This has in by a leftward shift are more pronounced when PO2 is in fact been found in hypothermic (32 C) patients under the medium range. Therefore hypothermia leads to an endogenous circulation, i.e., without the use of extracor- increase in SvO2 and SjvO2 rather than SaO2 because poreal circulation [5]. normal SaO2 is already close to 100%. Hypothermia in- In conclusion, variations in body temperature signifi- hibits oxygen release from hemoglobin in the capillaries cantly affect the results of important and frequently used (i.e., oxygen extraction) without providing any benefits monitoring techniques in intensive care, anesthesia, and with regard to increasing SaO2. In other words, a much emergency medicine. The knowledge of physical and lower tissue PO2 would be required to obtain the same technical changes during hypothermia or hyperthermia is degree of oxyhemoglobin desaturation in the capillary. necessary to avoid pitfalls in monitoring of blood gases, The total amount of O2 flow from the capillary to the cells SO2, and etCO2. Ignoring these effects may lead to harm- and mitochondria would then decrease because the driv- ful and incorrect conclusions derived from our measure- ing force of O2 diffusion, i.e., the gradient between mi- ments in the clinical setting as well as for scientific pur- tochondrial PO2 and capillary or tissue PO2 is reduced. poses.
References
1. Hansen D, Syben R, Vargas O, Spies C, 3. Michenfelder JD, Milde JH (1992) The 5. Bacher A, Illievich UM, Fitzgerald R, Welte M (1999) The alveolar-arterial effect of profound levels of hypother- Ihra G, Spiss CK (1997) Changes in difference in oxygen tension increases mia (below 14 degrees C) on canine oxygenation variables during progres- with temperature-corrected determina- cerebral metabolism. J Cereb Blood sive hypothermia in anesthetized pa- tion during moderate hypothermia. An- Flow Metab 12:877–880 tients. J Neurosurg Anesthesiol 9:205– esth Analg 88:538–542 4. Michenfelder JD, Milde JH (1991) The 10 2. Kelman GR (1966) Digital computer relationship among canine brain tem- subroutine for the conversion of oxygen perature, metabolism, and function tension into saturation. J Appl Physiol during hypothermia. Anesthesiology 21:1375–1376 75:130–136 Frank Bloos Venous oximetry Konrad Reinhart
Physiology of mixed venous and central venous oxygen saturation
O2 delivery (DO2) describes whole-body oxygen supply according to the following formula:
DO2 ¼ CO CaO2 ð1Þ
where CO is cardiac output and CaO2 is arterial oxygen content, which itself is the sum of oxygen bound to he- moglobin [product of hemoglobin concentration (Hb) and arterial O2 saturation (SaO2)] and physically dissolved oxygen [arterial PO2 (PaO2)]: CaO ¼ðHb 1:36 SaO ÞþðPaO 0:0031Þð2Þ Introduction 2 2 2 Oxygen demand can be summarized in the whole-body The primary physiological task of the cardiovascular oxygen consumption (VO2), which is expressed mathe- system is to deliver enough oxygen (O2) to meet the matically by the Fick principle as the product of CO and metabolic demands of the body. Shock and tissue hypoxia arteriovenous O2 content difference (CaO2 CvO2): occur when the cardiorespiratory system is unable to VO ¼ CO ðCaO CvO Þð3Þ cover metabolic demand adequately. Sustained tissue 2 2 2 hypoxia is one of the most important cofactors in the where mixed venous O2 content (CvO2) is: pathophysiology of organ dysfunction [1]. Therefore de- CvO ¼ðHb 1:36 SvO ÞþðPvO 0:0031Þð4Þ termining the adequacy of tissue oxygenation in critically 2 2 2 ill patients is central to ascertain the health of the patient. Equation 3 may be transposed to:
Unfortunately, normal values in blood pressure, central VO2 venous pressure, heart rate, and blood gases do not rule CvO2 ¼ CaO2 ð5Þ CO out tissue hypoxia or imbalances between whole-body oxygen supply and demand [2]. This discrepancy has led As physically dissolved oxygen can be neglected, Eq. 5 to increased interest in more direct indicators of adequacy may be written as: of tissue oxygenation such as mixed and central venous VO Hb 1:36 SvO ðHb 1:36 SaO Þ 2 oxygen saturations. Pulmonary artery catheterization al- 2 2 CO lows obtaining true mixed venous oxygen saturation VO2 (SvO2) while measuring central venous oxygen saturation , SvO ð6Þ 2 CO (ScvO2) via central venous catheter reflects principally the degree of oxygen extraction from the brain and the Equation 6 also demonstrates that SvO2 is directly pro- upper part of the body. This brief review discusses the portional to the ratio of VO2 to CO. Thus SvO2 reflects role and limitations of SvO2 and ScvO2 as indicators of the relationship between whole-body O2 consumption and the adequacy of tissue oxygenation. cardiac output. Indeed, it has been shown that the SvO2 is well correlated with the ratio of O2 supply to demand [3].
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 53 DOI: 10.1007/978-3-642-01769-8_13, © Springer-Verlag Berlin Heidelberg 2009 912 54 F. Bloos K. Reinhart
Pathophysiology of central Table 1 Limits of mixed venous oxygen saturation or mixed venous O2 saturation during shock SvO2 >75% Normal extraction O2 supply >O2 demand Usually VO2 is independent of DO2 since tissues can 75% >SvO2 >50% Compensatory extraction Increasing O demand or decreasing O maintain O2 needs by increasing O2 extraction when DO2 2 2 decreases. However, this mechanism has its limits. Below supply 50% >SvO2 >30% Exhaustion of extraction a so-called critical DO2 compensatory increase in O2 Beginning of lactic acidosis O2 supply
sults. Given the fact that ScvO2 exceeds SvO2 on average by 8% in patients with septic shock, an SvO2 of about 62– 65% should suffice as endpoint for hemodynamic resus- citation in these conditions, although this has not been tested prospectively. However, the placement of pulmo- nary artery catheters and the potentially higher risk of this should not result in a delay in the start of the resuscitation of critically ill patients. Venous oximetry can reflect the adequacy of tissue oxygenation only if the tissue is still capable of extracting O2. In the case of arteriovenous shunting on the micro- circulatory level or cell death, SvO2 and ScvO2 may not decrease or even show elevated values despite severe tis- sue hypoxia. As demonstrated in patients after prolonged cardiac arrest, venous hyperoxia with an ScvO2 higher than 80% is indicative of impaired oxygen use [12].
Conclusion
Low values of SvO2 or ScvO2 indicate a mismatch be- tween O2 delivery and tissue O2 need. While measure- ment of SvO2 requires the insertion of a pulmonary artery catheter, measurement of ScvO2 requires only central venous catheterization. ScvO2 directed early goal-directed therapy improves survival in patients with septic shock who are treated in an emergency department. However, ScvO2 values may differ from SvO2 values, and this difference varies in direction and magnitude with car- diovascular insufficiency. ScvO2 should not be used alone Fig. 1 Arterial and venous oxygen saturations in various vascular in the assessment of the cardiocirculatory system but regions [2] combined with other cardiocirculatory parameters and indicators of organ perfusion such as serum lactate con- centration and urine output.
References
1. Marshall JC (2001) Inflammation, co- 5. Scheinman MM, Brown MA, Rapaport 9. Edwards JD, Mayall RM (1998) Im- agulopathy, and the pathogenesis of E (1969) Critical assessment of use of portance of the sampling site for mea- multiple organ dysfunction syndrome. central venous oxygen saturation as a surement of mixed venous oxygen sat- Crit Care Med 29:S99–S106 mirror of mixed venous oxygen in uration in shock. Crit Care Med 2. Reinhart K (1989) Monitoring O2 severely ill cardiac patients. Circulation 26:1356–1360 transport and tissue oxygenation in 40:165–172 10. Reinhart K, Rudolph T, Bredle DL, critically ill patients. In: Reinhart K, 6. Lee J, Wright F, Barber R, Stanley L Hannemann L, Cain SM (1989) Com- Eyrich K (ed) Clinical aspects of O2 (1972) Central venous oxygen satura- parison of central-venous to mixed-ve- transport and tissue oxygenation. tion in shock: a study in man. Anes- nous oxygen saturation during changes Springer, Berlin Heidelberg New York, thesiology 36:472–478 in oxygen supply/demand. Chest pp 195–211 7. Reinhart K, Kuhn HJ, Hartog C, Bredle 95:1216–1221 3. Reinhart K, Sch fer M, Rudolph T, DL (2004) Continuous central venous 11. Rivers E, Nguyen B, Havstad S, Ressler Specht M (1989) Mixed venous oxygen and pulmonary artery oxygen saturation J, Muzzin A, Knoblich B, Peterson E, saturation. Appl Cardiopulm Patho- monitoring in the critically ill. Intensive Tomlanovich M (2001) Early goal-di- physiol 2:315–325 Care Med 30:1572–1578 rected therapy in the treatment of severe 4. Vincent JL, De Backer D (2004) Oxy- 8. Meier-Hellmann A, Specht M, Hanne- sepsis and septic shock. N Engl J Med gen transport-the oxygen delivery con- mann L, Hassel H, Bredle DL, Reinhart 345:1368–1377 troversy. Intensive Care Med 30:1990– K (1996) Splanchnic blood flow is 12. Rivers EP, Rady MY, Martin GB, Fenn 1996 greater in septic shock treated with NM, Smithline HA, Alexander ME, norepinephrine than in severe sepsis. Nowak RM (1992) Venous hyperoxia Intensive Care Med 22:1354–1359 after cardiac arrest. Characterization of a defect in systemic oxygen utilization. Chest 102:1787–1793 Jérôme Aboab Relation between PaO /F O ratio and F O : Bruno Louis 2 I 2 I 2 Bjorn Jonson a mathematical description Laurent Brochard
Introduction (e.g., chronic obstructive lung disease and asthma). Sec- ond, at an FIO2 of 1.0 absorption atelectasis may occur, The acute respiratory distress syndrome (ARDS) is char- increasing true shunt [4]. Thus, at high FIO2 levels (> 0.6) acterized by severe hypoxemia, a cornerstone element true shunt may progressively increase but be reversible in its definition. Numerous indices have been used to by recruitment maneuvers. Third, because of the complex describe this hypoxemia, such as the arterial to alveolar mathematical relationship between the oxy-hemoglobin O2 difference, the intrapulmonary shunt fraction, the dissociation curve, the arterio-venous O2 difference, oxygen index and the PaO2/FIO2 ratio. Of these different the PaCO2 level and the hemoglobin level, the relation indices the PaO2/FIO2 ratio has been adopted for routine between PaO2/FIO2 ratio and FIO2 is neither constant nor use because of its simplicity. This ratio is included in linear, even when shunt remains constant. most ARDS definitions, such as the Lung Injury Score [1] Gowda et al. [5] tried to determine the usefulness of and in the American–European Consensus Confer- indices of hypoxemia in ARDS patients. Using the 50- ence Definition [2]. Ferguson et al. recently proposed compartment model of ventilation–perfusion inhomogene- a new definition including static respiratory system com- ity plus true shunt and dead space, they varied the FIO2 be- pliance and PaO2/FIO2 measurement with PEEP set above tween 0.21 and 1.0. Five indices of O2 exchange efficiency 10 cmH2O, but FIO2 was still not fixed [3]. Important were calculated (PaO2/FIO2, venous admixture, P(A-a)O2, for this discussion, the PaO2/FIO2 ratio is influenced PaO2/alveolar PO2, and the respiratory index). They de- not only by ventilator settings and PEEP but also by scribed a curvilinear shape of the curve for PaO2/FIO2 ra- FIO2. First, changes in FIO2 influence the intrapulmonary tio as a function of FIO2,butPaO2/FIO2 ratio exhibited shunt fraction, which equals the true shunt plus ventila- the most stability at FIO2 values ≥ 0.5 and PaO2 values tion–perfusion mismatching. At FIO2 1.0, the effects of ≤ 100 mmHg, and the authors concluded that PaO2/FIO2 ventilation–perfusion mismatch are eliminated and true ratio was probably a useful estimation of the degree of intrapulmonary shunt is measured. Thus, the estimated gas exchange abnormality under usual clinical conditions. shunt fraction may decrease as FIO2 increases if V/Q Whiteley et al. also described identical relation with other mismatch is a major component in inducing hypoxemia mathematical models [6, 7].
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 57 DOI: 10.1007/978-3-642-01769-8_14, © Springer-Verlag Berlin Heidelberg 2009 58 J. Aboab et al.
This nonlinear relation between PaO2/FIO2 and FIO2, In the ideal capillary (c ), the saturation is 1.0 and the however, underlines the limitations describing the inten- Pc O2 is derived from the alveolar gas equation: sity of hypoxemia using PaO2/FIO2, and is thus of major PaCO2 importance for the clinician. The objective of this note is Pc O2 = PAO 2 = (PB − 47) × FIO2 − . to describe the relation between PaO2/FIO2 and FIO2 with R a simple model, using the classic Berggren shunt equation This equation describes the alveolar partial pressure of and related calculation, and briefly illustrate the clinical O2 (PAO2) as a function, on the one hand, of barometric consequences. pressure (PB), from which is subtracted the water vapor pressure at full saturation of 47 mmHg, and FIO2,toget the inspired O2 fraction reaching the alveoli, and on the Berggren shunt equation (Equation 1) other hand of PaCO2 and the respiratory quotient (R)in- dicating the alveolar partial pressure of PCO2. Saturation, The Berggren equation [8] is used to calculate the magni- Sc O2 and SaO2 are bound with O2 partial pressure (PO2) tude of intrapulmonary shunt (S), “comparing” the theoret- Pc O2 and PaO2, by the oxy-hemoglobin dissociation ical O2 content of an “ideal” capillary with the actual ar- curve, respectively. The oxy-hemoglobin dissociation terial O2 content and taking into account what comes into curve describes the relationship of the percentage of the lung capillary, i.e., the mixed venous content. Cc O2 hemoglobin saturation to the blood PO2. This relationship is the capillary O2 content in the ideal capillary, CaO2 is is sigmoid in shape and relates to the nonlinear relation the arterial O2 content, and Cv¯O2 is the mixed venous O2 between hemoglobin saturation and its conformational content, changes with PO2. A simple, accurate equation for human blood O2 dissociation computations was proposed by ˙ ( − ) = Qs = Cc O2 CaO2 Severinghaus et al. [9]: S ˙ Qt (Cc O2 − CvO¯ 2)
This equation can be written incorporating the arterio- Blood O2 dissociation curve equation (Equation 4) venous difference (AVD) as: − −1 1 SO = PO3 + 150PO × 23 400 + 1 S 2 2 2 Cc O − CaO = × AV D . 2 2 1 − S This equation can be introduced in Eq. 1: Blood O2 contents are calculated from PO2 and PaCO 3 hemoglobin concentrations as: Hb × (P − 47) × F O − 2 B I 2 R −1 + ( − ) × − PaCO2 Equation of oxygen content (Equation 2) 150 PB 47 FIO2 R −1 CO2 = (Hb × SO2 × 1.34) + (PO2 × 0.0031) × 23 400 + 1 × 1.34 + (PB − 47) The formula takes into account the two forms of oxygen PaCO2 carried in the blood, both that dissolved in the plasma and × FIO2 − × 0.0031 that bound to hemoglobin. Dissolved O follows Henry’s R 2 law – the amount of O2 dissolved is proportional to its par- −1 − × 3 + × tial pressure. For each mmHg of PO2 there is 0.003 ml Hb PaO2 150PaO2 23 400 O2/dl dissolved in each 100 ml of blood. O2 binding to hemoglobin is a function of the hemoglobin-carrying ca- −1 + × . + ( × . ) pacity that can vary with hemoglobinopathies and with fe- 1 1 34 PaO2 0 0031 tal hemoglobin. In normal adults, however, each gram of S hemoglobin can carry 1.34 ml of O2. Deriving blood O2 = × − AV D content allows calculation of both Cc O2 and CaO2 and al- 1 S lows Eq. 1 to be rewritten as follows: Equation 1 modified gives a relation between FIO2 and PaO2 with six fixed parameters: Hb, PaCO2,therespira- (Hb × ScO × 1.34) + (PcO × 0.0031) 2 2 tory quotient R, the barometric pressure (PB), S and AVD. − (Hb × SaO 2 × 1.34) + (PaO2 × 0.0031) The resolution of this equation was performed here with S Mathcad® software, (Mathsoft Engineering & Education, = × AV D 1 − S Cambridge, MA, USA). Relation between PaO2 /FOI 2 ratio and FOI 2 59
Fig. 1 Relation between PaO2/FIO2 and FIO2 for a constant arterio-venous difference (AVD) and different shunt levels (S)
Fig. 2 Relation between PaO2/FIO2 and FIO2 for a constant shunt (S) level and different values of arterio-venous differences (AVD)
Resolution of the equation under conditions of constant metabolism and ventila- tion–perfusion abnormality. The equation results in a nonlinear relation between FIO2 and PaO2/FIO2 ratio. As previously mentioned, numerous factors, notably nonpulmonary factors, influence this Consequences curve: intrapulmonary shunt, AVD, PaCO2, respiratory quotient and hemoglobin. The relationship between This discussion and mathematical development is based on PaO2/FIO2 and FIO2 is illustrated in two situations. Fig- a mono-compartmental lung model and does not take into ure 1 shows this relationship for different shunt fractions account dynamic phenomena, particularly when high FIO2 and a fixed AVD. For instance, in patients with 20% shunt results in denitrogenation atelectasis. Despite this limita- (a frequent value observed in ARDS), the PaO2/FIO2 tion, large nonlinear variation and important morphologic ratio varies considerably with changes in FIO2. At both differences of PaO2/FIO2 ratio curves vary markedly with extremes of FIO2,thePaO2/FIO2 is substantially greater intrapulmonary shunt fraction and AVD variation. Thus, than at intermediate F O . In contrast, at extremely high not taking into account the variable relation between F O ∼ I 2 I 2 shunt (= 60%) PaO2/FIO2 ratio is greater at low FIO2 and and the PaO2/FIO2 ratio could introduce serious errors in decreases at intermediate FIO2, but does not exhibit any the diagnosis or monitoring of patients with hypoxemia on further increase as inspired FIO2 continue to increase, for mechanical ventilation. instance above 0.7. Figure 2 shows the same relation but Recently, the accuracy of the American–European with various AVDs at a fixed shunt fraction. The larger is consensus ARDS definition was found to be only moder- AVD, the lower is the PaO2/FIO2 ratio for a given FIO2. ate when compared with the autopsy findings of diffuse AVD can vary substantially with cardiac output or with alveolar damage in a series of 382 patients [10]. The oxygen consumption. problem discussed here with FIO2 may to some extent These computations therefore illustrate substantial participate in these discrepancies. A study by Ferguson variationinthePaO2/FIO2 index as FIO2 is modified et al. [11] illustrated the clinical relevance of this dis- 60 J. Aboab et al. cussion. They sampled arterial blood gases immediately between the “persistent” and “transient” ARDS groups. after initiation of mechanical ventilation and 30 min There was a large difference in mortality, and duration of after resetting the ventilator in 41 patients who had early ventilation, favoring the “transient” ARDS group. Thus, ARDS based on the most standard definition [2]. The varying FIO2 will alter the PaO2/FIO2 ratio in patients with changes in ventilator settings chiefly consisted of increas- true and relative intrapulmonary shunt of ≥ 20%. In clin- ing FIO2 to 1.0. In 17 patients (41%), the hypoxemia ical practice, when dealing with patients with such shunt criterion for ARDS persisted after this change (PaO2/FIO2 levels, one should know that the increasing PO2/FIO2 with < 200 mmHg), while in the other 24 patients (58.5%) FIO2 occurs only after FIO2 increase to > 0.6 (depending the PaO2/FIO2 had become greater than 200 mmHg after on the AVD value). Thus, the use of the PO2/FIO2 ratio as changing the FIO2, essentially “curing” them of their a dynamic variable should be used with caution if FIO2, ARDS in a few minutes. Of note, outcome varied greatly as well as other ventilatory settings, varies greatly.
References 1. Murray J, Matthay MA, Luce J, Flick M 4. Santos C, Ferrer M, Roca J, Torres A, 8. Berggren S (1942) The oxygen deficit (1988) An expanded definition of the Hernandez C, Rodriguez-Roisin R of arterial blood caused by nonventi- adult respiratory distress syndrome. Am (2000) Pulmonary gas exchange re- lating parts of the lung. Acta Physiol Rev Respir Dis 138:720–723 sponse to oxygen breathing in acute Scand 11:1–92 2. Bernard GR, Artigas A, Brigham KL, lung injury. Am J Respir Crit Care Med 9. Severinghaus J (1979) Simple, accurate Carlet J, Falke K, Hudson L, Lamy M, 161:26–31 equations for human blood O2 disso- Legall JR, Morris A, Spragg R (1994) 5. Gowda MS, Klocke RA (1997) Vari- ciation computations. J Appl Physiol The American–European Consensus ability of indices of hypoxemia in adult 46:599–602 Conference on ARDS. Definitions, respiratory distress syndrome. Crit Care 10. Esteban A, Fernandez-Segoviano P, mechanisms, relevant outcomes, and Med 25:41–45 Frutos-Vivar F, Aramburu JA, Najera L, clinical trial coordination. Am J Respir 6. Whiteley JP, Gavaghan DJ, Hahn CE Ferguson ND, Alia I, Gordo F, Rios F Crit Care Med 149:818–824 (2002) Variation of venous admixture, (2004) Comparison of clinical crite- 3. Ferguson ND, Davis AM, Slutsky AS, SF6 shunt, PaO2,andthePaO2/FIO2 ra- ria for the acute respiratory distress Stewart TE (2005) Development of tio with FIO2. Br J Anaesth 88:771–778 syndrome with autopsy findings. Ann a clinical definition for acute respiratory 7. Whiteley JP, Gavaghan DJ, Hahn CE Intern Med 141:440–445 distress syndrome using the Delphi (2002) Mathematical modelling of 11. Ferguson ND, Kacmarek RM, technique. J Crit Care 20:147–154 oxygen transport to tissue. J Math Biol Chiche JD, Singh JM, Hallett DC, 44:503–522 Mehta S, Stewart TE (2004) Screening of ARDS patients using standardized ventilator settings: influence on enroll- ment in a clinical trial. Intensive Care Med 30:1111–1116 Jukka Takala Hypoxemia due to increased venous admixture: influence of cardiac output on oxygenation
Introduction What does venous admixture measure?
Venous admixture is used to describe situations in which In the hypoxemic patient under mechanical ventilation, the oxygenation of the arterial blood is less than that ex- changes in cardiac output may influence the level of pected for the pulmonary end-capillary blood (100%, if the arterial oxygenation, with several and sometimes opposite alveolar partial pressure of oxygen exceeds 13.3 kPa). Ve- effects. The purpose of this Physiological Note is to give nous admixture is the calculated amount of mixed venous the reader the physiological background to understand blood needed to bypass the alveoli and mix with the arte- these effects, which are often highly relevant for the rial blood to produce the observed degree of arterial hy- bedside management of patients with acute lung injury. poxemia. In other words, venous admixture represents the In the healthy lung, the venous blood returning to calculated fraction of cardiac output completely bypassing the right heart and flowing through the pulmonary artery oxygenation in the lung if the rest of the cardiac output is to the pulmonary capillaries will be fully saturated by fully oxygenated (assumed to be the case in the absence of oxygen during the passage through the alveolar part of inspired gas hypoxia) [1]. A pulmonary artery catheter is the capillary. The prerequisite for complete saturation necessary to obtain true mixed venous blood. of hemoglobin with oxygen is sufficiently high oxygen The venous admixture (Qs/Qt) can be calculated as partial pressure in the alveoli. Complete saturation is Qs/Qt = (CcO − CaO )/(CcO − CvO ), (1) approached if the alveolar partial pressure of oxygen ex- 2 2 2 2 ceeds 13.3 kPa (100 mmHg). This prerequisite is achieved where CcO2 is the pulmonary venous capillary oxygen during normoventilation of ambient air with normal lungs content in the ideal (i.e., normally ventilated and perfused) at the sea level. Hypoventilation (increased alveolar CO2) alveoli, and CaO2 and CvO2 are the arterial and mixed and decrease in barometric pressure (increased altitude) venous oxygen content, respectively. For the ideal alveoli, both reduce the alveolar PO2 – an effect which can be CcO2 = Hgb (hemoglobin; g/l) × 1.34 + 0.2325 × alveolar readily counteracted by increasing the inspired fraction of PO2 (kPa), assuming 100% saturation of the pulmonary oxygen. The degree of hypoxemia in these circumstances and capillary blood. can be predicted from the PO2 of ideal alveolar gas and Apart from hypoventilation, increased venous ad- the oxyhemoglobin dissociation curve. mixture or physiologic intrapulmonary shunt is the most
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 61 DOI: 10.1007/978-3-642-01769-8_15, © Springer-Verlag Berlin Heidelberg 2009 62 J. Takala common cause of hypoxemia in critically ill patients. In can be calculated as the product of cardiac output (CO) this paper, “venous admixture” and “physiologic shunt” and arterial-mixed venous oxygen content difference: are used interchangeably. The term “physiologic shunt” = × ( − ¯ ), should not be confused with the presence of slight venous VO2 CO CaO2 CvO2 (2) admixture in the normal lungs (around or below 5%); This can be rewritten as the venous admixture in the normal lungs results from venous blood flow through the thebesian veins (cardiac CvO¯ 2 = CaO2 − VO2/CO, (3) venous effluent directly into the left heart) and the deep true bronchial veins (into the pulmonary veins), and from or as the presence of a small amount of ventilation/perfusion = ¯ + / . mismatch. CaO2 CvO2 VO2 CO (3 ) The equation for venous admixture (Eq. 1) can be rear- ranged and written as What causes increased venous admixture? CaO2 = CcO2 × (1 − Qs/Qt) + ¯ × / . (4) Venous admixture can be caused by true shunt (blood CvO2 Qs Qt flow through alveoli that are not ventilated at all, Equations 3 and 4 can be combined to i.e., alveoli with a ventilation/perfusion = 0), and by ventilation/perfusion mismatch (alveoli with a low venti- CaO = CcO − (VO /CO) 2 2 2 (5) lation/perfusion). For further information on the concept ×(Qs/Qt)/(1 − Qs/Qt) of ventilation/perfusion matching see the Physiological Note by Calzia and Radermacher [2]. In the non-ventilated and Eqs. 3 and4to alveoli, oxygen will be transported to the capillary blood CvO¯ = CcO − (VO /CO) until the alveolar PO2 approaches the mixed venous 2 2 2 (6) ×[1 + (Qs/Qt)/(1 − Qs/Qt)]. PO2. In the alveoli with low ventilation/perfusion, the amount of oxygen reaching the alveoli per unit of time If the dissolved oxygen is ignored, Eqs. 5 and 6 can be is smaller than the amount needed to fully saturate the written as venous blood arriving at the alveolar capillary per unit of time. Hence, the alveolar PO will decrease until the SaO = 1 − (VO /CO × Hgb × 1.34) 2 2 2 (5 ) amount of oxygen reaching the alveoli through ventila- ×(Qs/Qt)/(1 − Qs/Qt), tion equals the amount transferred to the blood flowing through the alveoli (blood flow × arteriovenous oxygen SvO = 1 − (VO /CO × Hgb × 1.34) 2 2 (6 ) content difference); the consequence of the low ventila- ×[1 + (Qs/Qt)/(1 − Qs/Qt)]. tion/perfusion is that only partly oxygenated blood will be mixed in the pulmonary venous blood. The calculation Equations 5 and 6 demonstrate that in the presence of in- of venous admixture assumes that the mixed venous creased venous admixture, arterial oxygenation (SaO2)is blood is either fully oxygenated or not oxygenated at directly related to cardiac output and hemoglobin, and in- versely related to oxygen consumption. The effect of these all – hence, it cannot differentiate between true shunt and low ventilation/perfusion [3, 4]. It should be noted variables on arterial oxygenation will be markedly magni- that hypoxemia due to diffusion problems also causes fied in the presence of large Qs/Qt [5]. These equations can an increase in the calculated venous admixture, although be applied to demonstrate the interactions between venous no shunt or ventilation/perfusion mismatch would be admixture, arterial and mixed venous oxygenation, cardiac present. output, hemoglobin and oxygen consumption (Figs. 1, 2).
Cardiac output and increased venous admixture Venous admixture and interaction between mixed venous and arterial oxygenation In the interactions between venous admixture, arterial oxygenation, and mixed venous oxygenation in the clin- In the healthy lungs, arterial oxygenation is defined almost ical setting, cardiac output has the largest variability. As completely by the alveolar oxygen partial pressure. When shown in Fig. 1, an infinite number of arterial and mixed venous admixture increases, mixed venous oxygenation venous saturation lines form two concave surfaces, as will have a progressively larger impact on arterial oxy- a function of cardiac output and venous admixture. These genation. This interaction can be interpreted using the Fick surfaces slope progressively downwards when cardiac equation (Eq. 2) for oxygen consumption (VO2) together output decreases and the venous admixture increases. with the equation for venous admixture (Eq. 1). The VO2 An increase in oxygen consumption and a decrease in Hypoxemia due to increased venous admixture 63
Fig. 1 The relationship between venous admixture (Qs/Qt), arterial and mixed venous saturation and cardiac output. For the calculations, Fig. 2 Effect of oxygen consumption and hemoglobin on arterial dissolved oxygen has been ignored; a hemoglobin of 100 g/l and an (red) and mixed venous (blue) oxygenation. The solid curves are oxygen consumption of 250 ml/min have been assumed. Points A taken from Fig. 1 and represent a physiologic shunt of 50%. A sim- and B represent the effect of cardiac output decreasing from 8 l/min ilar proportional increase in oxygen consumption and decrease in to 4 l/min. The venous admixture is likely to decrease – in this case hemoglobin have identical effects: in both cases the whole family of from 0.50 to 0.40. Since the decrease in cardiac output is accom- arterial (red dotted line) and mixed venous (blue dotted line) satura- panied by increased oxygen extraction, the mixed venous saturation tion curves shown in Fig. 1 shifts downwards (open arrows)andthe decreases substantially (points C and D), and the net effect is wors- arterial–venous saturation difference widens (solid arrows) ened arterial hypoxemia
hemoglobin both move the surfaces down and increase the lower mixed venous oxygenation. Even if the venous the distance between them. This is shown for one pair admixture were to decrease enough to completely abol- of saturation lines at 50% physiologic shunt in Fig. 2. ish the effect of a concomitant reduction of mixed venous In order to maintain a given level of metabolic activity oxygenation on arterial oxygenation, this would result in (250 ml/min of VO2, hemoglobin 100 g/l in Fig. 1), the decrease in oxygen delivery to the tissues in proportion cardiac output has to increase if the venous admixture with the decrease in cardiac output. Conversely, if an acute increases. Thus a cardiac output of approximately 4 l/min increase in cardiac output increases the physiologic shunt under the conditions shown in Fig. 2 (250 ml/min of enough to abolish the impact of an increased mixed venous VO2, hemoglobin 100 g/l) would result in mixed venous oxygenation on arterial oxygenation, the oxygen delivery saturation approaching zero – a situation incompatible to the tissues will increase in proportion with the increase with survival. Assuming that a mixed venous saturation of in cardiac output. 40–50% could be tolerated in the acutely ill patient over If an increase in cardiac output from 6.5 l/min to a reasonable period of time, a minimum cardiac output 9.5 l/min increases venous admixture from 40% to 50% of 6–7.5 l/min would be necessary. A higher metabolic while the hemoglobin and oxygen consumption remain activity or a lower hemoglobin (Fig. 2) would necessitate unchanged, the arterial saturation remains unchanged even higher levels of cardiac output. This example demon- (at around 81% in the example in Fig. 3), but the mixed strates the fundamental role of cardiac output in states venous saturation increases from 52% to 61% and the with acute major increases in physiologic shunt, such as in systemic oxygen delivery by 46%. In the clinical setting, severe acute respiratory distress syndrome (ARDS). the magnitude of individual responses in physiologic Acute changes in cardiac output are likely to cause par- shunt to acute changes in cardiac output varies widely, allel changes in physiologic shunt, which tend to counter- although the directional changes are usually parallel. act the changes imposed on arterial oxygenation [6, 7]: In contrast to deliberately induced increases in cardiac when cardiac output decreases, the physiologic shunt de- output, acute spontaneous increases in cardiac output are creases as well. Decreased cardiac output reduces mixed often accompanied by increased metabolic demand. As venous oxygenation, and thereby also arterial oxygenation. discussed before, an increase in oxygen consumption will Although the physiologic shunt is likely to decrease in par- shift the relationship between arterial and mixed venous allel with cardiac output, the favorable effect of reduced saturation towards desaturation of both, and widen the shunt on arterial oxygenation is at least in part set off by arterio-venous oxygen content difference (Figs. 1, 2), 64 J. Takala
vasoactive substances in sepsis, acute lung injury/ARDS and shock may modify the hypoxic pulmonary vasocon- striction.
Implications for treatment of acute hypoxemia
Diverse pathologies increase the venous admixture, e.g., atelectasis, pulmonary edema of any etiology, and infec- tions and inflammatory processes that reduce the ventila- tion/perfusion locally or regionally in the lung. The treat- ment strategy should aim at prompt correction of the cause. While this may be possible in atelectasis, in most other conditions prolonged support of oxygenation is likely to be necessary. Since atelectatic components are common in many situations in which hypoxemia is due to increased venous admixture, maneuvers to re-expand the atelectatic lung regions and to keep them open (recruitment, positive Fig. 3 Effect of an increase in cardiac output from 6.5 to 9.5 l/min airway pressure, prone positioning) should be considered. and a simultaneous increase in physiologic shunt from 40% to 50% When hypoxemia and increased physiologic shunt persist on arterial (red arrow) and mixed venous (blue arrow) oxygenation. despite these maneuvers, it is advisable to consider the in- The effect of increased physiologic shunt on arterial oxygenation is completely eliminated due to increased mixed venous saturation, and teraction of arterial and mixed venous oxygenation in the the whole body oxygen delivery is increased substantially (by 46%) management of the hypoxemia. Typical therapeutic mea- sures (increased positive end-expiratory and mean airway pressure) are likely to reduce cardiac output and mixed ve- nous oxygenation. Hence, the cost of attempts to improve thereby reducing the positive effect of an increased cardiac or maintain arterial oxygenation may be reduced oxygen output. delivery to the tissues. On the other hand, increased car- The mechanism by which cardiac output and the phys- diac output, even if accompanied by increased venous ad- iologic shunt change in parallel is not certain; the most mixture, may result in well-maintained arterial oxygena- likely explanation is that changes in mixed venous oxy- tion and increased oxygen delivery. In addition, reducing genation alter the hypoxic pulmonary vasoconstriction [8]. oxygen consumption and increasing hemoglobin should be This would also explain the intra- and interindividual vari- considered (Fig. 2). All these measures to increase mixed ability in the changes in physiologic shunt in response to venous oxygenation may be worthwhile, especially in pa- changes in cardiac output observed in the clinical setting: tients with low mixed venous saturation and large physio- changes in local and circulating endo- and exogenous logic shunt.
References 1. Lumb AB (2000) Distribution of 4. Siggaard-Anderson O, Gothgen IH 7. Freden F, Cigarini I, Mannting F, pulmonary ventilation and perfu- (1995) Oxygen parameters of arterial Hagberg A, Lemaire F, Hedenstierna G sion. In: Lumb AB (ed) Nunn’s and mixed venous blood—new and old. (1993) Dependence of shunt on cardiac applied respiratory physiology, Acta Anaesthesiol Scand 39:41–46 output in unilobar oleic acid edema: dis- 5th edn. Butterworth-Heinemann, 5. Giovannini I, Boldrini G, Sganga G, tribution of ventilation and perfusion. Oxford, UK, pp 163–199 Castiglioni G, Castagneto M (1983) Intensive Care Med 19:185–90 2. Calzia E, Radermacher P (2003) Quantification of the determinants 8. Marshall BE, Hanson CW, Frasch F, Alveolar ventilation and pulmonary of arterial hypoxemia in critically ill Marshall C (1994) Role of hy- blood flow: the V(A)/Q concept. patients. Crit Care Med 11:644–645 poxic pulmonary vasoconstriction Intensive Care Med 29:1229–1232 6. Dantzker DR, Lynch JP, Weg JG in pulmonary gas exchange and 3. Ratner ER, Wagner PD (1982) Reso- (1980) Depression of cardiac output blood flow distribution. Basic sci- lution of the multiple inert gas method is a mechanism of shunt reduction in ence series: 2. Pathophysiology. for estimating VA/Q maldistribution. the therapy of acute respiratory failure. Intensive Care Med 20:379–389 Respir Physiol 49:293–313 Chest 77:636–642 Robert Naeije Pulmonary vascular resistance A meaningless variable?
nants of resistance. Numerous painstaking measurements of pressures at variable continuous streamlined flows of Newtonian and non-Newtonian fluids of different viscos- ities, through variable dimension capillary glass tubes, led to what is presently known as Poiseuille’s law. It states that the resistance R to flow, defined as a pressure drop (∆P) to flow (Q) ratio, is equal to the product of the length (l) of the tube by a viscosity constant (η) divided by the product of fourth power of the internal radius (r) by π:
Introduction A remarkable feature of Poiseuille’s resistance equation is its exquisite sensibility to changes in internal radius r, Almost 20 years ago, Adriaan Versprille published an because it is at the fourth power. editorial in this journal to explain why, in his opinion, the calculation of pulmonary vascular resistance (PVR) is meaningless [1]. The uncertainties of PVR were un- Transposition to the pulmonary circulation derscored a year later by McGregor and Sniderman in the American Journal of Cardiology [2]. Obviously, both The transposition of Poiseuille’s law to the pulmonary papers failed to convince. A Medline search from 1985 circulation rests on the invalid assumptions that blood is to the end of 2002 reveals no less than 7,158 papers with a Newtonian fluid (that is with a velocity-independent PVR calculations. What is it that could be wrong in all viscosity), that the pulmonary resistive vessels are un- this literature? branched small rigid tubes of circular surface sections and that pulmonary blood flow is streamlined and non- pulsatile. But the approximations have less impact on What is a resistance calculation? calculated PVR values than the internal arteriolar radius, to which the Poiseuille’s resistance variable is so sensi- A resistance calculation derives from a physical law first tive. Accordingly, it is reasonable to calculate PVR as developed by the French physiologist Poiseuille in the the ratio of the pressure drop through the pulmonary cir- early nineteenth century. Poiseuille invented the U-tube culation [mean pulmonary artery pressure (Ppa) minus mercury manometer. He used the device to show that left atrial pressure (Pla)] to pulmonary blood flow (Q) blood pressure does not decrease from large to small using the electrical principles described as Ohm’s law: arteries to the then existing limit of cannula size of about 2 mm, and rightly concluded that the site of systemic vascular resistance could only be at smaller-sized vessels [3]. Since he could not penetrate to these minute vessels, The resulting PVR value is a valid indicator of structural he used small size glass tubes to investigate the determi- changes at the small resistive pulmonary arteriole level,
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 65 DOI: 10.1007/978-3-642-01769-8_16, © Springer-Verlag Berlin Heidelberg 2009 527 66 R. Naeije
How is it possible that the extrapolated pressure inter- cepts of (Ppa−Pla)/Q plots are positive, meaning that the apparent back-flow pressure for pulmonary blood flow exceeds Pla? A possible answer is that pulmonary ves- sels are collapsible. Consider a circulatory system made of two rigid tubes connected by a collapsible tube sur- rounded by a pressure chamber (Fig. 1). This model is called the “Starling resistor”, because Starling used such a device in his heart-lung preparation to control arterial blood pressure. If the outflow pressure (Pla) is higher than the chamber pressure (Pc), then several aspects of the circulation exist. First, flow starts when the inflow pressure (Ppa) is higher than Pla and it increases linearly with the increase in the Ppa−Pla difference. Second, the Fig. 1 Starling resistor model to explain the concept of closing (Ppa−Pla)/Q line crosses the origin. And third, PVR, the pressure within a circulatory system. Flow (Q) is determined by − the gradient between an inflow pressure, or mean pulmonary ar- slope of the (Ppa Pla)/Q relationship, is constant. If the tery pressure (Ppa), and an outflow pressure which is either clos- Pc is higher than Pla, however, then flow starts when ing pressure (Pc) or left atrial pressure (Pla). When Pla is greater Ppa is higher than Pc, independent of the lower Pla than Pc, the (Ppa−Pla)/Q relationship crosses the origin (A curve) value, and flow increases linearly with the increase in and PVR is constant. When Pc is greater than Pla, the (Ppa−Pla)/Q − relationship has a positive pressure intercept (B curve) and PVR (Ppa Pc). The Pc is also referred to as the closing pres- decreases curvilinearly with increasing Q. Also shown are possi- sure, because when intraluminal pressure decreases be- ble misleading PVR calculations: PVR, the slope of (Ppa−Pla)/Q low Pc, the vessels collapse and flow ceases. Important- may remain unchanged in the presence of a vasoconstriction (from ly, both the (Ppa−Pla)/Q line has a positive extrapolated 1 to 2) or decrease (from 1 to 3) with no change in the functional state of the pulmonary circulation (unchanged pressure/flow line) intercept that is equal to Pla and PVR decreases with in- creasing flow. If either alveolar pressure or pulmonary vascular tone are increased enough to cause vascular col- lapse at values above Pla, then these conditions will also which is the major site of most types of acute and chron- exist in vivo. ic pulmonary hypertension states. Permutt et al. conceived a vascular waterfall model made of parallel collapsible vessels with a distribution of closing pressures [4]. At low flow, these vessels would Pulmonary vascular pressure-flow relationships be progressively derecruited, accounting for a low flow Ppa/Q curve that is concave to the flow axis and inter- However, PVR is flow-sensitive and this can be a source cepts the pressure axis at the lowest closing pressure to of confusion. The Ohm’s law resistance equation of pres- be overcome to generate a flow. At higher flows, com- sure drop divided by flow implies that the (inflow minus pleted recruitment and negligible distension account outflow) pressure difference as a function of flow is for a linear Ppa/Q curve with an extrapolated pressure linear and crosses the origin. If correct, resistance would intercept representing a weighted mean of all the parallel be independent of either flow or pressure (Fig. 1). A circuit Pc values. In this model, the mean Pc is the effec- PVR calculation assumes that if one were to increase tive outflow pressure of the pulmonary circulation. A Pla Ppa and examine the resultant Ppa/Q relationship, it lower than the mean Pc is then only an apparent down- would display an extrapolated pressure axis intercept at a stream pressure, irrelevant to flow as is the height of a value equal to Pla. This assumption appears valid in waterfall. Resistance calculations remain applicable to well-oxygenated healthy lungs. Accordingly, normal evaluate the functional state of the pulmonary circulation healthy lungs appear to be fully recruited and maximally even in these conditions, provided that the apparent distended. Also, in intact animal models, progressive downstream pressure (Pla) is replaced by the effective decreases in pulmonary vascular pressures with their as- one (Pc). sociated decreasing flow do not induce a systemic baro- But pulmonary vessels are also distensible. Accord- reflex, thus changes in pulmonary sympathetic vasomo- ingly, pulmonary circulation models have been devel- tor tone is constant over a wide range of pulmonary oped that explain Ppa/Q relationships by a distribution of arterial pressures and flow. However, hypoxia and many both resistances and compliances [5]. Positive extrapo- cardiac and respiratory diseases increase both the slope lated pressure intercepts of (Ppa−Pla)/Q plots can be pre- (PVR) and the extrapolated intercepts of multipoint dicted by concomitant increases in resistance and com- (Ppa−Pla)/Q plots. Importantly, these pulmonary vascu- pliance of small resistive vessels [6]. Intuitively, one lar pressure-flow relations still tend to remain linear over would rather imagine constricted vessels to be stiffer. a physiological range of flows [2]. However, it has been shown experimentally that con- 528 Pulmonary vascular resistance 67 stricted arterioles become more distensible, probably be- cause decreased surface section area places them on the steeper portion of the dimension-pressure curve. In reality, provided a large enough number of Ppa/Q coordinates are generated and submitted to an adequate fitting procedure, Ppa/Q curves can always be shown to be curvilinear with concavity to the flow axis [7]. On the other hand, derecruitment can be directly observed at low pressures and flows. Both recruitment and disten- sion probably explain most of the Ppa/Q curves. According to this integrated view, at low inflow pres- sures many pulmonary vessels are closed as their intrin- sic tone and surrounding alveolar pressure exceed intra- Fig. 2 Pressure/flow diagram for the interpretation of pulmonary luminal pressure and those that are open are relatively hemodynamic measurements. The central point C corresponds to initial mean pulmonary artery pressure (Ppa), left atrial pressure narrow. As inflow pressure increases, previously closed (Pla) and flow (Q) measurements. A decrease in (Ppa−Pla) at in- vessels progressively open (recruitment) and previously creased Q can only be explained by pulmonary vasodilatation. An narrow vessels progressively dilate (distension). Both increase in (Ppa−Pla) at decreased Q can only be explained by mechanisms explain a progressive decrease in the slope pulmonary vasoconstriction. Rectangles of certainty are extended of pulmonary vascular pressure/flow relationships to adjacent triangles because negative slopes or pressure intercepts of (Ppa−Pla)/Q lines are impossible. Arrows indicate changes in (resistance) with increasing flow or pressure and ac- measured (Ppa−Pla) and Q, (1) vasodilatation, (2) vasoconstriction count for apparent functional dissociation between Ppa and Q as reported, for example, in the acute respiratory distress syndrome [8]. axis at a negative pressure in the absence of a change in vasomotor tone. The (Ppa−Pla)/Q line and the line of A pressure/flow diagram to avoid errors based on maximum possible Pc at an actually measured initial isolated pulmonary vascular resistance calculations point C determine a series of areas on the pressure/flow diagram. At increasing flow, any decrease in (Ppa−Pla) As illustrated in Fig. 1, PVR calculations can give mis- can only be vasodilation. At decreasing flow, any leading information under conditions of changing cardi- increase in (Ppa−Pla) can only be vasoconstriction. In ac output. Vasomotor tone in subjects with pulmonary addition, a decrease in (Ppa−Pla) at decreasing flow that hypertension may appear to be either increasing or is more than predicted by the initial PVR equation can decreasing while, in fact, the functional state of the pul- only be vasodilatation. An increase in (Ppa−Pla) more monary circulation remains unchanged. In his original than predicted by the initial PVR equation can only be physiological note on this topic 17 years ago Versprille vasoconstriction. As shown in Fig. 2, zones of uncer- apologized to the clinicians for not being able to offer an tainties remain because the actual value of closing pres- alternative solution while pointing at the limitations of sure is not known. An additional uncertainty is related PVR measures [1]. However, PVR measures are similar to the assumption that the pressure/flow coordinates are to other composite variables in having inherent limita- best described by a linear approximation, but this is tions. Systemic vascular resistance carries similar limita- generally reasonable in the absence of extreme changes tions and for related reasons. Importantly, when assess- in flow. ing pulmonary vasomotor tone, measurements of prima- ry variables always minimize the inherent inaccuracies of calculating derived measurements. For example, in Improved definition of pulmonary vascular pulmonary hemodynamic studies, directly measured resistance by a multipoint pulmonary vascular pressures and pulmonary blood flow can be plotted on a pressure/flow plot pressure/flow diagram (Fig. 2). On such a diagram, connecting the central starting Still, the resistive properties of the pulmonary circulation point C to the origin defines PVR. However, a closing are best defined by the measurement of pulmonary vas- pressure Pc higher than the apparent outflow pressure cular pressures at several levels of flow. The problem is Pla is possible, which causes the pressure/flow line to increase or to decrease flow with interventions that do drawn from point C to cross the pressure axis at increas- not affect vascular tone. Exercise changes cardiac output ing pressures up to a maximum corresponding to a hori- but may lead to spuriously increased slopes with Ppa/Q zontal line. It is indeed physically impossible that plots [9]. This is probably due to exercise-induced pul- (Ppa−Pc) would decrease at increasing flow. On the oth- monary vasoconstriction, because of a decrease in mixed − er hand, a (Ppa Pla)/Q line cannot cross the pressure venous PO2, sympathetic nervous system activation and 529 68 R. Naeije exercise-associated increase in left atrial pressure. A bet- Conclusions ter option may be to increase flow by an infusion of low dose dobutamine. There is experimental evidence that The calculation of PVR is sensitive to pulmonary arterio- dobutamine has no effect on pulmonary vascular tone lar tone and dimensions, but can be misleading when doses below 10 µg/kg per min [10]. used to assess the functional state of the pulmonary circulation at increased or decreased cardiac output. In case of doubt, pulmonary hemodynamic determinations are better interpreted with the help of a pressure/flow diagram. The ideal is to define PVR using a multipoint pulmonary vascular pressure/flow plot.
References 1. Versprille A (1984) Pulmonary 4. Permutt S, Bromberger-Barnea B, 8. Zapol WM, Snider MT (1977). vascular resistance. A meaningless Bane HN (1962) Alveolar pressure, Pulmonary hypertension in severe variable. Intensive Care Med 10:51–53 pulmonary venous pressure and the acute respiratory failure. N Engl 2. McGregor M, Sniderman A (1985) vascular waterfall. Med Thorac J Med 296:476–480 On pulmonary vascular resistance: the 19:239–260 9. Kafi A S, Mélot C, Vachiéry JL, need for more precise definition. Am 5. Zhuang FY, Fung YC, Yen RT (1983) Brimioulle S, Naeije R (1998) Parti- J Cardiol 55:217–221 Analysis of blood flow in cat’s lung tioning of pulmonary vascular resis- 3. Landis EM (1982) The capillary with detailed anatomical and elasticity tance in primary pulmonary hyperten- circulation. In: Fishman AP, data. J Appl Physiol 55:1341–1348 sion. J Am Coll Cardiol 31:1372–1376 RichardsDW (eds) Circulation of the 6. Mélot C, Delcroix M, Lejeune P, 10. Pagnamenta A, Fesler P, Vandivinit A, Blood. Men and Ideas. American Leeman M, Naeije R (1995) Starling Brimioulle S, Naeije R (2003) Pulmo- Physiological Society, Bethesda, resistor versus viscoelastic models for nary vascular effects of dobutamine in Maryland, pp 355–406 embolic pulmonary hypertension. experimental pulmonary hypertension. Am J Physiol 267 (Heart Circ Physiol Crit Care Med (in press) 36:H817–827) 7. Nelin LD, Krenz GS, Rickaby DA, Linehan JH, Dawson CA (1992) A distensible vessel model applied to hypoxic pulmonary vasoconstriction in the neonatal pig. J Appl Physiol 73:987–994 Michael R. Pinsky Pulmonary artery occlusion pressure
Measurement of pulmonary artery occlusion pressure
Balloon occlusion
Intravascular pressure, as determined using a water-filled catheter connected to an electronic pressure transducer, measures the pressure at the first point of flow and with a frequency response determined primarily by the stiff- ness and length of the tubing. Balloon occlusion of the pulmonary artery stops all flow distal to that point until the pulmonary veins converge about 1.5 cm from the left Introduction atrium. Thus, if a continuous column of blood is present from the catheter tip to the left heart, then Ppao measures The bedside estimation of left ventricular (LV) perfor- pulmonary venous pressure at this first junction, or J-1 mance of critically ill patients is an important aspect of point, of the pulmonary veins [1]. the diagnosis and management of these patients. Ever since the introduction of the balloon flotation pulmonary catheterization, health care providers have used measure- Hydrostatic influences ments of pulmonary artery occlusion pressure (Ppao) to estimate both pulmonary venous pressure and LV pre- If one places the pressure transducer at a point lower load. However, the significance of any specific value for than the catheter tip, then the pressure recorded will be Ppao in the diagnosis and treatment of cardiovascular in- greater than the pressure at the catheter tip by an amount sufficiency in patients with diseases other than cardio- equal to that height difference. Since pressure is usually genic shock has never been validated. The reasons for measured in millimeters of mercury and the density of this continued uncertainty reflect both intrinsic inaccura- mercury relative to water is 13.6, for every 1.36 cm the cies in the measurement of Ppao and misconceptions transducer lies lower than the catheter tip the measured about their physiological significance. In this first Physi- pressure will increase by 1 mmHg. Placing the transduc- ological Note we shall discuss problems in the accurate er at the mid-axillary line references both the catheter tip measurement of Ppao at the bedside, while in the second and the transducer to a common cardiovascular point, Physiological Note we shall discuss the physiological such that even if the catheter tip is higher or lower than significance of Ppao measurements. this reference point, the hemodynamic measure still uses the heart’s level as zero [2].
Pressure profile during occlusion maneuver
The stiffer a vascular catheter is, the more faithfully it will transmit rapid changes in pressure at the catheter tip
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 69 DOI: 10.1007/978-3-642-01769-8_17, © Springer-Verlag Berlin Heidelberg 2009 20 70 M.R. Pinsky
Fig. 1 Strip chart recording of pulmonary artery pressure (Ppa) to balloon occlusion (Ppao) as hemodynamic condi- tions change. Note the change in pressure waveform with oc- clusion and the logarithmic na- ture of the pressure decay. Also note that when alveolar pres- sure compresses the pulmonary capillaries, the change in Ppao during ventilation exceeds the change in Ppa
to the electronic pressure transducer. When a pulmonary pulmonary vascular circuit up to the point of blood flow. arterial catheter’s distal balloon is inflated, three things Since the vasculature is compliant relative to the cathe- happen simultaneously (Fig. 1). First, the catheter rapid- ter, vascular pressure signals dampen. Thus, the two pri- ly migrates more distally into the pulmonary vasculature, mary aspects of Ppao measurements are that they are less carried by the force of pulmonary blood flow against the than pulmonary arterial diastolic pressure and their inflated balloon until it impacts upon a medium-sized waveforms are dampened relative to the non-occluded pulmonary artery whose internal diameter is the same or state. less than that of the balloon. This rapid swing induces a ringing of the pressure system as the tip impacts onto the smaller vessel. Second, as downstream pulmonary blood Pulmonary capillary pressure flow ceases, distal pulmonary arterial pressure falls in a double exponential fashion to a minimal value, reflecting It is very important to understand that Ppao is not the the pressure in the pulmonary vasculature downstream pulmonary capillary pressure. The pressure at the capil- from the point of occlusion. Third, the column of water lary site, however, can be estimated from the pulmonary at the end of the catheter is now extended to include the artery pressure tracing during an occlusion. At the in- 21 Pulmonary artery occlusion pressure 71 stant of balloon occlusion, the pressure distal to the cath- increases too much above left atrial pressure, the pulmo- eter tip decreases as pressure and blood discharge into nary vasculature in the zone of the occluded vessels may the downstream pulmonary vessels. Flow across the pul- collapse such that the occlusion pressure senses actually monary vasculature can be considered to reflect two dy- reflect more airway pressure (Paw) than Ppao. Such con- namic components: flow from a proximal pulmonary ar- ditions classically occur in West zones 1 and 2. Howev- terial capacitance system across an arterial resistance in- er, under conditions in which Paw exceeds left atrial to a pulmonary capillary capacitance system, then across pressure, Ppao may still reflect left atrial pressure and its a pulmonary venous resistor into the pulmonary venous change. The reasons are two-fold. First, if the vascular capacitor. Pressure in the latter is measured as Ppao. region occluded is in a dependent region, then pulmona- Thus, the downstream pulmonary arterial pressure de- ry capillary pressure will be greater than Ppao because of creases as the pulmonary arterial capacitor discharges its the effect of gravity on dependent vessels. Since balloon blood into the pulmonary capillary system. When the occlusion tends to occur in vessels with flow and more pressure in the pulmonary artery and capillary are equal, flow goes to dependent regions, this is a common event. the pressure continues to discharge across the venous re- However, even in non-dependent regions, a continuous sistor. Plotting the log of pulmonary arterial pressure column of fluid may persist in clear Zone 2 conditions over time during its pressure decay can separate these (i.e. Paw >Ppao) when Paw is not much greater than two distinct pressure decay patterns. A clear inflection Ppao. Presumably the corner vessel alveolar capillaries point is often seen, reflecting pulmonary capillary pres- remain patent while the mid-wall capillaries flatten. sure. Usually it occurs two-thirds of the way between Once Paw increases enough relative to left atrial pres- pulmonary diastolic pressure and Ppao, because two- sure, the distal tip of the balloon-occluded catheter sens- thirds of the pulmonary vascular resistance is in the arte- es Palv rather than Ppao. However, such conditions are ries. easy to identify at the bedside because the respiratory in- By separating the pressure drop into arterial and ve- creases in Ppao during this condition exceed the respira- nous components, one can calculate total pulmonary vas- tory swings in pulmonary arterial diastolic pressure. This cular resistance as the ratio of the difference between is because the pulmonary vasculature senses pleural mean pulmonary artery pressure and Ppao to cardiac out- pressure (Ppl) as its surrounding pressure, whereas the put, and pulmonary arterial and venous resistances as the alveoli sense Paw as their pressure. With inspiration, proportional amounts of this pressure drop on either side transpulmonary pressure, the difference between Ppl and of the capillaries [3]. Using such an analysis, it has been Paw, increases. Prior to balloon occlusion, pulmonary ar- shown that, in acute respiratory distress syndrome terial pressures reflect a patent vasculature, thus pulmo- (ARDS), once pulmonary vascular obliteration occurs, nary diastolic pressure will vary with pleural pressure. pulmonary capillary pressure often exceeds Ppao by a Thus, if Ppao senses Paw rather than Ppl, then it will in- considerable amount because pulmonary venous resis- crease more during inspiration [4] (Fig. 1). tance increases. Thus, some “low pressure” pulmonary edema characterized by low Ppao values in a hyperdy- namic state may actually reflect hydrostatic pulmonary Pleural pressure and pulmonary artery occlusion pressure edema. Since the pulmonary vasculature has a measurable re- Ventilation causes significant swings in Ppl. Pulmonary sistance, pressure inside the pulmonary arteries decreas- vascular pressures, when measured relative to atmo- es along its length. The original pulmonary artery cathe- spheric pressure, will reflect these respiratory changes. ter method to measure left-sided pressures was to To minimize the impact that ventilation has on the pul- “wedge” a very small catheter into a small pulmonary ar- monary vascular values measured, these variables are teriole, the so-called “wedge” pressure measurement. conventionally measured at end-expiration. This point is Wedge pressure is not Ppao. Since collateral flow and picked because it reflects a common point easily re- vessel diameter are different, wedge pressure tends to be turned to even as ventilation changes, rather than the av- slightly lower than Ppao values. Realistically, this is of erage hemodynamic position. During quiet spontaneous little importance, except in remembering not to call Ppao breathing, end-expiration occurs at the highest vascular “wedge pressure.” pressure values whereas, during positive-pressure breath- ing, end-expiration occurs at the lowest vascular pres- sure values. With assisted ventilation, where both spon- Airway pressure and pulmonary artery taneous and positive-pressure breathing coincide, it is of- occlusion pressure ten difficult to define end-expiration. In addition, a high respiratory drive during spontaneous or assisted breath- Since a continuous column of fluid is required for a stop- ing usually results in expiratory muscles recruitment, flow pulmonary arterial catheter to sense pulmonary ve- making end-expiration unreliable for estimating intravas- nous pressure at the J-1 point, if alveolar pressure (Palv) cular pressures [5]. These limitations are the primary 22 72 M.R. Pinsky reasons for inaccuracies in estimating Ppao at the bed- fall in Ppao to a nadir value. This nadir Ppao value accu- side. rately reflects on-PEEP LV filling pressure in patients on 15 cmH2O or less [6]. It may be accurate above this val- ue, but that question has not been studied. However, in Positive-end expiratory pressure (PEEP) subjects with intrinsic PEEP, transiently removing them and hyperinflation from a ventilator may not result in lung deflation to off- PEEP levels. Ppao values can still be measured, but using Even if one measures an actual Ppao value reflecting a a more indirect technique. One may calculate a transmu- continuous column of fluid from the catheter tip to the J- ral value of end-expiratory Ppao as a ratio of airway to 1 point and correctly identified end-expiration, one may pleural pressure changes during a breath. Since Ppao will still overestimate Ppao if Ppl is elevated. Hyperinflation, vary with Ppl and Paw can be measured directly, the pro- either due to extrinsic or intrinsic PEEP, will increase portional transmission of pressure from the airway to the end-expiratory Ppl relative to the increase in PEEP and pleural surface, referred to as the index of transmission lung and chest wall compliance. Because Palv is partly (IT), equals the ratio of the differences between changes transmitted to Ppl, end-expiratory Ppao overestimates in Ppao and Paw during a breath. Thus, one may calculate LV filling pressure if PEEP is present. Unfortunately, it the transmural Ppao = end-expiratory Ppao –(IT × total is not possible to predict with much accuracy the degree PEEP), where IT is an index of transmission of Palv to to which increases in PEEP will increase Ppl. One can Ppao calculated as IT = (end-inspiratory Ppao –end-expi- remove a patient from PEEP to measure Ppao, but this ratory Ppao)/(plateau pressure –total PEEP). Paw needs will cause blood volume shifts with increases in Ppao to be transformed from centimeters of water into millime- that will not reflect the on-PEEP cardiovascular state. ters of mercury. Recall that total PEEP equals intrinsic What the clinician needs is a measure of LV filling pres- plus extrinsic PEEP. This formula, though complicated, sure while on PEEP. Regrettably, because of differences can be easily derived at the bedside from readily avail- in lung and chest wall compliance among patients and able values, and carries the added advantage of not re- changes in each over time, one cannot assume a fixed re- quiring airway disconnection to derive it [7]. lation between increases in Paw and Ppl. Thus, in sub- jects with compliant lungs but stiff chest walls most of the increase in PEEP will be reflected in an increase in Summary Ppl, whereas in those with markedly reduced lung com- pliance Ppl may increase very little, if at all, with the ap- Technical limitations in the accurate measurement of plication of PEEP [6]. Ppao and its change in response to therapy are daunting, Two techniques allow for the accurate estimation of but surmountable. By using a firm understanding of the Ppao even if lung hyperinflation is present. In patients on technical determinants of Ppao during ventilation one PEEP without airflow obstruction, measuring Ppao at may measure it accurately at the bedside under almost end-expiration while the airway is transiently disconnect- any situation. In the next Physiological Note we shall ad- ed (<3 s) results in a sudden loss of hyperinflation and a dress the physiological significance of Ppao values.
References
1. Swan HJC, Ganz W, Forrester JS, 3. Maarek J, Hakim T, Chang H (1990) 6. Pinsky MR, Vincent JL, DeSmet JM Marcus H, Diamond G, Chonette D Analysis of pulmonary arterial pressure (1991) Estimating left ventricular (1970) Catheterization of the heart in profile after occlusion of pulsatile blood filling pressure during positive end- man with the use of a flow-directed bal- flow. J Appl Physiol 68:761–769 expiratory pressure in humans. Am Rev loon tipped catheter. N Engl J Med 4. Teboul JL, Besbes M, Andrivet P, Respir Dis 143:25–31 283:447–451 Besbes M, Rekik N, Lemaire F, 7. Teboul JL, Pinsky MR, Mercat A, 2. Rajacich N, Burchard KW, Hasan FM, Brun-Buisson C (1992) A bedside Anguel N, Bernardin G, Achard JM, Singh AK (1989) Central venous index assessing the reliability of pulmo- Boulain T, Richard C (2000) pressure and pulmonary capillary wedge nary artery occlusion pressure Estimating cardiac filling pressure pressure as estimate of left atrial pres- measurements during mechanical in mechanically ventilated patients with sure: effects of positive end- ventilation with positive end-expiratory hyperinflation. Crit Care Med expiratory pressure and catheter tip mal- pressure. J Crit Care 7:22–29 28:3631–3636 position. Crit Care Med 17:7–11 5. Hoyt JD, Leatherman JW ( 1997) Interpretation of pulmonary artery occlusion pressure in mechanically ven- tilated patients with large respiratory ex- cursions in intrathoracic pressure. Inten- sive Care Med 23:1125–1131 Michael R. Pinsky Clinical significance of pulmonary artery occlusion pressure
Abstract Background: Ppao values Keywords Bedside measurements · are routinely used to assess pulmo- Pulmonary hemodynamics · Left nary vascular status and LV perfor- ventricular performance · Critically mance. Regrettably, under many ill patients · Pulmonary artery common clinically relevant condi- occlusion pressure · Pulmonary tions, even when Ppao values are vascular status measured accurately, Ppao values at baseline and in response to therapy often reflect an inaccurate measure of cardiovascular status. Results and conclusions: Thus, caution should be used when apply- ing measures of Ppao in determining therapy if changes in RV volume, hyperinflation, or LV diastolic compliance are simultaneously occurring.
Introduction status and LV preload, and (d) LV performance. We ad- dress each separately. Balloon floatation pulmonary arterial catheterization has permitted the bedside estimation of pulmonary hemody- namics and left ventricular (LV) performance of critical- Pulmonary edema ly ill patients. Present-day pulmonary artery catheters can routinely estimate cardiac output and right ventricu- Acute pulmonary edema can be life threatening because lar (RV) ejection fraction, by the thermodilution tech- of the systemic hypoxemia that it creates. Pulmonary ede- nique, mixed venous oxygen saturation, by reflective ox- ma can be caused by either elevations in pulmonary cap- imetry, and three intrapulmonary vascular pressures: illary pressure (hydrostatic or secondary pulmonary ede- right atrial, pulmonary arterial and pulmonary artery oc- ma), increased capillary and/or alveolar epithelial perme- clusion pressure. Of all of these, pulmonary artery occlu- ability (primary pulmonary edema), or a combination of sion pressure (Ppao) is perhaps subject to the most error the two. If pulmonary capillary pressure increases above in its measurement and interpretation. The previous 18–20 mmHg, increased fluid flux across the capillary "Physiological Note" discussed problems in the accurate membrane occurs, promoting alveolar flooding. Howev- measure of Ppao at the bedside. In this one we discuss er, if capillary or alveolar cell injury is present, alveolar the physiological significance of Ppao measures. flooding can occur at much lower pulmonary capillary Pulmonary artery occlusion pressure is used most of- pressures. Measures of Ppao are commonly used to deter- ten in the bedside assessment of: (a) pulmonary edema, mine the cause of pulmonary edema. Thus Ppao values (b) pulmonary vasomotor tone, (c) intravascular volume lower than 18–20 mmHg suggest a nonhydrostatic cause,
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 73 DOI: 10.1007/978-3-642-01769-8_18, © Springer-Verlag Berlin Heidelberg 2009 176 74 M.R. Pinsky whereas values higher than 18–20 mmHg suggest a hy- causes are primarily within the lung, whereas if PVR is drostatic cause of pulmonary edema [1]. However, these normal then LV dysfunction is the more likely cause [2]. are not hard values. Regrettably, PVR is not a good measure of pulmonary Ppao may be lower than 18–20 mmHg in a patient vasomotor tone. Pulmonary vascular pressure does not with secondary pulmonary edema if either the Ppao in- decrease linearly from input to output and may vary crease had been transient and is now gone, or if pulmo- from region to region due to lung distention, structural nary capillary pressure significantly exceeds Ppao. Tran- damage and acute processes, such as hyperinflation, sient severe LV dysfunction can transiently increase pneumonia, emphysema, pulmonary fibrosis, and acute Ppao during upper airway obstruction with vigorous in- lung injury. Thus PVR as a lumped parameter may not spiratory efforts (inspiratory stridor, obstructive sleep ap- identify local injury or define why PVR is elevated. As nea), unstable angina (reversible ischemia), and arrhyth- alveolar pressure increases above Ppao (West zone 2 mias. Increased pulmonary capillary pressure can occur conditions) alveolar pressure becomes the backpressure due to massive sympathetic discharge (e.g., intracerebral to pulmonary blood flow. Thus measures aimed at de- hemorrhage and heroin overdose), which rapidly revers- creasing pulmonary vasomotor tone (e.g., inhaled nitric es, but the pulmonary edema lingers. Furthermore, per- oxide) have little effect on Ppa [3]. Furthermore, with sistently elevated pulmonary capillary pressures may co- nonhomogeneous lung disease blood flow is preferential- exist with normal Ppao values if pulmonary venous re- ly shifted to those circuits with the lowest resistance, sistance is increased and cardiac output not decreased thus making the lung vascular pathology appear less than (e.g., high altitude pulmonary edema, pulmonary veno- it actually is. By examining the change in Ppa in re- occlusive disease, and end-stage acute respiratory dis- sponse to interventions that alter cardiac output, one may tress syndrome). obtain a better understanding of the determinants of pul- Ppao may be higher than 18–20 mmHg in a patient monary hypertension. If the extrapolated zero-flow pul- without hydrostatic pulmonary edema. Since Ppao is monary artery pressure created from such a maneuver is measured relative to atmospheric pressure, elevations in much higher than Ppao, Ppao is probably not the down- pleural pressure artificially elevate Ppao values. Any in- stream pressure to flow thus measures aimed at reducing crease in pleural pressure increases measured Ppao. Hy- zone 2 conditions (reverse hyperinflation) should be perinflation, either intrinsic or extrinsic, increases pleu- more effective at decreasing Ppa. ral pressure. Furthermore, when active expiratory muscle effort persists, pleural pressure increases. Intravascular volume status and LV preload
Pulmonary vasomotor tone Hemodynamically unstable patients often benefit for fluid resuscitation, as manifested by increases in organ Increased pulmonary arterial pressure (Ppa) impedes RV perfusion and function, resolution of lactic acidosis, and ejection, causing RV dilation and a decreased cardiac increased survival. A fundamental tenant of such therapy output. If pulmonary hypertension occurs rapidly, as is that fluid resuscitation increases LV end-diastolic vol- with massive pulmonary embolism or marked hyperin- ume (EDV), and that such increases in EDV translates flation, acute cor pulmonale and cardiovascular collapse into increased cardiac output. For a given level of con- also occurs. Pulmonary hypertension can be due to either tractile function, increasing LV EDV increases both LV an increase in pulmonary vasomotor tone or passive in- stroke volume (and thus cardiac output) and LV stroke creases in Ppao due to LV failure. The pulmonary circu- work. It is difficult to make repeated measures of LV lation normally has a low resistance, with pulmonary ar- EDV at the bedside to titrate fluid resuscitation and va- terial diastolic pressure only slightly higher than Ppao soactive therapy. Ppao values are often taken to reflect and mean pulmonary arterial pressure thus a few mmHg LV filling pressure, and by inference LV EDV. Opera- higher than Ppao Global pulmonary vascular resistance, tionally, subjects with cardiovascular insufficiency and a by Ohm's law, equals the ratio of the driving pressure low Ppao are presumed to be hypovolemic and initially (mean Ppa−Ppao) and flow (cardiac output). Normal treated with fluid resuscitation, whereas patients with pulmonary vascular resistance is between 1.8 and similar presentations but and elevated Ppao are not. Al- 3.1 mmHg l−1 min−1. Usually these values are multiplied though there is no accepted high and low Ppao values for by 80 to give normal pulmonary vascular resistance which LV under filling is presumed to occur, Ppao val- range of 150–250 dynes s−1 /cm−5 of. Thus by measuring ues lower than 10 mmHg are usually used as presumed Ppa, Ppao, and cardiac output in patients with pulmonary evidence of a low LV EDV, whereas values higher than hypertension, one may determine whether the increase in 18 mmHg suggest a distended LV [4]. Ppa is due to increased pulmonary vascular resistance Regrettably, of all the uses of Ppao in the manage- (PVR) or a passive pressure build-up. If pulmonary hy- ment of the critically ill, this one use is the least accu- pertension is associated with an increased PVR then the rate. The reasons for this are multiple and relate to the 177 Clinical significance of pulmonary artery occlusion pressure 75
sessment of LV performance is important in determining the causes of cardiovascular insufficiency and the poten- tial of the patient to response to fluid challenge, increas- ing arterial pressure and afterload reduction. Although many factors converge on the resultant LV stroke vol- ume, including valvular function, synchrony of contrac- tion, and diastolic filling time the four primary determi- nants of LV performance are preload (LV EDV), after- load (LV wall stress, which is itself the product of LV EDV and diastolic arterial pressure), heart rate, and con- tractility. To the extent that Ppao mirrors LV EDV, Ppao can be used to construct Starling curves that plot Ppao vs. LV stroke work (LV stroke volume × developed pres- sure). Patients with heart failure can be divided into four Fig. 1 Schematic representation of the relationship between left groups depending on their Ppao (>or
LV performance
As stated above, LV EDV is a fundamental determinant of stroke volume and LV stroke work. The bedside as- 178 76 M.R. Pinsky
References
1. Fishman AP (1985) Pulmonary circula- 2. Abraham AS, Cole RB, Green ID, 4. Forrester JS, Diamond G, Chatterjee K, tion. In: Handbook of physiology. The Hedworth-Whitty RB, Clarke SW, Swan HJC (1976) Medical therapy of Respiratory system. Circulation and Bishop JM (1969) Factors contributing acute myocardial infarction by applica- nonrespiratory functions, vol 1. Ameri- to the reversible pulmonary hyperten- tion of hemodynamic subsets. N Engl J can Physiological Society, Bethesda, sion of patients with acute respiratory Med 295:1356–1362 pp 93–166 failure studied by serial observations 5. Raper R, Sibbald WJ (1986) Misled during recovery. Circ Res 24:51–60 by the wedge? The Swan-Ganz catheter 3. West JB, Dollery CT, Naimark A (1964) and left ventricular preload. Chest Distribution of blood flow in isolated 89:427–434 lung; relation to vascular and alveolar pressures. J Appl Physiol 19:713–724 Jukka Takala Pulmonary capillary pressure
What are the components of the pressure drop across the pulmonary vasculature? The resistance to flow across the pulmonary circulation results in the pressure drop from the large pulmonary ar- tery to the left atrium. This resistance can be separated into arterial and venous components, with relatively little resistance seen in the compliant capacitance pulmonary capillary vessels. This physical situation can be modeled as an electrical circuit consisting of two or several resis- tances in series with one or several capacitors connected between the resistances (Fig. 1). The simplest model as- sumes one arterial and one venous resistance with one capacitance located in the capillaries [2, 3]. A three- compartment model consisting of compliant arterial, capillary and venous capacitance compartments between four resistances (resistance of large and small arterial and venous vessels, respectively) is probably more repre- Introduction sentative but does not improve the accuracy of measur- ing pulmonary capillary pressure [1]. Pulmonary capillary pressure is a primary determinant of Because of this series resistance interposed by a com- fluid flux across the pulmonary capillary wall [1]. In- pliant pulmonary capillary network, pulmonary capillary creasing pulmonary capillary pressure increases fluid pressure can be measured from the pressure decay pro- flux out of the capillaries into the interstitium and in the file of an acute pulmonary artery balloon occlusion ma- extreme induces pulmonary edema. Pulmonary capillary neuver. When the pulmonary artery is occluded, there is pressure is itself determined by the mean pulmonary ar- a rapid decrease in blood flow as the occluded down- tery pressure, pulmonary vascular resistance, and total stream pulmonary artery discharges its blood volume se- blood flow. The distribution of the pulmonary vascular quentially into the pulmonary capillaries across the arte- resistance from precapillary arterial to postcapillary ve- rial resistance and then into the pulmonary veins across nous compartments varies. Accordingly, at any given the venous resistance. This two-part pressure discharge blood flow rate the hydrostatic pressure in the pulmonary is reflected in the pulmonary artery pressure decay capillaries depends on the magnitude of the resistance to curve. The initial rapid pressure drop approaches the blood flow across the pulmonary circulation and its dis- pressure in the capillaries (the main capacitance compo- tribution between precapillary and postcapillary vessels. nent) as the blood trapped in the downstream pulmonary Since pulmonary capillary pressure cannot be directly capillaries equilibrates with pulmonary capillary pres- measured, the presence and relevance of increased pul- sure. This is followed by a slower pressure decrease ap- monary capillary hydrostatic pressures to values in ex- proaching the pulmonary artery occlusion pressure as cess of pulmonary artery occlusion pressure are often pulmonary capillary pressure equilibrates with pulmona- overlooked. ry venous pressure (Fig. 1a). The initial pressure drop re-
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 77 DOI: 10.1007/978-3-642-01769-8_19, © Springer-Verlag Berlin Heidelberg 2009 891 78 J. Takala
Fig. 1 A schematic representa- tion of the electric circuit ana- logue of the pulmonary circula- tion is superimposed on the two pressure recordings. a Pulmo- nary artery pressure decay after the balloon of the Swan-Ganz catheter has been occluded. For better visualization the occlu- sion trace is superimposed on a nonoccluded trace, both record- ed during an expiratory hold during mechanical ventilation. b Capillary pressure has been estimated from the trace shown in a. An additional trace using 20 data point moving average smoothing of the original trace (collected at 100 Hz) is super- imposed on the curves. This further facilitates the visual es- timation of the capillary pres- sure by defining more exactly the point of divergence of the occluded and nonoccluded curves. In addition, an expo- nential curve has been fitted on the curve 0.3–2 s after occlu- sion. This fitted curve has then been extrapolated to the time of occlusion to provide the capil- lary pressure
flects the proximal arterial resistance, and the slower lation by the lung lymphatics. When the capacity of the pressure drop reflects the distal, venous resistance. The lymphatics is exceeded, first interstitial and then alveolar model shown in Fig. 1 consisting of serial resistance and edema ensues. The rate of fluid filtration from the capil- capacitances does not represent the simultaneous dis- lary to the interstitium can be estimated by the Starling charge of the different capacitance components of the equation: pulmonary circulation. Nevertheless, it provides a close approximation of the decay of pressure after a pulmona- ry arterial occlusion for most clinical conditions.
where P=hydrostatic pressure, π=oncotic pressure, What is the physiological relevance Kfc=capillary filtration coefficient (product of capillary of the pulmonary capillary pressure? wall hydraulic conductivity and capillary surface area), and Kd=reflection coefficient (values from 0 to 1; 0=cap- Pulmonary capillary pressure is a major determinant of illary freely permeable to proteins, 1=capillary imperme- fluid flux across the capillary wall and lung edema for- able to proteins). When fluid efflux increases for any mation. Under normal conditions some fluid and protein reason, lymph flow increases as well, washing out inter- is filtered through the capillary into the pulmonary inter- stitial protein and decreasing πinterstitium, thus increasing stitium and subsequently drained into the systemic circu- the oncotic gradient for fluid flux back into the blood 892 Pulmonary capillary pressure 79 and counteracting edema formation. When the perme- mately one-third of the pressure drop occurring over the ability to protein increases, the influence of the term Kd venous resistance. However, a selective increase in pul- (πcapillary−πinterstitium) in the Starling equation is reduced monary venous resistance can occur and directly in- due to the decreased Kd as well as the decreased creases pulmonary capillary pressure in proportion to (πcapillary−πinterstitium) (loss of protein to the tissue). How- blood flow. Many normal physiological responses and ever, no matter what the oncotic pressure gradient, based disease states are associated with increased pulmonary on the Starling equation, increasing pulmonary capillary venous resistance. Increased pulmonary vasomotor tone pressure always increases fluid efflux. If the capillary occurs with hypoxic pulmonary vasoconstriction. If as- permeability to protein is normal, a higher capillary pres- sociated with increased blood flow, as with exercise at sure is needed for a given rate of fluid efflux. Converse- high altitude, one can rapidly understand how high alti- ly, in the presence of increased capillary permeability, tude pulmonary edema may occur. Disease states associ- lower capillary pressure is needed for a given rate of flu- ated with transient massive sympathetic discharge, such id efflux. as acute cerebral hemorrhage and heroin overdose, pro- Since the capillary pressure is the major determinant duce transient massive increases in pulmonary capillary of fluid efflux from the capillaries both in normal and pressure. Finally, during the reparative phase of acute abnormal permeability states, division between “hydro- lung injury, pulmonary fibrosis may occur. Fibrosis is static” or “cardiogenic” lung edema and “permeability” indiscriminate of the vasculature and obstructs all ves- or “low-pressure” edema when pulmonary capillary sels, thus making increased pulmonary vascular resis- pressure is unknown is artificial and arbitrary. Indeed, tance a hallmark of end-stage acute lung injury. Persis- capillary hydrostatic pressure and capillary permeability tent pulmonary edema in a patient with late-stage acute interact in all types of lung edema. An increase in the respiratory distress syndrome may reflect occult hydro- pulmonary venous resistance increases the pulmonary static pulmonary edema. capillary pressure. Under these conditions the pulmonary artery occlusion pressure or left atrial pressure underesti- mates the pulmonary capillary pressure [4, 5]. Further- How can the pulmonary capillary pressure more, the pressure difference between pulmonary capil- be estimated at the bedside? lary pressure and left atrial pressure varies with blood flow. The higher the blood flow then for the same pul- Bedside assessment of pulmonary capillary pressure is monary venous resistance the greater the pulmonary cap- based on visual inspection of the pulmonary artery pres- illary pressure and the greater the pressure drop. sure decay during balloon occlusion using a balloon floa- tation pulmonary artery catheter [1, 2, 3] (Fig. 1). Ideally the occlusion should be performed during an expiratory How to interpret an increased transpulmonary hold to avoid the effect of dynamic changes in intratho- pressure gradient? racic pressure and lung volume on the pressure curve. After occlusion, one sees a rapid decrease in pressure, A positive pressure gradient must exist between the pul- followed by a slower pressure decrement approaching monary arterial diastolic pressure and the left atrium for the pulmonary artery occlusion pressure (Fig. 1a). When blood to flow. Under normal circumstances this gradient is a straight line is drawn tangent to the rapid component, less than 6–8 mmHg, increasing slightly with increasing pulmonary capillary pressure can be estimated as the flow and decreasing to near zero at rest when pulmonary point at which the pressure transient begins to deviate blood flow almost ceases during each diastole. A widen- from the rapid portion of the pressure tracing (Fig. 1b). ing gradient between the pulmonary arterial diastolic pres- The assessment can be facilitated by the use of a strip sure and the left atrial pressure is a signal of increased pul- chart recorder or a computer sampling of the signal, and monary vascular resistance, increased pulmonary blood by superimposing the occlusion tracing on a nonocclud- flow, or both, and is an indicator that pulmonary capillary ed one (Fig. 1a). More sophisticated approaches include pressure may exceed pulmonary artery occlusion pressure. the use of moving average smoothing of the pressure sig- While the pulmonary artery occlusion pressure may over- nal and mathematical curve fitting of the signal (Fig. 1b). estimate the left atrial pressure in the presence of Starling The visual inspection method has been thoroughly vali- resistor forces causing pulmonary venous collapse [6], an dated in experimental conditions and gives values very increased gradient between the pulmonary arterial diastol- similar to those of the more complex approaches. In the ic pressure and the pulmonary artery occlusion pressure is clinical routine a rough estimate of capillary pressure still a valid indicator of increased capillary pressure. An can even be obtained directly from the monitor screen by isolated increase in the arterial resistance does not in- freezing the pressure trace when measuring the pulmona- crease the capillary pressure by itself. ry artery occlusion pressure. Normally two-thirds of the transpulmonary pressure To assess the risk of pulmonary edema in the presence drop occurs over the arterial resistance, with approxi- of pulmonary hypertension and increased transpulmona- 893 80 J. Takala ry pressure gradient it is necessary to estimate the capil- imize pulmonary capillary pressure may include reduc- lary pressure. Importantly, once pulmonary capillary ing total blood flow (hypothermia, sedation, paralysis) pressure is known, the arterial and venous components and the use of pulmonary vasodilator substances (inhaled of the pulmonary vascular resistance can be calculated as nitric oxide, calcium channel blockers, and infusions of the ratio of their respective pressure gradients (pulmona- potent vasodilators such as prostaglandin E, prostacy- ry artery diastolic to pulmonary capillary and pulmonary clin, nitroglycerin, hydralazine) with appropriate inter- capillary to left atrial) to total blood flow. If pulmonary mittent monitoring of pulmonary capillary pressure to venous resistance is elevated, effective strategies to min- document its reduction.
References
1. Cope DK, Grimbert F, Downey JM, 3. Cope DK, Allison RC, Parmentier JL, 6. Fang K, Krahmer RL, Rypins EB, Law Taylor AE (1992) Pulmonary capillary Miller JN, Taylor AE (1986) Measure- WR (1996) Starling resistor effects on pressure: a review. Crit Care Med ment of effective pulmonary capillary pulmonary artery occlusion pressure in 20:1043–1056 pressure using the pressure profile after endotoxin shock provide inaccuracies in 2. Holloway H, Perry M, Downey J, Parker pulmonary artery occlusion. Crit Care left ventricular compliance assessments. J, Taylor A (1983) Estimation of effec- Med 14:16–22 Crit Care Med 24:1618–1625 tive pulmonary capillary pressure in in- 4. Pellett AA, Lord KC, Champagne MS, tact lungs. J Appl Physiol 54:846–851 deBoisblanc BP, Johnson RW, Levitzky MG (2002) Pulmonary capillary pres- sure during acute lung injury in dogs. Crit Care Med 30:403–409 5. Benzing A, Bräutigam P, Geiger K, Loop T, Beyer U, Moser E (1995) In- haled nitric oxide reduces pulmonary transvascular albumin flux in patients with acute lung injury. Anesthesiology 83:1153–1161 François Jardin Ventricular interdependence: how does it impact on hemodynamic evaluation in clinical practice?
can alter pericardial pressure independent of esophageal pressure, such as hyperinflation, pericardial effusions and acute RV dilation Another aspect of ventricular interdependence relates to the fact that both ventricles are arranged in series. Since LV filling requires RV output, adequate left ventricular filling can be only supplied by adequate RV output. In turn, adequate RV output requires adequate venous return, and nonobstructed pulmonary circulation.
The “age of oil lamps”: ventricular interdependence The left (LV) and right ventricles (RV) are enclosed in a renders inaccurate the classical hemodynamic evalua- stiff envelope, the pericardium. They have similar end- tion by a pulmonary artery catheter. For a long time, diastolic volumes, and there is no free space for acute fluid management in critically ill patients requiring me- ventricular dilatation within a normal pericardial space. chanical ventilation was guided by measurement of both Thus, when RV end-diastolic volume increases owing to RV and LV filling pressures. Moreover, evidence of de- increased RV loading, it can only occur at the expense of the space devoted to the left ventricle, which is prevent- ed from dilating to as large an end-diastolic volume as it would otherwise given its distending pressure. From a practical point of view this reduced LV end-diastolic vol- ume is accompanied by decreases in LV diastolic com- pliance, such that for the same LV distending pressure LV end-diastolic volume is less. This point was de- scribed in a previous Physiological Note [1]. LV im- paired relaxation by RV enlargement is evidenced by Doppler examination of mitral flow velocity (Fig. 1). Such competition for end-diastolic volume between the right and left ventricles is enhanced when mediasti- nal pressure (i.e., pleural, pericardial, or both) or lung volume are increased. Moreover, relative ventricular Fig. 1 Illustration of left ventricular (LV) relaxation impairment compliance, that is, the relation between LV end-diastol- by right ventricular (RV) dilatation, in a mechanically ventilated patient with acute respiratory distress syndrome. During the first ic pressure and LV end-diastolic volume, is markedly af- day of mechanical ventilation (left) a normal right ventricular size, fected by pericardial pressure. If pericardial pressure observed in the two-dimensional view, was associated with a nor- were to increase but not accounted for in the calculation mal pattern of Doppler mitral flow velocity, with a preeminent of LV distending pressure, LV diastolic compliance peak velocity of the E wave (early filling) and a less marked peak velocity of the A wave (atrial systole). After 48 h of respiratory would appear to be decreased. Often esophageal pressure support (right) right ventricular dilatation, observed on the two-di- is used to estimate intrathoracic pressure and, by exten- mensional view, was associated with a modified pattern of Dopp- sion, pericardial pressure. Importantly, many processes ler mitral flow velocity, with equalization of peak velocities
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 81 DOI: 10.1007/978-3-642-01769-8_20, © Springer-Verlag Berlin Heidelberg 2009 362 82 F. Jardin pressed systolic ventricular function was based upon ob- servational changes in filling pressure related to changes in cardiac output during a fluid challenge. Pulmonary arterial catheterization is commonly used to assess these parameters. Direct measures of right atrial (or central venous, CV) pressure (P) and pulmonary artery occlu- sion pressure (Ppao) can be made from a pulmonary ar- terial catheter. And using a distal tip thermistor, pulmo- nary blood flow as a surrogate of cardiac output can be measured. Clinically CVP is used to reflect RV filling pressure and Ppao LV filling pressure. This allows the construction of RV and LV “Frank-Starling curves” when filling pressures are plotted against stroke volume or cardiac output. It is theoretically possible to discrimi- Fig. 2 Illustration of the gauge for central blood volume constitut- nate between an insufficient preload (requiring volume ed by vena caval collapsibility. Before volume expansion (left) the patient exhibited a marked reduction in superior vena caval diame- expansion) and a contractile defect (requiring inotropic ter during tidal ventilation. After volume expansion (right) inspi- support) in the hemodynamically unstable patient using ratory reduction in vena caval diameter was minimized this analysis. A major drawback of the above method results from the lack of measurement of ventricular volume. Since RV and LV diastolic compliance can and do vary rapidly in unstable patients, filling pressures or their changes in response to therapy may poorly reflect preload. Regretta- bly, at the present time it is not possible to measure diastolic compliance at the bedside. As a result a high filling pressure may coexist with a reduced preload if ventricular compliance is low, and a low filling pressure may coexist with a normal preload if ventricular compli- ance is high [2]. This drawback characterizes particularly patients with acute respiratory distress syndrome, in Fig. 3 Two illustrations of ventricular interdependence, where whom a progressive increase in PEEP produces a pro- acute right ventricular dilatation is associated with a reduced size gressive increase in measured LV end-diastolic pressure, of the left ventricular cavity. This interdependence was observed associated with a progressive decrease in LV end-diastol- by a long-axis view, in a patient with massive pulmonary embo- ic size [3]. lism (left, transthoracic examination) and in a patient with acute respiratory distress syndrome (right, transesophageal examination) The “age of electricity”: ventricular interdependence does not affect the accuracy of hemodynamic evaluation by bedside echocardiography. Whereas knowledge of RV and LV end-diastolic dimensions can be obtained ventricular diastolic compliance is fundamental in inter- by bedside echocardiography. These measurements are preting ventricular intracavitary pressure, it is less im- particularly relevant in the clinical setting of acute cor portant with the use of echocardiography, which permits pulmonale, where hemodynamic impairment resulting direct visualization of venous distention, biventricular from ventricular interdependence has been documented maximal chamber size, and a rough approximation of (Fig. 3) [5]. Echocardiographic measurements of LV size systolic function. has documented an inability of the left ventricular of In clinical practice, the adequacy of venous return un- septic patients to dilate [6]. der respiratory support can be evaluated by inspection of respiratory changes in the superior vena caval diameter (Fig. 2). In particular, a high collapsibility index (i.e., major expiratory diameter minus minor inspiratory diam- eter divided by major expiratory diameter) of the superi- or vena cava identified potential differences between measured CVP and actual RV filling pressure, because the external pressure for the vessel, which is pleural pressure, causes vascular collapse. Such a condition in a hemodynamically unstable person denotes a need for volume expansion [4]. 363 Ventricular interdependence 83
References
1. Pinsky MR (2003) Significance 3. Jardin F, Farcot JC, Boisante L, 6. Vieillard-Baron A, Schmitt JM, of pulmonary artery occlusion Curien N, Margairaz A, Bourdarias JP Beauchet A, Augarde R, Prin S, pressure. Intensive Care Med 29:19–22 (1981) Influence of positive end- Page B, Jardin F (2001) Early preload 2. Jardin F, Bourdarias JP (1995) Right expiratory pressure on left ventricular adaptation in septic shock? A heart catheterization at bedside: performance. N Engl J Med transesophageal echocardiographic a critical view. Intensive Care Med 1981:304:387–392 study. Anesthesiology 94:400–406 21:291–295 4. Vieillard-Baron A, Augarde R, Prin S, Page B, Beauchet A, Jardin F (2001) Influence of superior vena caval zone condition on cyclic changes in right ventricular outflow during respiratory support. Anesthesiology 95:1083–1088 5. Vieillard-Baron A, Prin S, Chergui K, Dubourg O, Jardin F (2002) Echo-Doppler demonstration of acute cor pulmonale at the bedside in the medical intensive care unit. Am J Respir Crit Care Med 166:1310–1319 Fran ois Jardin Cyclic changes in arterial pressure during mechanical ventilation
of inspiratory increase in transpulmonary pressure in determining these changes has been demonstrated by chest strapping in a clinical study performed in acute respiratory distress syndrome (ARDS) patients [4]. Me- chanical lung inflation produces a sudden increase in distal airway pressure, whereas, at the same time, pleu- ral pressure increases to a lesser extent. As a result, transpulmonary pressure, i.e., alveolar pressure minus pleural pressure, is suddenly increased. These cyclic changes in transpulmonary pressure have an instanta- neous impact on the pulmonary circulation, particularly on the capillary bed, which is intra-alveolar. The blood present in this capillary bed, approximately 100 ml, For a given level of arterial distensibility, the amplitude constitutes, with the blood present in pulmonary veins, of the arterial pulse is directly related to the left ventric- the filling reserve of the left ventricle [2, 5, 6]. As a ular (LV) stroke volume. Thus, rapid changes in arterial result, the pulmonary capillary bed is emptied, and LV pulse pressure, the difference between systolic and dia- filling is increased, resulting in an inspiratory increase in stolic pressures, essentially reflect changes in LV stroke LV ejection [6]. volume. At the same time, the sudden increase in transpul- During mechanical ventilation, cyclic inspiratory in- monary pressure increases right ventricular (RV) outflow creases in pleural pressure are transmitted to the intra- impedance [4], and produces a drop in RV ejection [6, 7]. thoracic aorta, resulting in a cyclic inspiratory increase in This drop causes a delay in re-filling of the pulmonary arterial pressure [1]. However, this transmission of pleural capillary bed, and, as a consequence, a late inspiratory pressure produces a similar increase in both systolic and and early expiratory decrease in LV filling produces an diastolic pressures, and does not increase the arterial pulse expiratory decrease in LV ejection [6]. pressure. The amplitude of cyclic changes in arterial pulse Cyclic changes in arterial pulse pressure during posi- pressure, pulse pressure variation (PPV), can be measured tive-pressure ventilation, in patients ventilated on con- as a percentage of expiratory decrease, as proposed by trolled mode and without spontaneous breathing, can be Michard et al. [8]. In the original formula given by these described as a succession of inspiratory increases, fol- authors, PPV = maximal inspiratory value minimal lowed by expiratory decreases [2]. The inspiratory in- expiratory value/1/2 (maximal inspiratory value + mini- crease in systolic arterial pressure observed in this setting mal expiratory value) [8]. With the recently accepted has also been termed delta Up (DUp) (Fig. 1, upper respiratory strategy limiting airway pressure (low stretch panel), whereas the expiratory decrease in systolic arterial strategy), PPV, which is present in all mechanically pressure has been termed delta Down (DDown) (Fig. 1, ventilated patients, is usually small, between 1% and 5%. lower panel) [3]. This amplitude may be increased by either hypervolemia Cyclic changes in arterial pulse pressure during res- or hypovolemia. piratory support are produced by cyclic changes in pul- When hypervolemia is present, the amount of blood monary venous return altering LV preload. The main role filling the pulmonary capillary bed is increased, and,
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 85 DOI: 10.1007/978-3-642-01769-8_21, © Springer-Verlag Berlin Heidelberg 2009 1048 86 F. Jardin
Fig. 1 Two illustrative exam- ples of simultaneous recording of invasive arterial pulse and tracheal pressure in mechani- cally ventilated patients. In the upper panel, a short disconnec- tion from the respirator shows that previous cyclic changes were exclusively produced by a DUp (dUp). Conversely, in the lower panel, the same discon- nection indicates that previous cyclic changes were exclusively produced by a DDown (dDown). Note that systolic ar- terial pressure is in a normal range in the upper example, whereas it is low in the lower example
with each lung inflation, a greater amount of blood is effort [8]. In a recent clinical study conducted in septic boosted toward the left ventricle. This squeeze of blood patients by Michard et al. [8], a PPV >13% detected enlarges PPV by increasing DUp (Fig. 2, upper left subsequent fluid responsiveness with 94% sensitivity and panel). A rapid fluid removal may reduce PPV (Fig. 2, 96% specificity. Additionally, hypovolemia may not be lower left panel). Importantly, this pattern of increased absolute, but only relative to the level of pleural pressure PPV is usually observed in patients with a normal or change [10]. Conversely, and probably more importantly, elevated arterial pressure, but may also occur in patients when a patient with septic shock does not exhibit marked with low arterial pressure, especially if heart failure is change in arterial pulse pressure under respiratory sup- present [3]. port, fluid expansion is likely unprofitable, and perhaps When hypovolemia is present, the right ventricle may deleterious. be on the initial ascending part of its Starling curve, and More recently, we have observed that septic patients sensitive to preload changes. Thus, inspiratory increases with acute RV dysfunction may be associated with a large in pleural pressure will induce an additional decrease in PPV coexisting with a low arterial pressure. Importantly, RV preload, resulting from the transient decrease in ve- such conditions, usually referred to as cor pulmonale, may nous return, accentuating the inspiratory drop in RV not respond to volume expansion (Fig. 3). This finding ejection [9]. This preload impairment enlarges PPV by illustrates the main role of the right ventricle in cyclic enlarging DDown (Fig. 2, upper right panel). A rapid changes in arterial pulse pressure during mechanical ven- volume expansion may reduce PPV (Fig. 2, lower right tilation. When RV systolic function is markedly impaired panel). Importantly, this pattern of increased PPV is and/or pulmonary vascular resistance markedly increased, usually observed in patients with low arterial pressure. In volume expansion at the venous level cannot attain pul- these patients, volume expansion usually significantly monary circulation and cannot correct a LV preload de- increases cardiac output and arterial pressure. Measure- fect [11]. ment of PPV has thus been proposed and documented Thus, cyclic changes in arterial pulse pressure and its to be a sensitive index of fluid responsiveness in the systolic component during mechanical ventilation are hemodynamically unstable patient, provided that sinus induced by complex interactions between systemic ve- rhythm is regular and there is no spontaneous breathing nous return, RV ejection, intrathoracic blood volume 1049 Cyclic changes in arterial pressure during mechanical ventilation 87
Fig. 2 In the left panel, the overfilled patient A exhibits an expiratory drop in arterial pulse of 12% at baseline (upper pan- el), coexisting with a normal systolic arterial pressure. Rapid fluid removal by veno-venous hemodiafiltration reduces this expiratory drop to 4%. In the right panel, the hypovolemic patient B exhibits a major ex- piratory drop in arterial pulse of 27% at baseline, coexisting with an abnormally low systolic ar- terial pressure. Rapid volume expansion reduces this expira- tory drop to 9%
Fig. 3 Two successive record- ings of arterial pulse in a me- chanically ventilated patient with ARDS due to bacterial pneumonia. Transesophageal echocardiography demonstrates severe acute cor pulmonale. In the upper panel, this patient exhibits hypodynamic circula- tory failure, with depressed systolic arterial pressure and Doppler cardiac output. Be- cause this critical hemodynamic state was associated with a large 21% PPV, it was decided to apply a rapid volume expan- sion. After volume expansion (lower panel), the hemodynam- ic status was unchanged. This illustrates the key role of right ventricular function in deter- mining the cyclic changes in arterial pulse under respiratory support. Norepinephrine infu- sion promptly and completely corrected circulatory failure in this patient 1050 88 F. Jardin shifts and LV performance. Although the existence of a paired, these simple rules may not apply. Importantly, RV DUp usually identifies those patients with impaired LV dysfunction often occurs in the setting of acute respiratory contractility and volume expansion, and an enlarged PPV failure and may complicate the non-specific application volume responsive hypovolemia, if RV function is im- of pulse pressure as a monitoring tool.
References
1. Denault A, Gasior T, Gorcsan J, 6. Vieillard-Baron A, Chergui K, Augarde 9. Vieillard-Baron A, Augarde R, Prin S, Mandarino W, Deneault L, Pinsky M R, Prin S, Page B, Beauchet A, Jardin F Page B, MD, Beauchet A, Jardin F (1999) Determinants of aortic pressure (2003) Cyclic changes in arterial pulse (2001) Influence of superior vena variation during positive-pressure ven- during respiratory support revisited by caval zone conditions on cyclic chang- tilation in man. Chest 116:178–186 Doppler echocardiography. Am J Re- es in right ventricular outflow during 2. Jardin F, Farcot JC, Gueret P, Prost JF, spir Crit Care Med 168:671–676 respiratory support. Anesthesiology Ozier Y, Bourdarias JP (1983) Cyclic 7. Jardin F, Delorme G, Hardy A, Auvert 95:1083–1088 changes in arterial pulse during respi- B, Beauchet A, Bourdarias JP (1990) 10. Michard F, Chemla D, Richard C, ratory support. Circulation 68:266–274 Reevaluation of hemodynamic conse- Wysocki M, Pinsky M (1999) Clinical 3. Preisman S, Pfeiffer U, Liberman N, quences of positive pressure ventilation: use of respiratory changes in arterial Perel A (1997) New monitors of intra- emphasis on cyclic right ventricular pulse pressure to monitor the hemody- vascular volume: a comparison of arte- afterloading by mechanical lung infla- namic effect of PEEP. Am J Respir Crit rial pressure waveform analysis and the tion. Anesthesiology 72:966–970 Care Med 159:935–939 intrathoracic blood volume. Intensive 8. Michard F, Boussat S, Chemla D, 11. Vieillard-Baron A, Prin S, Chergui K, Care Med 23:651–657 Anguel N, Mercat A, Lecarpentier Y, Dubourg O, Jardin F (2003) Hemody- 4. Vieillard-Baron A, Loubi res Y, Richard C, Pinsky M, Teboul JL (2000) namic instability in sepsis: bedside as- Schmitt JM, Page B, Dubourg O, Relation between respiratory changes in sessment by Doppler echocardiography. Jardin F(1999) Cyclic changes in right arterial pulse pressure and fluid re- Am J Respir Crit Care Med 168:1270– ventricular outflow impedance during sponsiveness in septic patients with 1276 mechanical ventilation. J Appl Physiol acute circulatory failure. Am J Respir 87:1644–1650 Crit Care Med 162:134–138 5. Versprille A (1990) The pulmonary circulation during mechanical ventila- tion. Acta Anaesthesiol Scand 34 (Suppl) 94:51–62 Daniel De Backer Lactic acidosis
ATP production. This causes the lactate to pyruvate ratio to increase (normal ratio 10/1). Once molecular oxygen is again available, assuming that mitochondrial function is preserved, the excess lactate is rapidly metabolized back through pyruvate into CO2 and H2O via the Krebs cycle. Some cells, such as red blood cells, do not have mitochondria and thus are primary lactate producers. Since lactate is rapidly metabolized by liver and skeletal muscle, these functional anaerobic cells result in mini- mal blood lactate levels. Lactate in the blood is metabolized mainly by the liv- er (50%) and kidneys (20%). Liver function and liver Introduction blood flow influence hepatic lactate clearance, but ex- treme conditions of pH can also decrease lactate clear- Hyperlactatemia is considered a hallmark of ongoing tis- ance. Renal lactate clearance occurs in the cortex, and sue hypoxia, but this is not always the case, and errone- this area is very sensitive to a reduction in blood flow. ous conclusions may sometimes be drawn that lead to Striated muscle, the heart, and the brain also metabolize unjustified therapeutic interventions. In this note we dis- lactate and in some conditions this clearance can be sig- cuss the possible implications of hyperlactatemia nificant. In basal metabolic conditions arterial lactate levels are between 0.5 and 1 mEq/l, and this value repre- sents the balance between lactate production and con- Lactate metabolism sumption. Traditionally, elevated blood lactate levels in hemodynamically unstable subjects are often taken to re- Lactate is a byproduct of glycolysis. In the energy- flect circulatory shock, arterial hypoxemia or both. How- producing metabolism of glucose two distinct processes ever, other factors may coexist, complicating the inter- occur. The first series of enzymatic reactions (Enden- pretation of hyperlactatemia. Mierhoff pathway), occurring in the cytoplasm of cells, anaerobically transforms 1 molecule of glucose into 2 molecules of pyruvate, generating 2 molecules of ATP. Lactate vs. pH measurements in assessing This is the primary energy process for all cells function- anaerobic metabolism? ing in a low oxygen environment, such as in poorly per- fused tissues. Pyruvate may either be converted to lac- Monitoring the blood pH, base deficit, or anion gap may tate, producing one additional molecule of ATP, or move fail to detect hyperlactatemia. Hyperventilation corrects into the second series of reactions. The second series of arterial pH. Measurements of base excess and anion gap enzymatic reactions (Krebs cycle) takes place in the mi- reflect lactate levels in pure lactic acidosis, buts may be tochondria and requires oxygen: pyruvate is oxidized in- influenced by other factors in complex situations. to CO2 and H2O producing 18 ATP molecules. In the ab- Concomitant renal failure, preexisting acid base disor- sence of oxygen, pyruvate cannot enter the Krebs cycle ders, and decreased albumin levels alter the specificity and is preferentially transformed into lactate to maintain and sensitivity of base excess. Hence measurements of
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 89 DOI: 10.1007/978-3-642-01769-8_22, © Springer-Verlag Berlin Heidelberg 2009 700 90 D. De Backer blood lactate levels are mandatory to detect hyperlactat- ration of pyruvate into the Krebs cycle, is inhibited after emia. endotoxin administration or cecal ligation. However, the impact of pyruvate dehydrogenase inhibition in septic patients remains to be determined as the administration Lactate measurements of dichloroacetate, bypassing pyruvate dehydrogenase, results in small and clinically insignificant changes in Measurement has long involved sampling blood on iced blood lactate levels and arterial pH [2]. fluoride tubes to inhibit in vitro red blood cells lactate More importantly, sepsis-induced inflammatory medi- production. Lactate is then measured on plasma using ators accelerate aerobic glycolysis, increasing pyruvate enzymatic colorimetry with lactate dehydrogenase. More availability. In hemodynamically stable septic patients recent analyzers use enzymatic amperometry with lactate Gore et al. [3] reported that lactate and pyruvate were oxidase generating H2O2, which is detected by the elec- both markedly increased and related to an accelerated trode. The time response with these two methods is ap- glucose turnover, as glucose production was fourfold proximately 1 h. Alternatively, blood lactate levels can higher in septic patients than in healthy volunteers. be measured by a blood gas analyzer using the same en- zymatic amperometry technique. The time response is only 2 min. To be valid, blood gas analyzer measure- Regional lactate production ments must be made with a short delay between sam- pling and analysis (less than 5 min, with the syringe Animal studies have reported that the lungs are major stored on ice). Blood lactate concentrations overestimate lactate producers in sepsis [4]. In patients with acute plasma concentrations by 1 or 2 decimals. Measurement lung injury, several groups have reported that lung lac- of plasma lactate with enzymatic amperometry is the ref- tate production is markedly increased and proportional to erence method, which should be used when accurate the severity of lung injury. The amount of lactate pro- measurements are required (especially for estimating ar- duced by the lungs in acute lung injury is tremendous teriovenous lactate differences). Pyruvate measurements and can higher than basal endogenous lactate production may be useful to identify anaerobic lactate production, by the entire body. De Backer et al. [5] demonstrated that but these are cumbersome, time consuming, and subject lung lactate production occurs in subjects with acute to many errors. lung injury states but not in patients with normal lungs, cardiogenic pulmonary edema, or pneumonia. Thus lung lactate production requires a diffuse inflammatory pro- Anaerobic lactate production cess. Other organs can also produce lactate. Experimental In experimental conditions blood lactate concentrations studies suggest that the gut can produce lactate in sepsis, rise when O2 consumption becomes dependent on O2 which is likely from anaerobic metabolism as portal lac- delivery (VO2/DO2 dependency), reflecting anaerobic tate to pyruvate ratio is increased. The investigation of metabolism. In critically ill patients in low flow states hy- splanchnic lactate turnover in humans is much more perlactatemia is mostly of hypoxic origin, although some complicated as access to the portal vein is not possible impairment in liver metabolism may coexist. Tissue wash outside the operating room. Since the liver is usually out may also be present following acute resuscitation. able to clear this small amount of gut-produced lactate, In septic conditions hyperlactatemia can also be ob- splanchnic ischemia may go unsuspected. Accordingly, served, but its hypoxic origin is less clear. In patients De Backer et al. [6] reported that splanchnic lactate re- with acute circulatory failure treated with high doses of lease is uncommon in patients with severe sepsis and vasoactive agents there is a strong suspicion that hyper- was not related to arterial lactate concentrations, abdom- lactatemia is related to tissue hypoxia [1]. However, tis- inal infection or signs of gut or liver dysoxia. sue hypoxia and anaerobic metabolism cannot be sus- Finally, white blood cells may also take an active part tained for long periods of time without inducing cell in the increased tissue lactate production. Under basal death, as the energy produced by anaerobic metabolism conditions, only 10% of ATP production is of mitochon- is quite low compared to aerobic metabolism. Mild hy- drial origin; hence anaerobic glycolysis provides most of perlactatemia (2Ð4 mEq/l) in hemodynamically stable the additional energy requirements when white blood septic patients is probably not related to tissue hypoxia. cells are activated, producing large amounts of lactate. Although generated by anaerobic metabolism, this in- crease in lactate production is not due to O2 deprivation. Aerobic lactate production After exposure to endotoxin in vitro, whole blood lactate production almost doubles, and this is due exclusively to Experimental studies in rodents have reported that pyru- an increase in white blood cell lactate production [7], as vate dehydrogenase, an enzyme essential for the incorpo- red blood cell lactate production is not modified. Hence 701 Lactic acidosis 91 large amounts of lactate can be produced in inflammato- ry processes even in the absence of tissue hypoxia. Pre- sumably this is the cause of the positive lactate flux from the lung in acute lung injury.
Decreased lactate clearance
Blood lactate concentrations are the result of the balance between lactate production and clearance. In normal con- ditions at rest the liver accounts for more than one-half of lactate clearance, with kidneys and muscles account- ing for the remaining part. The respective contribution of these organs can be influenced by several factors includ- Fig. 1 Interpretation of hyperlactatemia. Blood lactate concentra- ing exercise, liver dysfunction and glucose and O2 avail- tions reflect the balance between lactate production, either anaero- ability. bic (mainly in tissue hypoxia) or aerobic, and lactate clearance Liver dysfunction is frequent in critically ill patients (i.e., the sum of the endogenous oxidative-phosphorylation lactate production and the additional lactate production under the influ- and can affect blood lactate concentrations. Using an ence of overwhelming inflammation, and lactate clearance, mainly external lactate load in hemodynamically stable septic pa- by the liver). WBC White blood cells tients, Levraut et al. [8] reported that lactate clearance was altered in patients with mildly elevated blood lactate levels (2Ð4 mEq/l) but not in patients with normal blood Prognostic value lactate concentrations. However, blood lactate concentra- tions are within normal values in patients with very se- Whatever its source, lactic acidosis is associated with verely impaired liver function such as in ambulatory cir- impaired survival. Admission blood lactate levels are rhotic patients. Hence, an increased blood lactate concen- strongly associated with outcome [9]. Interestingly, the tration suggests that lactate is actively, or has been recent- prognostic value is better for lactate than for pyruvate or ly, produced in increased amounts; the impairment in liv- the lactate to pyruvate ratio, suggesting that the prognos- er function being responsible for a delayed clearance. tic value is not related to tissue hypoxia alone. The course of blood lactate concentrations give the best prog- nostic value. A decrease in blood lactate levels during Interpretation of blood lactate concentrations the first 24 h is associated with a better outcome while persistent hyperlactatemia and increasing lactate levels Increased blood lactate can only be caused by increased are associated with a worse outcome. anaerobic or aerobic lactate production, eventually com- Early recognition of hyperlactatemia is essential, as bined with decreased lactate clearance (Fig. 1). Hence early interventions targeted on hemodynamic endpoints tissue hypoxia should always be excluded first, as persis- can decrease mortality in patients with severe sepsis and tent tissue hypoxia can lead to multiple organ failure and elevated blood lactate levels [10]. However, it has not death. Tissue hypoxia can be global, especially in low been confirmed that interventions targeted specifically to flow states and hypoxemia, but it can also be localized, normalize blood lactate concentrations can improve out- especially within the gut microcirculation. Sometimes come. impaired mitochondrial performance can induce hyper- lactemia. In particular, antiretroviral therapies can induce uncoupling of cytochrome energy transfer, leading to se- Conclusions vere and often lethal lactic acidosis. Aerobic lactate pro- duction, either global or focal (especially in the lungs), is Measurements of blood lactate concentrations are useful the result of activation of the inflammation cascade. to detect occult tissue hypoxia and to monitor the effects Hence hyperlactatemia may be a warning indicator of a of therapy. However, hyperlactatemia can be due to other very severe inflammatory state. One should examine any causes than tissue hypoxia, in particular inflammatory patient with unexplained lactic acidosis in order to en- processes, and therefore hemodynamic interventions in sure that no focus of infection remains uncovered. When subjects with elevated blood lactate levels may not al- an altered lactate clearance is involved, it can be due to ways be warranted. an altered liver metabolism, usually insensitive to hemo- dynamic manipulations, but also to a decreased perfusion of the liver, which can be improved by hemodynamic in- terventions. 702 92 D. De Backer
References
1. Levy B, Sadoune LO, Gelot AM, 3. Gore DC, Jahoor F, Hibbert JM, 8. Levraut J, Ciebiera JP, Chave S, Bollaert PE, Nabet P, Larcan A (2000) DeMaria EJ (1996) Lactic acidosis Rabary O, Jambou P, Carles M, Evolution of lactate/pyruvate and during sepsis is related to increased Grimaud D (1998) Mild hyperlactate- arterial ketone body ratios in the early pyruvate production, not deficits in mia in stable septic patients is due to course of catecholamine-treated septic tissue oxygen availability. Ann Surg impaired lactate clearance rather than shock. Crit Care Med 28:114Ð119 224:97Ð102 overproduction. Am J Respir Crit Care 2. Stacpoole PW, Wright EC, Baum- 4. Bellomo R, Kellum JA, Pinsky MR Med 157:1021Ð1026 gartner TG, Bersin RM, Buchalter S, (1996) Transvisceral lactate fluxes 9. Weil MH, Afifi AA (1970) Experimen- Curry SH, Duncan CA, Harman EM, during early endotoxemia. Chest tal and clinical studies on lactate and Henderson GN, Jenkinson S (1992) A 110:198Ð204 pyruvate as indicators of the severity of controlled clinical trial of dichloroace- 5. De Backer D, Creteur J, Zhang H, acute circulatory failure (shock). Circu- tate for treatment of lactic acidosis in Norrenberg M, Vincent JL (1997) lation 41:989Ð1001 adults. The Dichloroacetate-Lactic Lactate production by the lungs in 10. Rivers E, Nguyen B, Havstadt S, Acidosis Study Group. N Engl J Med acute lung injury. Am J Respir Crit Ressler J, Muzzin A, Knoblich B, 327:1564Ð1569 Care Med 156:1099Ð1104 Peterson E, Tomlanovich M (2001) 6. De Backer D, Creteur J, Silva E, Early goal-directed therapy in the Vincent JL (2001) The hepatosplanch- treatment of severe sepsis and septic nic area is not a common source of shock. N Engl J Med 345:1368Ð1377 lactate in patients with severe sepsis. Crit Care Med 29:256Ð261 7. Haji-Michael PG, Ladriere L, Sener A, Vincent JL, Malaisse WJ (1999) Leukocyte glycolysis and lactate out- put in animal sepsis and ex vivo human blood. Metabolism 48:779Ð785 Rinaldo Bellomo Defining acute renal failure: John A. Kellum Claudio Ronco physiological principles
(small peptide excretion, tubular metabolism, hormonal production) in the ICU and are not considered clinically important. There are only two physiological functions that are routinely and easily measured in the ICU, which are “unique” to the kidney and which are considered clinically important: the production of urine and the ex- cretion of water soluble waste products of metabolism. Thus, clinicians have focused on these two aspects of re- nal function to help them define the presence of ARF.
Renal solute excretion: glomerular filtration
Renal solute excretion is the result of glomerular filtra- tion and the glomerular filtration rate (GFR) is a conve- nient and time-honoured way of quantifying renal func- tion. However, GFR varies as a function of normal phys- iology as well as disease. For example, subjects on a vegetarian diet may have a GFR of 45–50 ml/min, while subject on a large animal protein intake may have a GFR Introduction of 140–150 ml/min, both with the same normal renal mass [3]. Definitions are never “right” or “wrong”. They are sim- Baseline GFR can be incremented by efferent arterio- ply more or less “useful” for a given purpose. The same lar vasoconstriction or afferent arteriolar vasodilatation is true of the clinical syndrome of acute renal failure or both. Angiotensin converting enzyme (ACE) inhibi- (ARF), which is common in the ICU [1, 2]. In many tors induce the opposite effect and reduce filtration frac- ways, its nature and epidemiology resemble those of tion and GFR [4]. It is not clear what the maximum GFR other loosely defined ICU syndromes, such as sepsis or value can be, but it can be approached with an acute ani- ARDS. In this physiological note, however, we wish to mal protein or amino acid load. The concept of a base- focus on how our understanding of renal physiology can line and maximal GFR in humans has been defined as be used to guide the definition of ARF. the “renal functional reserve”. Figure 1 displays a series of examples describing the GFR/functional renal mass domain graph. For the purposes of this illustration, GFR What are the physiological functions of the kidney? can be considered a continuous function, which is maximal in subjects with 100% renal mass, absent in Many renal functions are shared with other organs (acid- anephric patients and 50% in subjects with a unilateral base control with lung; blood pressure control via the re- nephrectomy. nin-angiotensin-aldosterone axis with liver, lung and ad- Patients 1 and 2 have the same renal mass but differ- renal glands). Other functions are not routinely measured ent baseline GFRs owing to different basal protein in-
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 93 DOI: 10.1007/978-3-642-01769-8_23, © Springer-Verlag Berlin Heidelberg 2009 34 94 R. Bellomo, J.A. Kellum and C. Ronco
the young male. In both cases, a doubling of serum creat- inine corresponds to an approximate decrease in GFR of 50% (exactly a 55% decrease in the above example) be- cause there is a linear relationship between GFR and 1/Scr. Thus, while every classification of ARF in the lit- erature relies on some threshold value for serum creati- nine concentration, no single creatinine value corre- sponds to a given GFR across all patients. Therefore, it is the change in creatinine that is clinically and physio- logically useful in determining the presence of ARF. Unfortunately, like all estimates of GFR (including creatinine clearance), the Scr is not an accurate reflection Fig. 1 of GFR in the non-steady state condition of ARF. During the evolution of dysfunction, Scr will underestimate the degree of dysfunction. Nonetheless, the degree to which takes levels. Subject 1 has a GFR of 120 ml/min that can Scr changes from baseline (and perhaps the rate of be stimulated to 170 ml/min [3, 4, 5, 6]. Patient 2 is a change as well) will reflect the change in GFR. Scr is vegetarian and has a baseline GFR of 65 ml/min that also easily measured and it is reasonably specific for renal can be stimulated to 170 ml/min. In other words, the re- function. Thus, Scr is a reasonable approximation of GFR nal functional reserve in these two patients is different in most patients with normal renal function [8]. Creati- because they are using their GFR capacity at a different nine is formed from non-enzymatic dehydration of cre- level. Patient 3 has undergone a unilateral nephrectomy. atine in the liver and 98% of the creatine pool is in mus- His baseline GFR corresponds to his maximal GFR un- cle. Critically ill patients may have abnormalities in liver der unrestricted dietary conditions. If a moderate protein function and markedly decreased muscle mass. Addi- restriction is applied to his diet, his baseline GFR may tional factors influencing creatinine production include decrease and some degree of renal functional reserve be- conditions of increased production such as trauma, fever come evident. The same concept is true for patient 4; and immobilisation; and conditions of decreased produc- however, to restore some functional reserve, severe pro- tion including liver disease, decreased muscle mass and tein restriction is needed. Thus, baseline GFR does not ageing. In addition, tubular re-absorption (“back-leak”) necessarily correspond to the extent of functioning renal may occur in conditions associated with low urine flow mass and even very careful measurements of GFR will rate. Finally, the volume of distribution (VD) for creati- not allow us to define renal function without placing it in nine (total body water) influences Scr and may be dra- the context of maximal capacity. In this regard GFR is matically increased in critically ill patients and, in the not unlike a resting ECG for the kidney. When it is short term, its concentration in plasma can be dramati- grossly abnormal, renal function is impaired, but when it cally altered by rapid plasma volume expansion. There is is normal, a stress test is required. Another approach, is currently no information on extra-renal creatinine clear- to compare measurements taken over time. Serial mea- ance in ARF and a non-steady state condition often ex- surements of GFR may be impractical but surrogates are ists [9]. readily available. Because urea, or blood urea nitrogen (BUN), is such a non-specific indicator of renal function [7] it is a very poor surrogate for GFR and will not be Creatinine clearance discussed further. Once GFR has reached a steady state it can be quantified by measuring a 24-h creatinine clearance. Unfortunately, Serum creatinine, its physiology the accuracy of a creatinine clearance (even when collec- and defining acute renal failure tion is complete) is limited because as GFR falls, creati- nine secretion is increased, and thus the rise in Scr is less Creatinine is much more specific at assessing renal func- [10, 11]. Accordingly, creatinine excretion is much tion than BUN, but it only loosely corresponds to GFR. greater than the filtered load, causing overestimation of For example, a serum creatinine (Scr) of 1.5 mg/dl the GFR [11]. Therefore creatinine clearance represents (133 mmol/l) at steady-state, corresponds to a GFR of the upper limit of true GFR. A more accurate determina- about 36 ml/min in an 80-year-old white female, but of tion of GFR would require measurement of the clearance about 77 ml/min in a 20-year-old black male. Similarly, a of inulin or radio-labelled compounds [12]. Unfortunate- serum creatinine of 3.0 mg/dl (265 mmol/l) in a patient ly, these tests are not routinely available. However, for suspected of having renal impairment would reflect a clinical purposes, determining the exact GFR is rarely GFR of 16 ml/min in the elderly female but 35 ml/min in necessary. Instead, it is important to determine whether 35 Defining acute renal failure 95 renal function is stable or getting worse or better. This creatinine [14]. Unfortunately, little information exists can usually be determined by monitoring Scr alone [8]. on the usefulness of cysC in ARF. A recent pilot study suggested that it might be superior to both Scr and the “modification of diet in renal disease” (MDRD) equation Other markers of renal failure in the detection of ARF [15].
Urine output Defining acute renal failure Urine output is the commonly measured parameter of re- when baseline renal function is unknown nal function in the ICU and is more sensitive to changes in renal haemodynamics than biochemical markers of One option is to calculate a theoretical baseline serum solute clearance. However, it is far less specific—except creatinine value for a given patient assuming a normal when severely reduced or absent. Severe ARF can exist GFR of approximately 95±20ml/min in women and despite normal urine output (i.e. non-oliguric ARF) but 120±25 ml/min in men [10]. A normal GFR of approxi- changes in urine output often occur long before bio- mately 75–100 ml/min per 1.73 m2 can be assumed by chemical changes are apparent. Since non-oliguric ARF normalising the GFR to body surface area [16] and, thus, has a lower mortality rate than oliguric ARF, urine out- a change from baseline can be estimated for a given pa- put is used to differentiate ARF conditions. Classically, tient. The simplified MDRD formula provides a robust oliguria is defined (approximately) as urine output less estimate of GFR relative to serum creatinine based on than 5 ml/kg per day or 0.5 ml/kg per h. It would be age, race and sex [17]. This estimate could then be used highly desirable to have markers which allow physicians to calculate the relative change in GFR in a given pa- to diagnose when oliguria is a true early marker of de- tient. The application of the MDRD equation to estimate veloping renal failure, because this would allow the baseline creatinine requires a simple table with age, race identification of patients in whom early intervention may and gender. Table 1 solves the MDRD equation for the be justified. lower end of the normal range (i.e. 75 ml/min per 1.73 m2). Note, the MDRD formula is used only to esti- mate the baseline when it is not known. For example, a Other markers 50-year-old black female would be expected to have a baseline creatinine of 1.0 mg/dl (88 µmol/l). This ap- Kidney injury molecule-1 (KIM-1) expression is mark- proach may misclassify some patients, but is probably edly up-regulated in the proximal tubule in the post- adequate for population studies. ischemic rat kidney [13]. A soluble form of human KIM-1 can be detected in the urine of patients with ARF and may serve as a useful biomarker for renal proximal Defining acute renal failure in the setting tubule injury, possibly facilitating the early diagnosis of of known renal dysfunction the disease and serving to discriminate between different forms of renal dysfunction [13]. If the patient has pre-existing renal disease, the baseline Another marker of potential importance is cystatin C GFR and Scr will be different from those predicted by the (cysC). Cys C is a cysteine proteinase inhibitor of low MDRD equation. Also, the relative decrease in renal molecular weight that is produced constantly by nucleat- function required to reach a given level of Scr will be less ed cells (apparently independently of pathological states) than that of a patient without pre-existing disease. For and is excreted by the glomerulus, thus closely reflecting example, a patient with a Scr of 1 mg/dl (88 mmol/l) will GFR. Thus, cysC may be a better marker of GFR than have a steady-state Scr of 3 mg/dl (264 mmol/l) when
Table 1 Estimated baseline creatinine Age Black males White males Black females White females (years) (mg/dl | µmol/l) (mg/dl | µmol/l) (mg/dl | µmol/l) (mg/dl | µmol/l)
20–24 1.5 | 133 1.3 | 115 1.2 | 106 1.0 | 88 25–29 1.5 |133 1.2 | 106 1.1 | 97 1.0 | 88 30–39 1.4 | 124 1.2 | 106 1.1 | 97 0.9 | 80 40–54 1.3 | 115 1.1 | 97 1.0 | 88 0.9 | 80 55–65 1.3 | 115 1.1 | 97 1.0 | 88 0.8 | 71 >65 1.2 | 106 1.0 | 88 0.9 | 80 0.8 | 71
Estimated glomerular filtration rate (GFR) =75 (ml/min per 1.73 m2) =186x (Scr)–1.154x (age) -0.203x(0.742 if female) x(1.210 if African-American) = exp(5.228 -1.154xIn(Scr)–0.203x In(age) -(0.299 if female) +(0.192 if African-American)) 36 96 R. Bellomo, J.A. Kellum and C. Ronco
75% of GFR is lost. By contrast, when only 50% of GFR mately, these cases will generally fall into defined criteria is lost in a perfectly matched patient for age, race and but they may cause confusion in the early acute situation. sex with a baseline Scr of 2.5 mg/dl (221 mmol/l), the Scr In the end, for operative purposes, it must be assumed will be 5 mg/dl (442 mmol/l). These Scr change criteria that patients are adequately hydrated, not treated with di- fail to convey accurately the degree of loss of renal func- uretics except in the case of volume overload and treated tion and the severity of injury. Thus, separate criteria with renal replacement therapy when clinically indicated. should be used for the diagnosis of ARF superimposed Although this may not always be true for individuals, it on chronic renal disease. One possible approach would should be broadly true for populations. be to use a relative change in Scr (e.g. threefold) as the primary criterion for ARF, with an absolute cut-off (e.g. 4 mg/dl or about 350 mmol/l) as a secondary criterion, Conclusions when baseline Scr is abnormal. For example, an acute rise in Scr (of at least 0.5 mg/dl or 44 mmol/l) to more There are no perfect ways to measure renal function. than 4 mg/dl (350 mmol/l) will serve to identify most pa- Even very precise measures of GFR will fail to distin- tients with ARF when their baseline Scr is abnormal. guish mild to moderate functional loss from normal function. Renal function reserve is important but cum- bersome to measure. Surrogate measures such as serum Testing a definition of acute renal failure? creatinine, while routinely available at the bedside, show limited correlation to GFR, especially in the setting of The ultimate value of a definition for ARF is determined critical illness. Injury markers are being developed by its utility. A classification scheme for ARF should be which might aid us in the future but are not ready for use sensitive and specific and also predictive of relevant just yet. Nonetheless, the lessons of physiology can be clinical outcomes such as mortality, use of dialysis and used to guide the development of definitions for ARF. length of hospital stay. These are testable hypotheses de- All the above physiological considerations have played spite the lack of renal specificity for such end points an important role in guiding the members of the Acute [18]. Dialysis Quality Initiative (ADQI) [19] in the formula- It is also understood that therapy can influence the pri- tion of a consensus set of criteria to define ARF. These mary criteria for the diagnosis of ARF. For example, vol- criteria are open for discussion and comments can be ume status will influence urine output and even, to some submitted to the ADQI website (http://www.ADQI.net). degree, Scr, by altering VD. Large-dose diuretics may be We believe this process to be fundamental to improving used to force a urine output when it would otherwise fall our care of ARF patients and hope to move to formal into a category consistent with a diagnosis of ARF. Ulti- testing of a final set of criteria soon.
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14. Jovanovic D, Krstivojevic P, Obradovic 15. Herget-Rosenthal S, Marggraf G, 18. Bellomo R, Kellum J, Ronco C (2001) I, Durdevic V, Dukanovic L (2003) Goering F, Phillip T, Kribben A (2003) Acute renal failure: time for consensus. Serum cystatin C and beta2-microglob- Can serum cystatin C detect acute renal Intensive Care Med 27:1685–1688 ulin as markers of glomerular filtration failure? (abstract). ISN-ERA/EDTA 19. Kellum JA, Mehta RL, Ronco C (2001) rate. Ren Fail 25:123–133 World Congress of Nephrology, Acute dialysis quality initiative (ADQI). Berlin:O11 Contrib Nephrol 132:258–265 16. Fliser D, Franek E, Joest M et al (1997) Renal function in the elderly: impact of hypertension and cardiac function. Kidney Int 51:1196–1204 17. National Kidney Foundation. K/DOQI (2002) Clinical practice guidelines for chronic kidney disease; evaluation, classification and stratification. Am J Kidney Dis (Suppl) 39:S76–S92 Frédérique Schortgen Hypotension during intermittent hemodialysis: new insights into an old problem
technique itself. Systemic blood pressure is determined by the interaction of blood flow and peripheral vasomo- tor tone, both of which may be altered by critical illness and hemodialysis. Vasomotor tone is the complex result of interactions between autonomic tone, metabolic de- mand, blood flow distribution, and the responsiveness of the vascular smooth muscle to vasoactive stimuli, such as ionized calcium, mediators of sepsis, and their vaso- active by-products (e.g., prostaglandin F2α, prostacy- clin). Blood flow, on the other hand, is the result of an- other complex interaction between the determinants of both venous return and ventricular pump function. Im- portantly, venous return is determined by the pressure gradient from the periphery to the heart, such that either Introduction loss of circulating blood volume (hypovolemia) or loss of vasomotor tone (functional hypovolemia) decreases The main indication for renal replacement therapy in venous return. The main pathogenesis of intradialytic hy- critically ill patients is ischemic acute tubular necrosis potension is a decrease in absolute or relative blood vol- associated with multiple organ failure requiring mechan- ume. Adaptation to this hypovolemic state includes fluid ical ventilation and catecholamine administration. The shift from the extra- to the intravascular space and in- kind of renal replacement therapy offering the best he- creases in vascular resistance and myocardial contractili- modynamic tolerance remains debated. Intermittent he- ty (Fig. 1). Although changes in cardiac contractility modialysis (IHD) is often viewed by many ICU physi- may also occur, these appear to less important. Hemodi- cians as inducing hemodynamic instability. The applica- alysis settings have a direct impact on these adaptive tion of recent concepts regarding hemodialysis modali- mechanisms, and hemodynamic stability requires hemo- ties is able to solve part of this old problem [1]. A major dialysis procedures to be optimized to facilitate plasma problem with IHD is the direct application of chronic he- refilling and cardiovascular reactivity. modialysis concepts in the management of acute renal failure. This approach is responsible for much of the ob- served hemodynamic instability and can be minimized How to preserve blood volume? by thoughtful planning prior to IHD in the critically ill patient. Role of ultrafiltration
The volume of ultrafiltration ordered must be based on What are the mechanisms of hypotension the patient’s intravascular volume status (volemia) and during hemodialysis? not on the patient’s dry weight. In contrast to chronic he- modialysis, where patients are always hypervolemic be- In critically ill patients intradialytic hypotension results fore starting IHD session, hypervolemia is rarely present from the underlying process and is exacerbated by the in critically ill patients, except in the case of congestive
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 99 DOI: 10.1007/978-3-642-01769-8_24, © Springer-Verlag Berlin Heidelberg 2009 1646 100 F. Schortgen
Fig. 1 Main mechanisms of hemodynamic stability during inter- pervolemic patient. To provide clinically effect dialysis mittent hemodialysis and, if indicated, fluid removal without inducing hypo- tension, patients with acute renal failure require a longer hemodialysis run than that required for chronic IHD. heart failure. Patients needing renal replacement therapy Thus to receive an adequate dialysis dose, patients suf- in the ICU are typically treated in the context of septic fering from acute renal failure need prolonged (>4 to shock complicated by oliguric acute tubular necrosis de- 6 h) or iterative (daily or every other day) IHD sessions, spite aggressive fluid loading and administration of va- which allows the ultrafiltration rate per hour to be re- soactive drugs. They often present interstitial edemas duced [1, 2]. with a positive weight gain, whereas their plasma vol- ume may not be yet fully restored, and vasopressor per- fusions are still needed. During the acute phase of sepsis Role of osmolality or hypovolemic shock the indication for ultrafiltration must be addressed cautiously. Fluid removal may be During hemodialysis solute removal is achieved by dif- beneficial only in the case of acute respiratory distress fusion according to concentrations gradient across the syndrome with severe hypoxemia, where the removal of membrane. Solute movements are independent of sol- extravascular lung water is expected to improve oxygen- vent shift and may occur in either direction between ation [1]. blood and dialysate depending on the respective solute At the beginning of the hemodialysis session intravas- concentrations in the dialysate and the blood. This dis- cular blood volume decreases due to ultrafiltration but sociation between solute and solvent shifts may be re- usually remains stable thereafter despite continuous fluid sponsible for changes in blood osmolality during the removal because of the plasma refilling process (Fig. 2). session. Removal of sodium, which represents the main Intravascular space filling comes at first from interstitial osmotic agent during hemodialysis, decreases osmolali- and then from intracellular fluids. The use of high ultra- ty. Decrease in blood osmolality during IHD has been filtration rates, approx. 1 l/h, promotes a high incidence shown to be a risk factor for hemodynamic worsening of intradialytic hypotensions in critically ill patients [2]. [3]. Indeed, fall in plasma osmolality promotes water Because plasma refilling is time dependent, a high rate displacement into the cells and impedes plasma refilling of blood volume decrease must be avoided in the nonhy- (Fig. 2). 1647 Hypotension during intermittent hemodialysis 101
Fig. 2 Principle of plasma refilling during intermittent hemodialy- vasoconstriction can decrease intravascular hydrostatic sis pressure and facilitate plasma refilling. The main initiat- ing factor for vasodilatation during IHD session is the in- crease in body temperature. Increasing sodium concentration in the dialysate above the plasma concentration permits sodium shift from the dialysate to the patient’s blood. Increase in Role of thermal balance plasma and interstitial osmolality facilitates adequate fluid movements for plasma refilling (i.e., from intracel- An increase in core temperature is observed during a lular to vascular space through the interstitium; Fig. 2). standard hemodialysis session (dialysate temperature In comparison to the usual sodium concentration used in 37°–37°5 C), which is associated with vasodilatation and chronic hemodialysis patients (i.e., 138–140 mmol/l), the impairment of vascular response to the decrease in blood use of high concentration of sodium in the dialysate, volume. In chronic hemodialysis patients cardiovascular 145–150 mmol/l, limits blood volume reduction despite tolerance to IHD is improved when the dialysate temper- a higher volume of ultrafiltration and reduces the inci- ature is adjusted to the range of 35°–35°5 C [5]. More dence of hypotensions needing therapeutic intervention important than the absolute dialysate temperature, a bet- [1, 4]. In the absence of ultrafiltration the use of a high ter hemodynamic tolerance is achieved if the dialysate concentration of sodium in the dialysate is useful to in- temperature setting prevents any increase in core temper- crease blood volume, similarly to the use of hypertonic ature and heat accumulation in the body [6]. To maintain saline perfusion. the body temperature unchanged in chronic hemodialysis patient the dialysate temperature must be set 1°–2°C be- low the baseline body temperature recorded before con- How to preserve vascular reactivity? nection. The level of the dialysate temperature setting avoiding increase in body temperature, however, has not Improving adaptation of peripheral vascular resistances been specifically studied in patients with acute renal fail- to volume depletion may reduce the risk of intradialytic ure. hypotension. According to the Starling law, precapillary 1648 102 F. Schortgen
Place of isolated ultrafiltration tility has been suggested. Acetate has been also incrim- inated in promoting vasodilatation; this adverse effect That a better adaptation of peripheral vascular resis- remains uncertain because of discrepancies between tances exists during ultrafiltration alone (i.e., fluid re- studies. moval without concomitant diffusive movements) was observed more than 20 years ago. The precise mecha- nism was unknown until recent studies showing that Role of calcium during isolated ultrafiltration the body temperature can easily decrease because the circulation of the dialysate Variations in ionized calcium related to hemodialys- is stopped in the membrane. Body temperature changes is may have an impact on myocardial contractility. then depend on room temperature, which is lower than A low calcium concentration in the dialysate has been dialysate temperature. Ultrafiltration alone results in shown to be associated with calcium removal, decrease the same hemodynamic stability than hemodialysis in serum ionized calcium concentration, and hemo- with a dialysate temperature set to obtain the same de- dynamic instability, particularly in patients suffering crease in body temperature [7]. Convective techniques from cardiac failure [10]. In contrast to chronic (hemofiltration and hemodiafiltration) may have a bet- hemodialysis in which the concentration of calcium ter thermal effect explaining their better hemodynamic is often low in the dialysate (e.g., high doses of oral tolerance. Large amounts of replacement fluid may in- calcium-based phosphate binder, hypercalcemia related duce a larger decrease in body temperature than during to hyperparathyroidism), in critically ill patients the IHD. In chronic dialysis patients van der Sande and calcium concentration must be rather high (at least colleagues [8] manipulated the dialysate temperature 1.75 mmol/l). during IHD and the amount of replacement fluid in- fused at room temperature during hemodiafiltration to obtain the same thermal effect on patient body tempera- Conclusion ture. They found that hemodiafiltration had no advan- tage in preventing hemodynamic instability in compari- In critically ill patients the IHD settings may differ son to IHD, when the body temperature decreased to from those in chronic hemodialysis patients, in whom the same degree with the two techniques. the main objective is the largest weight loss within the minimal session time. When IHD is the technique of re- nal replacement therapy used in critically ill patients, How to preserve cardiac contractility? adequate settings must be used to avoid excessive blood volume loss, vasodilatation, and myocardial de- Role of buffer solutions pression. Improving hemodynamic tolerance of IHD must be our primary goal to facilitate adequate dialysis Acetate hemodialysis promotes a large decrease in dose delivery and organ failure recovery, avoiding cardiac output in comparison to bicarbonate [9]. A di- shortened session time because of hypotension. rect negative impact of acetate on myocardial contrac-
References 1. Schortgen F, Soubrier N, Delclaux C, 4. Paganini EP, Sandy D, Moreno L, 6. Maggiore Q, Pizzarelli F, Santoro A, Thuong M, Girou E, Brun-Buisson C, Kozlowski L, Sakai K (1996) The Panzetta G, Bonforte G, Hannedouche Lemaire F, Brochard L (2000) Hemo- effect of sodium and ultrafiltration T, Alvarez de Lara MA, Tsouras I, dynamic tolerance of intermittent he- modelling on plasma volume Loureiro A, Ponce A, Sulkova S, Van modialysis in critically ill patients: use- changes and haemodynamic stability Roost G, Brink H, Kwan JT (2002) fulness of practice guidelines. Am J in intensive care patients receiving The effects of control of thermal bal- Respir Crit Care Med 162:197–202 haemodialysis for acute renal ance on vascular stability in hemodial- 2. Schiffl H, Lang SM, Fischer R (2002) failure: a prospective, stratified, ysis patients: results of the European Daily hemodialysis and the outcome of randomized, cross-over study. randomized clinical trial. Am J Kidney acute renal failure. N Engl J Med Nephrol Dial Transplant 11 Suppl Dis 40:280–290 346:305–310 8:32–37 7. van der Sand FM, Gladziwa U, 3. Henrich WL, Woodard TD, Blachley 5. Yu AW, Ing TS, Zabaneh RI, Kooman JP, Bocker G, Leunissen KM JD, Gomez-Sanchez C, Pettinger W, Daugirdas JT (1995) Effect (2000) Energy transfer is the single Cronin RE (1980) Role of osmolality of dialysate temperature most important factor for the difference in blood pressure stability after dialysis on central hemodynamics and in vascular response between isolated and ultrafiltration. Kidney Int urea kinetics. Kidney Int ultrafiltration and hemodialysis. J Am 18:480–488 48:237–243 Soc Nephrol 11:1512–1517 1649 Hypotension during intermittent hemodialysis 103
8. van der Sand FM, Kooman JP, Konings 9. Huyghebaert MF, Dhainaut JF, 10. van der Sand FM, Cheriex EC, JP, Leunissen KM (2001) Thermal ef- Monsallier JF, Schlemmer B (1985) van Kuijk WH, Leunissen KM (1998) fects and blood pressure response dur- Bicarbonate hemodialysis of patients Effect of dialysate calcium concentra- ing postdilution hemodiafiltration and with acute renal failure and severe tions on intradialytic blood pressure hemodialysis: the effect of amount of sepsis. Crit Care Med 13:840–843 course in cardiac-compromised pa- replacement fluid and dialysate temper- tients. Am J Kidney Dis 32:125–131 ature. J Am Soc Nephrol 12:1916–1920 Peter J. D. Andrews Intracranial pressure Giuseppe Citerio Part one: Historical overview and basic concepts
pressure (ICP), was widely used (Ayer 1929, Merrit and Fremont-Smith 1937, Browder and Meyer 1938, Cairns 1939, Landon 1917, Sharpe 1920 and Jackson 1922) and this was the earliest clinical method of ICP measurement. Jackson pointed out the neglect by surgeons of the field of acute traumatic brain injuries. He demonstrated that the pulse, respiration and blood pressure are affected only once the medulla is compressed and stated that to wait for these changes as an indication for operation on the cerebrum in acute cerebral injury is to court disaster. Furthermore, reports emerged that some patients, even if showing clinical signs of brain compression, had nor- mal lumbar CSF pressures or died after the procedure. Lumbar puncture fell into disuse for the diagnosis of in- tracranial hypertension due to the possibility of inducing Introduction brain-stem compression through tentorial or tonsillar herniation, and because, if the system does not commu- One hundred and seventy years ago, Magendie (1783– nicate, the spinal fluid pressure is not an accurate re- 1855) discovered a small foramen in the floor of the flection of ICP as demonstrated by Langfitt’s work [1]. fourth ventricle, now bearing his name, and pointed out the connection between the cerebrospinal fluid (CSF) in the ventricular system and in the subarachnoid spaces of Lundberg: a clinical pioneer the brain and cord. By this momentous discovery, he led the way to understanding the circulation of CSF and to Researchers moved from the lumbar approach to direct problems associated with increased CSF pressure. cannulation of the ventricular system. Early clinical re- search in this field was reported by Nils Lundberg and involved conscious volunteers with a multiplicity of in- Lumbar cerebral spinal fluid pressure measurement tracranial pathologies [2]. They were monitored by a fluid-filled transducer system attached to a ventricular Physiological exploration of human CSF started in the catheter placed in the lateral ventricle. Recordings lasted, late 18th century. In 1891, Quinke published his studies in some cases, several hours or days. Lundberg, enlighten on the diagnostic and therapeutic applications of lumbar by his clinical talent, reported a number of phenomena puncture. He standardised the technique and made it a that are relevant today. However, a recording system con- rule always to measure the pressure of the CSF by con- nected to an analogue output from the ICP transducer is necting the lumbar puncture needle with a fine glass pi- required for detection and this is frequently overlooked in pette in which the fluid was allowed to rise. modern ICU monitoring systems. A digital trend does not Subsequently, repeated measurement of lumbar cere- usually have sufficient resolution to detect ICP waves bral spinal fluid pressure, as an assessment of intracranial with a frequency of less than 2/min. The clinical impor- tance of ventricular fluid pressure (VFP) waveform was
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 105 DOI: 10.1007/978-3-642-01769-8_25, © Springer-Verlag Berlin Heidelberg 2009 1731 106 P.J.D. Andrews and G. Citerio
Fig. 1 Example of plateau waves recorded at bedside. The plateau waves are a haemody- namic phenomenon associated with cerebrovascular vasodila- tion. They are observed in pa- tients with preserved cerebral autoregulation but reduced pressure-volume compensatory reserve. As documented by the tracing, during plateau waves, cerebral perfusion pressure falls below the ischaemic threshold, shown by jugular saturation oximetry. MAP mean arterial pressure, ICP intracranial pres- sure, SjO2 continuous jugular saturation
elucidated in 48 patients and it was concluded that the thought to occur because of interaction between car- spontaneous changes in VFP curve were of two main diac and respiratory cycles. types, plateau waves and rhythmic oscillations[3]. Lund- berg stated that the former could cause both transient Both A and B waves require intervention to reduce ICP and persistent damage to the brain and therefore diagno- and preserve CPP. Without the continuous recording of sis, utilising a ventricular catheter, and prevention of ICP, judgement of correct timing and evaluation of the such pressure variations were of clinical importance. The efficacy of the therapy will be difficult. rhythmic fluctuations in VFP at the frequency of 1/min can be normal but their incidence increases with pathol- ogy and then may represent cerebral dysfunction. This Monro and Kellie doctrine may also be true for the rhythmic waves with a frequency of 6/min. The waves described by Lundberg were: The fundamental principles of raised intracranial pressure were developed in Scotland and are condensed in the – A waves or “Plateau waves” have amplitudes of 50– doctrine credited to Professors Monro (1783) [4] and 100 mmHg, lasting 5–20 min. These waves are always Kellie (1824) [5], which states, once the fontanelles and associated with intracranial pathology (Fig. 1). During sutures are closed, that: such waves, it is common to observe evidence of early herniation, including bradycardia and hypertension. – The brain is enclosed in a non-expandable case of The aetiology is uncertain, but it is postulated that as bone; cerebral perfusion pressure (i.e. the difference between – The brain parenchyma is nearly incompressible; mean arterial pressure and intracranial pressure, CPP) – The volume of the blood in the cranial cavity is becomes inadequate to meet metabolic demand, cere- therefore nearly constant and bral vasodilatation ensues and cerebral blood volume – A continuous outflow of venous blood from the cranial increases. This leads to a vicious circle, with further cavity is required to make room for continuous in- CPP decrease, predisposing the patient to other plateau coming arterial blood. waves and, if low CPP is not corrected, to ruinous effects. The importance of these observations is that the skull – B waves are oscillating and up to 50 mmHg in am- cannot easily accommodate any additional volume. The plitude with a frequency 0.5–2/min and are thought to craniospinal axis is essentially a partially closed box with be due to vasomotor centre instability when CPP is container properties including both viscous and elastic unstable or at the lower limits of pressure autoregu- elements. The elastic or, its inverse, the compliant prop- lation. erties of the container will determine what added volume – C waves are oscillating and up to 20 mmHg in am- can be absorbed before intracranial pressure begins to plitude and have a frequency of 4–8/min. These waves rise. In its original form the Monro-Kellie doctrine did not have been documented in healthy individuals and are take into account the CSF as a component of the cranial 1732 Intracranial pressure Part one: Historical overview and basic concepts 107
ComplianceðÞ¼C ¼ DV=DP 1=Elastance ¼ 1=VPR Marmarou, interested in CSF dynamics, was the first to provide a full mathematical description of the craniospi- nal volume-pressure relationship. He developed a math- ematical model of the CSF system which produced a general solution for the CSF pressure. The model pa- rameters were subsequently verified experimentally in an animal model of hydrocephalus. As a corollary of this Fig. 2 Pressure-volume curve of the craniospinal compartment. study, Marmarou demonstrated that the non-linear cra- This figure illustrates the principle that in the physiological range, niospinal volume-pressure relationship could be described i.e. near the origin of the x-axis on the graph (point a), intracranial as a straight line segment relating the logarithm of pres- pressure remains normal in spite of small additions of volume until sure to volume, which implies a mono-exponential rela- a point of decompensation (point b), after which each subsequent increment in total volume results in an ever larger increment in tionship between volume and pressure. Marmarou termed intracranial pressure (point c) the slope of this relationship the pressure-volume index (PVI), which is the notional volume required to raise ICP tenfold. PVI is expressed by the formula: compartment. The concept of reciprocal volume changes between blood and CSF was introduced in 1846 by Bur- PVI ¼ DV=ðlog10 Po=PmÞ rows and, later, extended in the early twentieth century by Where DV expresses the volume, in millilitres, added Weed to allow for reciprocal changes in all the cranio- or withdrawn from the ventricular system, P is the initial spinal constituents. o pressure and Pm the final pressure. An understanding of raised ICP encompasses an anal- Unlike elastance or its inverse, compliance, the PVI ysis of both intracranial volume and craniospinal com- characterises the craniospinal volume-pressure relation- pliance. Therefore, ICP is a reflection of the relationship ship over the whole physiological range of ICP. The PVI between alterations in craniospinal volume and the ability is calculated from the pressure change resulting from a of the craniospinal axis to accommodate added volume rapid injection or withdrawal of fluid from the CSF space (Fig. 2). and was utilised both clinically and experimentally as a If a new intracranial volume displaces venous blood measure of summed craniospinal compliance. In the clin- and CSF, for example haematoma, tumour, oedema or ical setting, PVI measures are obtained by first removing hydrocephalus, initially there is little change in ICP. How- 2 ml and recording the reduction in pressure [7]. By this ever, the ability to accept the cerebral blood flow com- technique, the PVI can be estimated and, after deciding ponent of the cardiac cycle is decreased and, provided the upon a peak pressure that should not be exceeded, a volume of each cerebral component of the cardiac cycle maximum volume injection can be calculated. Ordinarily, remains constant, close observation will recognise an in- the PVI measures are obtained by repeated withdrawal crease in the ICP wave amplitude [6]. This is because and injections of 2 ml and the average PVI is calculated intracranial compliance is reduced. Further exhaustion of from multiple injections. Injection of fluid into the CSF the volumetric compensatory reserve leads to an increase space is not performed when ICP is high. In those cases, in mean ICP and a further increase in ICP wave ampli- PVI is obtained only from withdrawal of known quantities tude. At very high ICP the amplitude of the ICP wave of fluid. decreases as cerebral blood flow (CBF) is reduced by a However, the use of the PVI method is not without reduction in compliance and perfusion pressure. Avezaat disadvantages: and Van Eijdhoven were some of the original researchers to study the changing shape of the ICP wave as the patient – Variability exists between measurements due to the moves along the volume-pressure curve. They developed difficulty in manually injecting consistent volumes of a model showing that the ICP pulse amplitude (DP) was fluid at a constant rate. As a result an average of re- linearly proportional to the ICP and the elastic coefficient peated measures is usually required. (E1). They used this method roughly to estimate the in- – There is an increased risk of infection with this tech- tracranial compliance of the patient. nique. Aetiologies include: manipulation of the CSF access system to test the PVI, CSF sampling and re- calibration of the pressure transducer, all of which Intracranial compliance potentially expose the patient to a higher risk of in- fection. Intracranial compliance is the change in volume (DV) per – Moreover, the procedure is time consuming and re- unit change in pressure (DP). Compliance is the inverse of quires highly trained personal. elastance (DP/DV), sometimes known as the volume-pres- sure response (VPR). 1733 108 P.J.D. Andrews and G. Citerio
As a consequence of these limitations, the PVI tests are of the craniospinal axis to accommodate added volume. It not routinely used in the clinical situation. can not be estimated without directly measuring it. In 1972, Mario Brock realised the interest in ICP monitoring and organised the first International Symposium on In- Conclusion tracranial Pressure in Hanover. This was the start of a very successful series of meetings and continues in Hong Intracranial pressure is a reflection of the relationship Kong this year, as ICP XII. between alterations in craniospinal volume and the ability
References
1. Langfitt TW, Weinstein JD, Kassell NF, 4. Monro A (1823) Observations on the 6. Ryder HW, Espey FF, Kristoff FV, Simeone FA (1964) Transmission of structure and function of the nervous Evans PP (1951) Observations on the increased intracranial pressure I: within system. Creech & Johnson, Edinburgh, interrelationships of intracranial pres- the craniospinal axis. J Neurosurg p5 sure and cerebral blood flow. J Neuro- 21:989–997 5. Kellie G (1824) An account of the ap- surg 8:46–58 2. Lundberg N (1960) Continuous record- pearances observed in the dissection of 7. Maset AL, Marmarou A, Ward JD, ing and control of ventricular fluid two of the three individuals presumed to Choi S, Lutz HA, Brooks D, Moulton pressure in neurosurgical practice. Acta have perished in the storm of the 3rd, RJ, DeSalles A, Muizelaar JP, Turner H Psychiat Neurol Scand 36 (suppl):149 and whose bodies were discovered in (1987) Pressure-volume index in head 3. Lundberg N, Troupp H, Lorin H (1965) the vicinity of Leith on the morning of injury. J Neurosurg. 67:832–840 Continuous recording of the ventricular the 4th November 1821 with some re- fluid pressure in patients with severe flections on the pathology of the brain. acute traumatic brain injury. J Neuro- Trans Med Chir Sci, Edinburgh 1:84– surg 22:581–590 169 Giuseppe Citerio Intracranial pressure Peter J. D. Andrews Part two: Clinical applications and technology
paired after acute injury and, importantly, the lower limit for pressure autoregulation may be increased markedly. When intracranial compliance is reduced, even a small increase in CBF and, therefore, cerebral blood volume will increase ICP. In health the intracranial volume is regulated by the crystalloid osmotic pressure gradient across the imper- meable blood brain barrier (BBB, crystalloid osmotic pressure about 5000 mmHg). In areas where the BBB is damaged, the considerably lower colloid osmotic (i.e. on- cotic) pressure (~20 mmHg) is solely responsible. With complete BBB disruption there is a pressure force equi- librium between brain tissue and capillary hydrostatic pressures. Therefore, after acute injury it is important to maintain crystalloid osmotic pressure (principally serum ++ Introduction [Na ]), oncotic pressure (albumin) and, if ICP is pressure passive, control brain microvascular pressure. Intracranial pressure (ICP) is a reflection of the relation- Temperature and cerebral metabolic rate of oxygen ship between alterations in craniospinal volume and the (CMRO2) are positively related. Control of brain tem- ability of the craniospinal axis to accommodate added perature offers the potential benefit of reducing CBF by volume. It cannot be estimated without directly measuring reducing CMRO2. it. Systemic physiology has an important influence on ICP and a systemic cause for raised ICP should always be sought before an ICP intervention is undertaken. Systemic physiological variables and intracranial pressure Intracranial pressure waveform The physiological variables that regulate cerebral blood flow (CBF) are the factors that influence acute changes in Brain tissue pressure and ICP increase with each cardiac ICP. Arterial carbon dioxide gas tension (PaCO2) has a cycle and, thus, the ICP waveform is a modified arterial near linear relationship with CBF within the physiological pressure wave. The ICP pressure waveform has three range, producing a 2–6% increase of CBF for each mil- distinct components that are related to physiological pa- limetre of mercury of PaCO2 rise. An inverse relationship rameters (Fig. 1). The first peak (P1) is the “percussive” links low arterial oxygen content and CBF. wave and is due to arterial pressure being transmitted A direct relationship exists between CBF and cerebral from the choroid plexus to the ventricle. It is sharply metabolic rate for oxygen and glucose. CBF is kept peaked and fairly consistent in amplitude. The second constant throughout the normal physiological range of wave (P2), often called the “tidal” wave, is thought to be arterial pressure in health. These responses are often im- due to brain tissue compliance. It is variable, indicates cerebral compliance and generally increases in amplitude
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 109 DOI: 10.1007/978-3-642-01769-8_26, © Springer-Verlag Berlin Heidelberg 2009 1883 110 G. Citerio and P.J.D. Andrews
Fig. 1 The intracranial pressure waveforms. The upper tracing is an example of an ICP waveform from a patient monitoring system in which can be identified the three distinct components, as indicated in the text. A depicts the situation of a compliant system, B A high pressure wave recorded from a non-compliant system in which P2 exceeds the level of the P1 waveform, due to a marked decrease in Fig. 2 Schematic representation of herniation syndromes. Ac- cerebral compliance cording to the Monro & Kellie doctrine, increased volume and pressure in one compartment of the brain may cause shift of brain tissue to a compartment in which the pressure is lower. M1 is an as compliance decreases; if it elevates or exceeds the level expanding supratentorial lesion; M2 is an expanding mass in the of the P1 waveform there will be a marked decrease in posterior fossa. A Increased pressure on one side of the brain may cause tissue to push against and slip under the falx cerebri toward cerebral compliance. P3 is due to the closure of the aortic the other side of the brain, B Uncal (lateral transtentorial) hernia- valve and therefore represents the dicrotic notch. tion. Increased ICP from a lateral lesion pushes tissue downward, initially compressing third cranial nerve and, subsequently, as- cending reticular activating system, leading to coma, C Infraten- torial herniation. Downward displacement of cerebellar tissue Brain distortion through the foramen magnum producing medullar compression and coma There are several different, but related, factors that have to be taken into consideration when a mass lesion within the cranial cavity starts to expand. One is distortion of the determine whether the prognosis of a patient can be ob- brain. Because of the viscoelastic properties of the brain, tained from ICP. Data from large prospective trials car- the tissues adjacent to the lesion will tend to flow away ried out from single centres and from well-controlled from it with axial movement of the brain as well as con- multi-centre studies have provided the most convincing ventional displacement. Although this suggests that the evidence for a direct relationship between ICP and out- local properties of the brain are important, the major fac- come. J. Douglas Miller and others [1] made detailed doc- tor responsible for spatial compensation is a reduction in umentation of ICP during intensive care after traumatic the volume of intracranial cerebrospinal fluid (CSF). The brain injury (TBI). A strong relationship exists with sur- sequence of events is, therefore, local deformity with vival and a recent analysis of the same data-set by re- displacement of CSF, shift and distortion of the brain and gression tree methodology shows a strong relationship eventually the appearance of internal herniae in the intact between ICP and functional recovery. cranium (Fig. 2). These are the displacement of brain tis- Narayan, in a prospective study in 133 severely head- sue from one intracranial compartment to another or the injured patients, demonstrated that the outcome prediction spinal canal. These herniae, in turn, lead to the develop- rate was increased when the standard clinical data such as ment of pressure gradients because of obliteration of sub- age, Glasgow Coma Score on admission (GCS) and pu- arachnoid space and cisterns and secondary vascular com- pillary response with extra-ocular and motor activity were plications such as haemorrhage and ischaemic brain dam- combined with ICP monitoring data [2]. Marmarou, re- age. porting on 428 patients’ data from the National Institute of Health’s Traumatic Coma Data Bank, showed that, following the usual clinical descriptors of age, admission Prognosis motor score and abnormal pupils, the proportion of hourly ICP recordings greater than 20 mmHg was the next Almost from the time of the first attempt to monitor ICP most significant predictor of outcome [3]. Jones studied in acute intracranial pathology, researchers have tried to prospectively 124 adult head-injured patients during in- 1884 Intracranial pressure Part two: Clinical applications and technology 111 tensive care using a computerised data collection sys- tem capable of minute-by-minute monitoring of up to 14 clinically indicated physiological variables [4]. She found that ICP above 30 mmHg, arterial pressure below 90 mmHg and cerebral perfusion pressure (CPP) below 50 mmHg significantly affected patient morbidity. In children, after TBI, Jones examined the early pre- dictive value of any physiological derangement in ICU monitored parameters. This multi-centred study was novel in that abnormalities in ICP, blood pressure, heart rate and temperature were recorded when age-specific normal physiological thresholds were breached. ICP, managed according to a CPP protocol, was strongly predictive if Fig. 3 Sites of measurement of intracranial pressure abnormal in the initial ICU 48 h. Although, in the past, there have been differing opin- ions about the contribution of continuous monitoring of a standard against which other devices can be com- ICP to reduction in mortality and morbidity following pared ”. This sentence still stands. head injury, there is now sufficient evidence to remove A ventricular catheter connected to an external strain doubt about the value of ICP monitoring towards im- gauge is the most accurate and low-cost method for ICP proving outcome and allowing more informed decisions monitoring. This method has proved to be reliable and to be made about patient management. permit periodic re-zeroing and it also allows the benefit of therapeutic CSF drainage. Nevertheless, the potential risks of difficult positioning, in the presence of ventricular Monitoring technology compression, and obstruction have lead to alternative in- tracranial sites for ICP monitoring (Fig. 3). In 2004, the The modern era of ICP monitoring started in the decade most common location for ICP monitoring is the cerebral between 1950 and 1960. In 1951, Guillaume and Janny parenchyma. ICP measurements obtained with intra- reported, even if their work went largely unnoticed, con- parenchymal transducers correlate well with the values tinuous clinical measurement of ICP with the use of an obtained with intraventricular catheters. Contemporary in- inductance manometer. In the United States, Ryder and traparenchymal transducers may be classified as solid Evans extended their physiological studies to patients. state, based on silicon chips with pressure-sensitive re- A milestone in the history of ICP recording was the sistors forming a Wheatstone bridge, or of fiberoptic de- work carried out by Nils Lundberg (1965) on the use of sign. Although both systems are very accurate at the time bedside strain gauge manometers to record ICP continu- of placement, they have been reported to zero-drift over ously by ventriculostomy in more than 400 patients. time, which can result in an error after 4 or 5 days. Most Lundberg, anticipating modern practice, wrote in 1965 clinicians, however, use these devices for a short period of that “The greatest value of recording the ventricular fluid time and these potential inaccuracies may not be clini- pressure is the information it gives in cases of severe cally relevant. The cost of these devices is higher than the injury of the brain without hematoma. In these cases, conventional ventricular system. Subdural and epidural intervention to decrease intracranial pressure by such monitors (fluid-coupled, pneumatic, solid state and fi- means as hypertonic solutions, hyperventilation, hypo- beroptic) and externally placed anterior fontanelle moni- thermia, drainage of fluid and removal of localized con- tors are less accurate. As the wise Douglas Miller wrote: tusions, may be more rationally applied.” The systematic “It is difficult to know when the subdural catheter is un- application of those monitoring systems to the manage- derreading. For this reason, the method is being used less ment of acute TBI did not take place for almost another and less”. decade. The overall safety of ICP monitoring devices is ex- By the mid 1970s, monitoring by means of a strain cellent, with clinically significant complications (e.g. in- gauge pressure transducer had begun to pervade neuro- fection and haematoma) occurring infrequently. surgical practice influenced by Becker and Miller’s good results in 160 traumatic brain-injured patients, using continuous ICP monitoring with a Statham strain gauge, How do intracranial pressure treated according to defined clinical algorithms over a 4- data help patient management? year period. In 1981, Flitter wrote that the technique used by The care of patients with acute brain injury and ICP Lundberg—the ventricular catheter and strain gauge trans- monitoring is a cause for ongoing debate. There are few ducer —for continuous monitoring “continues to serve as prospective randomised controlled trials of ICP inter- 1885 112 G. Citerio and P.J.D. Andrews ventions and no trial of ICP monitoring against no- all unconfounded randomised trials [6, 7]. They con- ICP monitoring. When the Traumatic Coma Data Bank cluded that existing trials have been too small to support (TCDB) members approached the NIH to fund such a trial or refute the existence of a real benefit from using these more than 14 years ago the view was that there was al- strategies and that further large-scale randomised trials of ready sufficient evidence to support the use of ICP mon- these interventions are required. itoring after TBI. These data included observational trials that showed a progressive reduction in mortality after TBI when ICP monitoring was instituted and subsequently Conclusion when ICP was managed to a lower threshold [5]. Nevertheless, no monitor will improve outcome on its Current management strategies for acute brain injury own. ICP data allow the clinician to manage the patient patients encompass the principle of physiological stabil- with an acute brain injury based upon objective data and ity. Although there is debate about which precise thresh- improved outcomes will only occur if the data obtained olds should be striven for, without monitoring intracranial are integrated into an appropriate therapeutic strategy. To pressure (ICP) considerable information is missing and date there are no adequately powered trials with patient objective management of the patient is not possible. In- outcome as the primary measure that have assessed an terventions to reduce ICP are double-edged swords and intervention for raised ICP. The Cochrane injuries group direct measurement will reduce their indiscriminate us- reviewed the available data to assess the effectiveness of age. ICP monitors are inexpensive and have an acceptably interventions routinely used in the intensive care man- low complication rate. They offer a high yield in infor- agement of severe head injury, specifically: hyperventi- mation gained and should be the cornerstone of all critical lation, mannitol, CSF drainage, barbiturates and corti- care management of acute brain injury. costeroids, using the methodology of systematic review of
References
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Abstract Background: Monitor- Abbreviations ABP: arterial blood ing the injured brain is an integral pressure · AMP: amplitude of part of the management of severely fundamental component of ICP brain injured patients in intensive waveform · CBF: cerebral blood care. Brain-specific monitoring tech- flow · CBV: cerebral blood volume · niques enable focused assessment of CO2: carbon dioxide · CPP: secondary insults to the brain and cerebral perfusion pressure · CSF: may help the intensivist in making cerebrospinal fluid · CT: appropriate interventions guided by computerised tomography · DID: the various monitoring techniques, delayed ischaemic neurological thereby reducing secondary brain deficit · EDP: effective downstream damage following acute brain injury. pressure · FV: flow velocity · HDI: Discussion: This review explores haemodynamic impairment · ICP: methods of monitoring the injured intracranial pressure · ICU: intensive brain in an intensive care unit, in- care unit · LDF: laser Doppler cluding measurement of intracranial flowmetry · MAP: mean arterial pressure and analysis of its wave- pressure · MCA: middle cerebral form, and techniques of cerebral artery · MRI: magnetic resonance blood flow assessment, including imaging · nCPP: non-invasively transcranial Doppler ultrasonography, determined cerebral perfusion laser Doppler and thermal diffusion pressure · nICP: non-invasive ICP flowmetry. Conclusions: Various measurement · PET: positron modalities are available to monitor emission tomography · PI: pulsatility the intracranial pressure and assess index · PRx: pressure reactivity cerebral blood flow in the injured index · RI: resistance index · RAP: brain in intensive care unit. Knowl- correlation of amplitude and pressure edge of advantages and limitations of of ICP waveform · SAH: the different techniques can improve subarachnoid haemorrhage · TBI: outcome of patients with acute brain traumatic brain injury · TCD: injury. transcranial Doppler · TD: thermal diffusion · THRT: transient Keywords Traumatic brain injury · hyperaemic response test · US: Intracranial pressure · Ultra- ultrasound · ZFP: zero flow pressure sonography, Doppler, transcranial · Flowmetry, laser Doppler · Thermal diffusion flowmetry
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 113 DOI: 10.1007/978-3-642-01769-8_27, © Springer-Verlag Berlin Heidelberg 2009 114 A. Bhatia and A.K. Gupta
Introduction published trial in survivors beyond 24 h following severe brain injury that compared ICP-targeted intensive care Whilst there is little that neurointensive care can offer with management based on clinical observations and to prevent the brain damage sustained from the primary CT findings reported no improvement in outcome with insult, the use of appropriate protocol-driven management ICP monitoring [5]. However, a review of neurocritical can, however, minimise the effects of secondary insults care and outcome from traumatic brain injury (TBI) sug- on outcome [1]. Monitoring the injured brain is an in- gested that ICP-/cerebral perfusion pressure (CPP)-guided tegral part of the management of severely brain injured therapy may benefit patients with severe head injury, patients in intensive care and can be classified into general including those presenting with raised ICP in the absence (systemic) and brain-specific methods. Although general of a mass lesion and also patients requiring complex systemic monitoring (e.g. invasive arterial blood pressure, interventions [1]. end-tidal carbon dioxide, oxygen saturation of blood) is of vital importance in detecting gross global changes in physiology, brain-specific monitoring techniques enable Measurement of ICP more focused assessment of secondary insults to the brain and may help the intensivist in making appropriate ICP can be measured at different sites in the brain–intra- interventions guided by the various monitoring techniques. ventricular and intraparenchymal measurements are more An important adjunct to these techniques is the use common, while extradural and subdural sensors are used of a variety of imaging modalities, which, as a result of occasionally. Intraventricular catheters are still thought significant advances over the last two decades, allow us to of as the “gold standard” [6] as they allow direct meas- assess the brain with respect to structural abnormalities, urement by insertion of a catheter into one of the lateral blood flow and metabolism. The advantage of these ventricles, which is connected to an external pressure techniques [computerised tomography (CT), magnetic transducer [7]. The advantages of these systems are that resonance imaging (MRI), xenon-CT, positron emission the clinician can check for zero drift and sensitivity of tomography, single photon emission computerised emis- the measurement system in vivo. Access to the ventric- sion tomography, magnetic resonance spectroscopy] is that ular system also allows CSF drainage if the ICP rises. they allow us to assess the interindividual heterogeneity However, this interferes with ICP monitoring, and only by providing detailed information of different regions of one currently available catheter allows concomitant CSF the brain. However this information is not continuous and drainage and ICP monitoring (Rehau, Switzerland). The at present cannot be obtained at the bedside. drawbacks of such catheters include difficulty or failure This review focuses on brain-specific monitoring and of insertion in patients with advanced brain swelling, as will include aspects of intracranial pressure measurement the ventricles can be narrowed or effaced. An increase and its interpretation, and methods to monitor cerebral in risk of infection after a period of time is another blood flow. potential problem, with reported rates of up to 10% [8] with modern ventricular micro-transducers even though these have excellent metrological properties [9]. There Intracranial pressure monitoring are now commercially available ventricular catheters Intracranial pressure (ICP) is the pressure within the cra- with antibiotic-coated tips [Codman Bactiseal® external nial vault relative to the ambient atmospheric pressure and ventricular drain catheter] that may reduce infection rates is now regarded as a core monitoring parameter in the in- but more studies are required before their use in clinical tensive care management of patients with acute brain in- practice can be supported. jury. The ICP increases when compensatory mechanisms The intraparenchymal systems may be inserted through which control ICP, such as changes in cerebrospinal fluid a support bolt or tunnelled subcutaneously from a burr (CSF) dynamics, cerebral blood flow (CBF) and cerebral hole. These have a micro-miniature strain gauge pressure blood volume (CBV), are exhausted. sensor side-mounted at the tip (Codman) or a fibre-optic Whilst routine ICP monitoring is widely accepted as catheter (Camino, Innerspace). Change of pressure results a mandatory monitoring technique for management of in a change of resistance in the former and an alteration in patients with severe head injury and is a guideline sug- reflection of the light beam in the latter. Intraparenchymal gested by the European Brain Injury Consortium [2], there probes are a good alternative to ventricular catheters and is some debate over its efficacy in improving outcome have a low infection rate [10], but in one study a signifi- from severe traumatic brain injury. A survey of Canadian cant increase in colonisation at 5 days after insertion was neurosurgeons revealed that only 20.4% of the respondents reported [11]. The main problem with these catheters is had a high level of confidence in ICP monitoring [3], and a small drift of the zero line. Neither of these systems a survey of neurointensive care units in the UK showing allows pressure calibration to be performed in vivo. that only 75% of centres monitor ICP may reflect some After these systems are zeroed relative to atmospheric of the drawbacks of ICP monitoring [4]. A recently pressure during a pre-insertion calibration, their output Neuromonitoring in the intensive care unit. Part I. Intracranial pressure and cerebral blood flow monitoring 115 is dependent on the zero drift of the sensor. Technical Foundation guidelines recommend ICP treatment should complications such as kinking of the cable and dislocation be initiated at an upper threshold of 20–25 mmHg [18]. of the sensor have also been reported [12]. It should be remembered that these sensors reflect a local pressure value that may be misleading, as the ICP is not uniform Waveform analysis within the skull, e.g. supratentorial measurements may not reflect infratentorial pressure. However, this is also Analysis of ICP waveforms can be used to obtain infor- a problem with intraventricular catheters. mation about brain compliance. A computer program to Subdural catheters are easily inserted following cran- correlate mean ICP and AMP has been developed [19]. iotomy but measurements are unreliable because when The ICP waveform consists of three components, which ICP is elevated, they are likely to underestimate the true overlap in the time domain but can be separated in the ICP. These are also liable to blockage. Extradural probes frequency domain. The pulse waveform has several have the advantage of avoiding penetration of the dura harmonic components; the fundamental component has but are even more unreliable as the relationship between a frequency equal to the heart rate. The amplitude of this ICP and pressure in the extradural space is unclear. The component (AMP) is very useful for the evaluation of Gaeltec ICP/B solid-state miniature ICP transducers are various indices. The linear correlation coefficient RAP designed for use in the epidural space and are reusable, (R = symbol of correlation, A = amplitude, P = pressure) and the zero reference can be checked in vivo. However, describes the relationship between pulse amplitude of measurement artefacts and decay in measurement quality ICP and mean ICP value over short periods of time with repeated use have limited the acceptance of this (1–3 min). When RAP is positive, changes in AMP are in technology [13]. Despite these drawbacks, the subdural the same direction as changes in mean ICP. When RAP and epidural catheters are associated with a lower risk is negative, the change in AMP is reciprocal to those in of infection, epilepsy and haemorrhage than ventricular mean ICP value. Lack of synchronisation between fast catheters [14, 15]. changes in amplitude and mean ICP is depicted by a RAP The Spiegelberg ICP monitoring system is a fluid- of 0. A potential application of this model is to predict filled catheter-transducer system that measures ICP using outcome after severe head injury. This is possible because a catheter that has an air-pouch balloon situated at the of the nature of relationship between mean ICP and tip. This device zeroes automatically in vivo and has AMP—as the ICP increases, the linear correlation with shown lower zero drift than standard catheter-tip ICP de- AMP becomes distorted by an upper breakpoint which is vices [16]. This system can be used in epidural, subdural, associated with a decrease in RAP coefficient from +1 to intraparenchymal and intraventricular sites. Despite its negative values. A similar relationship between AMP and obvious advantages, this system is still not used widely ICP is seen in patients with severe brain injury. A plot of and requires further evaluation. RAP against ICP shows similar results—RAP is positively ICP monitoring has several important applications, correlated to ICP in patients with good outcomes, whereas some of which are discussed below: the correlation decreases above ICP values of 20 mmHg and becomes negative above 50 mmHg in patients who die (Fig. 1) [20]. In the latter group of patients, the decrease Determination of CPP in RAP from +1 to 0 or negative precedes the final de- crease in ICP pulse amplitude and is a sign of impending Management of acute brain injury is largely CPP directed. brainstem herniation. ICP is an important determinant of CPP [CPP = mean arte- rial pressure (MAP)–ICP], which in turn affects CBF and CBV. The optimal level of CPP is still under some debate, Cerebrovascular pressure reactivity and derived indices with earlier studies recommending CPP > 70 mmHg [16] although many other centres maintain CPP between 60 Cerebrovascular pressure reactivity, which is the change and 70 mmHg and one centre permits CPP as low as in basal tone of smooth muscle in cerebral arterial walls 50 mmHg [17]. in response to changes in transmural pressure, can be es- timated from the ICP waveform by deriving the pressure reactivity index (PRx). PRx has been used to determine ICP correlation with outcome time responses to intracranial hypertension or changes in mean arterial blood pressure in brain-injured patients [21]. Experience from various centres with expertise in ICP PRx is calculated as a linear correlation coefficient be- monitoring and research into TBI confirms that mean ICP tween averaged arterial blood pressure and ICP from a time correlates with outcome with a threshold in the region of window of 3–4 min. Good cerebrovascular reactivity is 25 mmHg. However no prospective study has been un- associated with negative PRx and a poor reactivity with dertaken (and is unlikely) to prove this and Brain Trauma a positive PRx value (Fig. 2). The PRx may be analysed as 116 A. Bhatia and A.K. Gupta
Fig. 1 Pulse amplitude of intracranial pressure (ICP) (AMP, fundamental harmonic component) increases with mean ICP until critical threshold is reached, above which it starts to decrease. The correlation coefficient between AMP and ICP (RAP) marks this threshold by decreasing from positive to negative values [20]
Fig. 2 PRx index, calculated as linear correlation coefficient between averaged ABP and ICP. Good cerebrovascular reactivity is associated with negative PRx (a) and poor reactivity with positive PRx (b) [21] Neuromonitoring in the intensive care unit. Part I. Intracranial pressure and cerebral blood flow monitoring 117 a time-dependent variable, responding to dynamic events generally derived from the MCA as it is easy to insonate, such as ICP plateau waves or incidents of arterial hypo- carries a large proportion of supratentorial blood and its and hypertension. The validity of PRx for monitoring and location allows easy fixation of the probe (to keep the quantifying cerebral vasomotor reactivity has been stud- angle of insonation constant) for prolonged monitoring. ied in patients with brain injury. A close link was found The transtemporal window through the thin bone above between cerebral blood flow and intracranial pressure in the zygomatic arch is commonly used to insonate the head-injured patients. This suggested that increases in arte- proximal segment (M1) of the MCA. In each patient, the rial blood pressure and cerebral perfusion pressure may be same insonation window should be used throughout the useful for reducing intracranial pressure in selected brain- entire study period. injured patients, i.e. those with intact cerebral vasomotor As the volume of blood flowing through a vessel de- reactivity [22]. pends on the velocity of the moving cells and the diameter There are drawbacks of monitoring ICP. It requires an of the vessel concerned, then for a given blood flow, the invasive procedure and personnel to monitor as well as to velocity will increase with decreases in vessel diameter. react to changes. ICP monitoring is frequently performed Figure 3 shows a diagrammatic representation of a typi- by non-neurointensivists. A survey of intensive care units cal TCD waveform from the MCA. Mean FV (FVmean)is (ICU) in non-neurosurgical centres in the UK revealed that the weighted mean velocity that takes into account the dif- though more than half of all such ICUs were admitting pa- ferent velocities of the formed elements in the blood ves- tients with severe TBI, only 9% used ICP monitoring as sel insonated and is normally around 55 ± 12 cm s–1.This a routine [23]. This has significant implications, especially represents the most physiological correlate with the actual as there is a lack of class I evidence about the efficacy of CBF. The time-mean FV refers to the mean value of FVmax ICP monitoring in reducing morbidity and mortality. and is determined from the area under the spectral curve. It is possible that uptake of ICP monitoring may The shape of the envelope (maximal shift) of the increase if a non-invasive technique can be used. There Doppler spectrum from peak systolic flow to end- is currently keen interest in development of non-invasive diastolic flow with each cardiac cycle is known as the methods of ICP monitoring which include the use of waveform pulsatility. The FV waveform is determined transcranial Doppler ultrasonography [24]. An example of by the ABP waveform, the viscoelastic properties of this is a procedure for continuously simulated ICP derived the cerebral vascular bed and blood rheology. In the from simultaneously recorded curves of ABP and flow absence of vessel stenosis or vasospasm, changes in velocity (FV) in the middle cerebral artery (MCA) that has ABP or blood rheology, the pulsatility reflects distal been validated in patients with TBI [25]. This approach in- cerebrovascular resistance. This resistance is usually volves a dynamic systems analysis technique and enables quantified by the pulsatility index (PI or Gosling index): modelling of physiological systems in which the inner PI = (FVsystolic –FVdiastolic)/FVmean. Normal PI ranges structure is too complex to be described mathematically. from 0.6 to 1.1 with no significant side-to-side or cerebral The validity of this model was confirmed during infusion interarterial differences and shows better correlation with studies in patients with hydrocephalus [26]. Use of such non-invasive ICP (nICP) measurement techniques may make ICP monitoring accessible to a wider range of ICUs.
Assessment of blood flow Transcranial Doppler ultrasonography
Transcranial Doppler ultrasonography (TCD) is an ex- tremely useful method for non-invasively monitoring cerebral haemodynamics, by measuring red cell FV in real time using the Doppler shift principle. Ultrasound (US) waves are generated using a 2-MHz pulsed Doppler instru- ment. In order to penetrate the skull, the same transducer is used both for transmitting and receiving wave energy at regular intervals. The moving blood acts as a reflector, first receiving the transmitted wave from the transducer and Fig. 3 Method of determining systolic (Vs), diastolic (Vd)andtime- then reflecting it back. FV is calculated using the formula averaged mean flow velocity (Vmean) from the spectral outline. FV is flow velocity and PI is pulsatility index [PI =(Vs –Vd)/Vmean]. for Doppler shift. Changes in FV correlate with changes (Reproduced with permission from Greenwich Medical Media. In: in CBF only if the angle of insonation and the diameter Gupta AK, Summors A, Notes in Neuroanaesthesia and Critical of the insonated vessel remain constant [27]. Data are Care, 2001) 118 A. Bhatia and A.K. Gupta
CPP than ICP. Another index that can be used to quantify TCD indices failing to indicate these changes [33]. Thus vessel resistance is the resistance index (RI or Pourcelot detection of vasospasm on TCD may not be associated index): RI = (FVsystolic –FVdiastolic)/FVsystolic. with delayed cerebral ischaemia and vice versa. Care must therefore be taken when interpreting TCD data, and these should be matched with clinical findings, and other Applications of TCD investigations such as xenon-CT flow measurements may help to improve prediction of vasospasm and hence avoid There are many advantages of using TCD. It is non- repeated angiography [34]. However, when compared with invasive, relatively inexpensive and provides real-time angiography for the MCA, TCD has been shown to give information with high temporal resolution. Some of the high levels of specificity and positive predictive value for clinical applications of TCD include the following: vasospasm. Ratsep et al. found that vasospasm detected by TCD is associated with haemodynamic impairment (HDI, defined as blood flow velocity values consistent Assessment of cerebral autoregulation and vasoreactivity with vasospasm in conjunction with impaired THRT); thus, detection of HDI could identify patients at risk for TCD is used in assessment of cerebral autoregulation ischaemic complications [35]. and vasoreactivity to carbon dioxide (CO2)aslossof these mechanisms in patients with brain injury may indicate a poor prognosis. Autoregulation can be tested by Role of TCD in management of traumatic brain injury response of the TCD trace to vasopressor infusion (static autoregulation) or thigh tourniquet deflation (dynamic Following traumatic brain injury, TCD monitoring can be autoregulation). Autoregulation may also be tested at used to observe changes in FV, waveform pulsatility and the bedside using the transient hyperaemic response test for testing cerebral vascular reserve. The autoregulatory (THRT) [28], which assesses the hyperaemic response “threshold” or “breakpoint” (the CPP at which autoregula- in the TCD waveform following 5–9 s of digital carotid tion fails), which provides a target CPP value for treatment, artery compression. Lam et al. found that following an can also be determined by continuously recording the FV aneurysmal subarachnoid haemorrhage, patients with from the MCA. At very low levels of CPP, as in brain an initial impairment of the response to THRT were death, the microcirculation collapses. The net blood flow more likely to develop delayed ischaemic neurological diminishes, and the TCD pattern either shows low flow or deficits (DIDs) than patients with a normal response [29]. reversed flow during diastole. In a study using induced oscillations in the ABP (by controlling ventilation) and calculating the phase shifts between FV (measured using TCD) and ABP, cerebral Non-invasive determination of CPP autoregulation was found to be impaired preceding the onset of clinical vasospasm [30]. There is currently much interest in the use of TCD for non- invasive determination of CPP (nCPP). This involves esti- mation of CPP from parameters derived from MCA FV Detection of vasospasm following subarachnoid and the ABP [24]. Schmidt et al. found that absolute dif- haemorrhage ference between real CPP (i.e. MAP–ICP) and nCPP (i.e. determined using TCD) was less than 13 mmHg in the ma- TCD is often used in the clinical setting to determine jority of measurements for a range of CPPs between 60 presence of vasospasm. The primary effect of a decrease and 100 mmHg. Such a difference may have significant im- in vessel lumen diameter is an increase in flow resistance, plications in patients with raised ICP (and possibly lower and this results in an increase in FV. An MCA FVmean CPP). The absolute value of side-to-side (i.e. interhemi- above 120 cm s–1 is regarded as being significant [31] and spheric) difference in nCPP was significantly greater when may indicate either hyperaemia or vasospasm. Although CT evidence of brain swelling was present and was also it is generally regarded that vasospasm is likely if the correlated with mean ICP [36]. This technique needs to ratio of MCA FV to extracranial ICA FV (Lindegaard be evaluated in further randomised trials focusing on its ratio) is greater than 3 [32] and hyperaemia is present accuracy, cost-effectiveness and validity before it can be if MCA FV > 120 cm s–1 with a Lindegaard ratio less recommended for routine use. than 3, the distinction is not well defined, especially when commonly used TCD indices for diagnosis of vasospasm are compared with cerebral perfusion findings Measurement of zero flow pressure using PET. PET scans of patients following subarach- noid haemorrhage (SAH) who developed DIDs showed A recent development is the use of TCD to measure zero a wide range of cerebral perfusion disturbances, with flow pressure (ZFP), i.e. the pressure at which CBF ceases, Neuromonitoring in the intensive care unit. Part I. Intracranial pressure and cerebral blood flow monitoring 119 which gives an estimate of the effective downstream pres- race, may cause problems with transmission of ultrasound. sure (EDP) of the cerebral circulation (Fig. 4). EDP, rather In fact, 10% of normal subjects cannot be assessed due than ICP, is believed to determine the effective CPP in the to lack of an adequate temporal window. The incidence of absence of intracranial hypertension. FV in the MCA is failure can be reduced by increasing the power and perhaps measured by TCD. EDP is derived from the ZFP as extra- by use of 1 MHz probes [41]. In addition, TCD monitoring polated by regression analysis of instantaneous ABP/MCA focuses on the major cerebral arteries but flow character- FV relationships. Buhre et al. reported that extrapolation of istics in the cerebral microcirculation may be quite differ- ZFP enables detection of elevated ICP in patients with se- ent to those in the major arteries. Despite these limitations, vere head injury [37]. Thees et al. studied the correlation TCD holds promise of further applications for real-time between critical closing pressure determined using TCD indirect assessment of CBF, non-invasive ICP and CPP. and ICP measured invasively. They found that using ICP to determine CPP might overestimate the effective CPP, i.e. the difference between MAP and CCP [38]. Further Laser Doppler flowmetry evaluation is needed before this non-invasive technique of measuring CPP can be accepted as a standard. Laser Doppler flowmetry (LDF) allows continuous real- time measurements of local microcirculatory blood flow (red cell flux) with good dynamic resolution. Doppler Confirmation of brain death shift of reflected monochromatic laser light induced by movement of red blood cells within the microcirculation TCD has been suggested as a highly specific and sensi- is measured. The magnitude and frequency distribution tive test for confirmation of brain death. It can be a useful of the wavelength changes are directly related to the method to confirm brain death in patients in whom tradi- number and velocity of red blood cells but unrelated to the tional brain death criteria cannot be used because of pos- direction of their movement. A 0.5–1 mm diameter fibre- sible residual effects of sedative drugs [39]. The transtem- optic laser probe is placed in contact with or within brain poral approach is commonly used but the transorbital ap- tissue and conducts scattered light back to a photodetector proach has also been successfully employed [40]. within the flowmeter sensor. The signal is processed to The limitations of using TCD are that it requires a cer- give a continuous voltage fluctuation versus time which is tain degree of technical expertise, is operator dependent, linearly proportional to the real blood flow [42]. The probe and the skull thickness, which varies with age, gender and can be positioned in proximity to an area of intracranial injury to monitor pathologic variations of microvascular blood flow. LDF is considered an excellent technique for instanta- neous, continuous and real-time measurements of regional CBF and for assessment of relative regional CBF changes. LDF has a quick response to fluctuations in tissue per- fusion and is relatively inexpensive. The relationship be- tween LDF and CPP has been found to change with time, and this can indicate an improvement or deterioration in autoregulation [43]. The main drawbacks of this technique are that it is not a quantitative measure of CBF and mea- sures CBF in a small brain volume (1–2 mm3). It is inva- sive and prone to artefacts produced by patient movement or probe displacement, which limits its clinical applicabil- ity. However, it is a useful measure of local microcircula- tory changes in combination with other monitoring tech- niques and has been used to assess autoregulation, CO2 reactivity and responses to therapeutic interventions [44] and to detect ischaemic insults [45, 46].
Thermal diffusion flowmetry
Thermal conductivity of cerebral cortical tissues varies Fig. 4 Direct assessment of cerebral zero flow pressure. In a patient with severe intracranial hypertension, no flow was observed in the proportionally with CBF, and measurement of thermal middle cerebral artery during diastole. The epidurally measured ICP diffusion (TD) at the cortical surface can be used for was 48 mmHg. (Reproduced with permission from [37]) CBF determination [47]. A monitor that measures TD 120 A. Bhatia and A.K. Gupta
flowmetry consists of two small metal plates, which are flowmetry was characterised by more favourable diagnos- thermistors, one of which is heated. Insertion of a TD tic reliability and was reported to be more sensitive than probe on the surface of the brain at a cortical region of TCD ultrasonography in assessing patients with reversible interest allows CBF to be calculated from the temperature vasospasm following intra-arterial injection of papaverine difference between the plates. An intraparenchymal TD in patients with SAH [52]. probe has also been evaluated and the results are encour- TD flowmetry has the potential for bedside monitor- aging [48]. Although the changes in CBF are relative, the ing of cerebral perfusion at the tissue level, but it is inva- probes may be calibrated against absolute methods such sive and more clinical trials are needed to validate its use. as xenon-133 or xenon-CT measurement of CBF to give The intraparenchymal probes have excellent temporal res- absolute values that assess blood flow changes in a small olution and it is possible that in the future a large part of volume of brain (± 20–30 mm3). Placement of the sensor a single vascular territory may be monitored with single or over large surface vessels should be avoided. Similar multiple probes. sensors have been used to guide therapy for patients with This review has explored methods of assessing and severe brain injury and intracerebral haematomas [49, 50]. measuring intracranial pressure and cerebral blood flow Animal studies by Vajkoczy et al. revealed that TD in the injured brain in the intensive care unit. Appropriate microprobes provide continuous real-time assessment of use and knowledge of benefits and limitations of these intraparenchymal regional blood flow that was compar- techniques can improve the outcome of patients with acute able with measurement by xenon-enhanced CT [51]. TD brain injury.
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care. There is increasing interest in Abbreviations a-vDO2: methods to monitor global and re- arteriovenous oxygen content gional cerebral oxygenation. There difference · CBF: cerebral blood have been significant advances in flow · CMRO2: cerebral metabolic analysing tissue oxygenation and rate of oxygen · CPP: cerebral local metabolites in the injured brain perfusion pressure · over the past decade. Discussion: CT: computerised tomography · Cerebral oxygenation can be assessed CytOx: cytochrome aa3 · on a global or regional basis by jugu- EEG: electroencephalogram · lar venous oximetry and near infra-red GABA: γ-amino-butyric acid · spectroscopy respectively. Techniques Hb: haemoglobin (deoxygenated) · of brain tissue oxygenation monitor- HbO2: haemoglobin (oxygenated) · ing and microdialysis are also covered ICP: intracranial pressure · in this review. Conclusions: Various NIRS: near-infrared spectroscopy · modalities are available to monitor PbO2: brain tissue oxygen partial oxygenation and the local milieu in pressure · PbCO2: brain tissue the injured brain in the intensive care carbon dioxide partial pressure · unit. Use of these modalities helps to PET: positron emission tomography · optimise brain oxygen delivery and SAH: subarachnoid haemorrhage · metabolism in patients with acute SjvO2: jugular venous oxygen brain injury. saturation · TBI: traumatic brain injury · TCD: transcranial Doppler · Abstract Background: Monitor- Keywords Traumatic brain injury · TOI: tissue oxygenation index ing the injured brain is an integral Oximetry, jugular venous · part of the management of severely Spectroscopy, near-infrared · brain injured patients in intensive Microdialysis
Assessment of cerebral oxygenation to measure cerebral oxygenation should be employed in such patients to ensure optimal oxygen delivery to the Methods for assessing whole body oxygenation (e. g. injured brain. Measurement of cerebral oxygenation can pulse oximetry, arterial blood gas analysis) are not reliable be divided into global methods such as jugular venous indicators of cerebral oxygenation in patients with trau- oximetry and regional methods including near-infrared matic brain injury (TBI) or brain pathology. Techniques spectroscopy (NIRS) and tissue probes.
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 123 DOI: 10.1007/978-3-642-01769-8_28, © Springer-Verlag Berlin Heidelberg 2009 124 A. Bhatia and A.K. Gupta
Jugular venous oximetry by CMRO2) and supply (i. e. CBF), thereby affecting SjvO2 (Table 1). Jugular venous oxygen saturation (SjvO2) provides an in- In addition to measuring venous oxygen saturation, direct assessment of cerebral oxygen utilisation and is used this technique allows estimation of arteriovenous oxygen to guide therapy in the neurocritical care unit. Blood from content difference (a-vDO2) and lactate by intermittent the venous sinuses of the brain drains via the internal jugu- sampling. Increase in a-vDO2 to greater than 9 ml/dl lar veins into the right atrium. Measurement of SjvO2 can provides a useful marker of inadequate CBF. There determine adequacy of the balance between global cere- is good evidence to suggest that increases in a-vDO2 bral blood flow (CBF) and cerebral metabolic demands. indicate increased oxygen extraction by the brain and/or A fibre-optic catheter is inserted retrograde into the in- inadequate blood flow [3, 4]. ternal jugular vein and advanced cephalad beyond the in- SjvO2 has many potentially useful applications in man- let of the common facial vein into the jugular bulb at the agement of patients in neurocritical care: base of the skull. Correct placement is confirmed when the catheter tip is level with the mastoid air cells on the lateral neck radiograph (level with the bodies of C1/C2). Monitoring adequacy of CBF Aspiration of blood from the jugular bulb is rep- resentative of mixed cerebral blood. Although there is SjvO2 monitoring allows detection of episodes of desat- no evidence to suggest that either side is better [1] and uration associated with raised intracranial pressure (ICP) supratentorial venous drainage is less lateralised than pre- and hyperventilation therapy. Robertson et al. reported viously thought, the right jugular vein is more frequently episodes of jugular venous desaturation (SjvO2 < 50%) in cannulated [2]. Continuous monitoring of SjvO2 can be patients with severe brain injury; intracranial hypertension performed with catheters that employ two wavelengths of and systemic causes (hypoxia, hypotension, and pyrexia) light (e. g. Edslab Sat II, Baxter-Edwards Critical Care were the main reasons for this desaturation. A poor Division). Such catheters need to be calibrated against neurological outcome was more likely with an increase a sample of the patient’s own blood, whereas catheters in frequency of desaturation episodes with mortality rates using three wavelengths (Opticath Oximetrix, Abbott of 21% in the group with no evidence of desaturation, Critical Care System) have in-built calibration, thus compared with 37% in patients with one episode and allowing continuous monitoring. 69% in patients with multiple episodes. Jugular venous Under physiological conditions, cerebral metabolic desaturation was identified in a majority of patients rate of oxygen (CMRO2) and CBF are coupled and the undergoing emergency evacuation of a traumatic intracra- ratio of these two parameters remains constant. The nial haematoma, and there was also an increase in SjvO2 difference between the oxyhaemoglobin saturation of values following evacuation [5]. cerebral arterial and mixed venous (i. e. internal jugular) Hyperventilation therapy for reduction of ICP in pa- blood represents the oxygen extraction. Thus a low SjvO2 tients with acute intracranial hypertension can be associ- (i. e. a high oxygen extraction ratio) may indicate low ated with significant reduction in CBF. Assuming a con- CBF in relation to CMRO2. Whilst the normal SjvO2 is stant brain metabolism, this will lead to reduction in global 60–70%, changes in trends of measured SjvO2 can reveal brain oxygenation. SjvO2 monitoring is therefore useful in useful information about adequacy of cerebral blood flow, optimising the use of hyperventilation. However, there is as SjvO2 is proportional to CBF/CMRO2.Avarietyof increasing evidence that hyperventilation therapy may still physiological and pathological conditions can alter the cause regions of reduced cerebral perfusion and potential relationship between brain oxygen demand (as indicated ischaemia even when SjvO2 is within normal limits [6].
Table 1 Factors affecting jugular venous oxygen saturation (SjvO2)
Decrease in SjvO2 Increase in SjvO2 Lowered O2 delivery Raised O2 consumption Raised O2 delivery Lowered O2 consumption Raised ICP, lowered CPP Increased metabolism Lowered ICP, raised CPP Coma Excessive hypocapnia Hyperthermia Hypercapnia Hypothermia Vasospasm Pain Drug induced vasodilation Sedative drugs Hypotension Light plane of anaesthesia Arterial hypertension Cerebral infarction Hypoxia Seizures Arteriovenous malformation Brain death Cardio-respiratory insufficiency Raised PaO2 Anaemia Haemorrhage Hb abnormalities Sepsis Neuromonitoring in the intensive care unit. Part II. Cerebral oxygenation monitoring and microdialysis 125
Close monitoring with SjvO2 and other methods of assess- measured from within areas of local pathology, suggesting ing tissue oxygenation may make detection of these hypo- that differences in regional cerebral oxygenation may not perfused regions easier. be detected by measurement of SjvO2 [11]. Inaccuracies in SjvO2 can occur for a number of rea- sons. For example, there may be no blood draining from Combination of SjvO2 with other modalities an infarcted area of the brain, therefore not affecting the SjvO2 value. Blood samples may be contaminated with Another application of SjvO2 is its use in conjunction with extracranial blood when the catheter is placed too proxi- TCD to distinguish between hyperaemia and vasospasm mally or blood is aspirated too rapidly, although this can following subarachnoid haemorrhage (SAH). If the TCD be avoided if blood is sampled at a site within 2 cm of detects a high flow velocity, hyperaemia is confirmed by the jugular bulb and at a rate of < 2 ml/min. There may a high SjvO2, whereas a low or normal SjvO2 is more be substantial discrepancy between the readings in sam- likely to indicate vasospasm. SjvO2 has also been used ples obtained from the two internal jugular veins. The con- as a complementary test for diagnosis of brain death. In tinuous fibre optic catheters may give inaccurate readings a study on 118 patients meeting criteria of brain death with if impacted against the vessel wall, if a thrombosis de- iso-electric electroencephalography (EEG), a ratio of < 1 velops on the catheter tip or if the sensor is curled within between central venous blood (SvO2) and SjvO2 was asso- the vessel. A few potential complications are associated ciated with 96% sensitivity and 99% specificity for brain with this technique (carotid artery puncture, thrombosis, death [7]. raised ICP), but these are rare. In conclusion, SjvO2 monitoring is a safe and valuable aid in evaluating status of cerebral oxygenation and Guiding therapy metabolism in patients with brain injury and also helps in our understanding of cerebral physiology. However, there The use of SjvO2 monitoring to guide hyperventilation are no randomised prospective trials that convincingly therapy is commonplace. One potential use of SjvO2 demonstrate a poor outcome in patients with low SjvO2 monitoring is with therapy for vasospasm following SAH. values. Limitations of SjvO2 monitoring should be kept in Fandino et al. used SjvO2 to monitor localised injection mind and values should be interpreted in conjunction with of the arterial vasodilator papaverine in a small series those from other cerebral monitoring devices. of patients and noted an immediate improvement [8]. However, the vasospastic area would need to be relatively large to affect global oxygenation markers. Near-infrared spectroscopy Barbiturate-induced cerebral metabolic suppression in patients with severe brain injury can be guided by Near-infrared spectroscopy (NIRS) is a non-invasive SjvO2 monitoring. Cruz et al. used SjvO2 to evaluate technique used for observing real-time changes in regional global cerebral oxygenation before and after intravenous cerebral oxygenation at the bedside. The physical princi- administration of pentobarbital for the management of ple of NIRS is based upon the ability of light waves of refractory intracranial hypertension in comatose patients near-infrared wavelength (i. e. 700–1,000 nm) to penetrate with traumatic brain swelling. Outcomes were signifi- scalp, skull and brain to a depth of a few centimetres. These cantly better in patients whose SjvO2 remained above light waves are differentially absorbed by oxygenated 45% than in those in whom it dropped to below this value, haemoglobin (HbO2), deoxygenated haemoglobin (Hb) despite the fact that there were no significant differences and cytochrome aa3 (CytOx). Quantification of this optical between the two groups with regard to ICP and cerebral attenuation is achieved by using reflectance spectroscopy perfusion pressure (CPP) [9]. based upon the modified Beer–Lambert law. Measure- Continuous SjvO2 monitoring, however, has some ments are obtained by optodes placed 4–6 cm apart on the limitations. Sheinberg et al. demonstrated that up to half forehead, thereby estimating oxygen content of all vascu- of measured desaturations below 50% might be false lar compartments (arterial, capillary and venous) within positives [10]. Furthermore, continuous monitoring has a “banana”-shaped region of the brain. The measurements limited ability to detect discrete regions of ischaemia or reflect relative concentrations of HbO2, Hb and CytOx. hyperaemia unless they are significantly large enough NIRS has been used to monitor patients with TBI, to influence the ‘global’ picture. A study that compared intracranial haemorrhage and in patients undergoing changes in SjvO2 with brain tissue oxygen partial pressure carotid endarterectomy. In one study in patients on the (PbO2) in response to hyperventilation in patients with intensive care unit following head injury, NIRS detected severe brain injury found a good correlation between the 97% of desaturations while jugular venous oximetry two modalities when PbO2 was measured outside of areas detected only 53%, and NIRS was more specific and more of focal pathology. However, changes in SjvO2 could not sensitive [12]. NIRS has also been used to detect cerebral be correlated to changes in PbO2 when the latter was hypoxia during carotid endarterectomy, with more than 126 A. Bhatia and A.K. Gupta
50% of patients developing cerebral desaturation on protocols. The technique involves insertion of a microsen- internal carotid artery cross-clamping [13]. NIRS can sor into brain parenchyma either through a bolt inserted be easily combined with other bedside methods such as into the skull or directly through a craniotomy site and transcranial Doppler (TCD), and simultaneous use of tunnelled under the skin. Two commercially available both these modalities provides useful information about microsensors allow direct, continuous measurement of haemodynamic and metabolic cerebral adaptive status in brain tissue gases. One of these sensors measures brain patients with carotid artery occlusive disease [14]. tissue oxygen tension using a polarographic Clarke-type Recent developments in NIRS technology have re- electrode, whilst the other measures PbO2,PbCO2 and sulted in availability of single, easy-to-use numerators pH using fibre-optic technology. Both of these sensors are for measuring cerebral tissue oxygenation – the NIRO approximately 0.5 mm in diameter and have the ability to 300 (Hamamatsu Phototonics, Japan) measures tissue measure brain temperature using a thermocouple. oxygenation index (TOI-the ratio of oxygenated to total Whilst early animal studies demonstrated that these tissue haemoglobin) and the INVOS 5100 (Somanetics, sensors respond to physiological responses in a predictable USA) provides regional cerebral oxygen saturation. manner [20, 21], the majority of clinical experience with Al-Rawi et al. found that in patients undergoing carotid these sensors has been in patients following severe TBI endarterectomy, NIRS reflects changes in cerebral tissue and patients undergoing cerebrovascular surgery. Data oxygenation with high sensitivity and specificity when from these patients have enabled a broad identification of TOI is calculated [15]. Dunham et al. found a correlation baseline values. PbO2 is normally lower than arterial PaO2 between NIRS and cerebral perfusion in a pilot study due to the extravascular placement of probes and high on patients with severe head injury. Cerebral tissue sat- metabolic activity of the brain (range 15–50 mmHg) [20]. uration of ≥ 75% was associated with CPP ≥ 70 mmHg, PbCO2 is normally higher than PaCO2 but these are whereas saturation of < 55% was associated with CPP directly related, reflecting the high diffusibility of CO2 < 70 mmHg most of the time. The authors also found (range 40–70 mmHg). pH is normally lower in brain tissue, that desaturation occurred in some patients despite CPP also reflecting high brain metabolism (range 7.05–7.25). being ≥ 70 mmHg [16]. TOI, as determined by NIRS, was Attempts have also been made to identify thresholds of is- compared with tissue microprobes and SjvO2 for meas- chaemia, with different authors using different approaches. uring cerebral oxygenation during normobaric hyperoxia Although this threshold is as yet not clearly defined with in patients with severe brain injury. Tissue microprobes relation to outcome, there are some reports indicating that exhibited a time lag in reaching steady state following PbO2 values less than 8–10 mmHg represent a high risk induction of hyperoxia, whereas TOI and SjvO2 responded of ischaemia [22, 23]. Data are beginning to emerge on promptly to each change of inspired oxygen concentra- the utility of other parameters, with evidence of increased tion [17]. A potential use of NIRS is in detection of risk of vasospasm if tissue pH is less than 7.0 and PbCO2 intracranial haematomas. Gopinath et al. suggested use of greater than 60 mmHg in patients with cerebrovascular NIRS to detect delayed traumatic intracranial haematomas disease [24] and an increased risk of mortality in head in patients who have a subdural haematoma or massive injury if brain tissue pH level falls below 7 [25]. amount of blood in the subarachnoid space, thus leading Validation of brain tissue oxygenation sensors requires to better-timed follow-up CT scans and operations [18]. comparison both with existing techniques, such as jugular There are some limitations of NIRS in its present form. bulb oximetry, and with a ‘gold standard’. Changes in Increase in path length of near-infrared light in pathologic PbO2 have correlated well with changes in SjvO2, particu- conditions, such as brain swelling following head injury larly when the sensor was inserted into non-contusional can affect the accuracy and reliability of NIRS. Further- areas of brain [26], indicating that tissue sensors do reflect more, although the algorithms that are employed in the changes in cerebral oxygenation. A study comparing system have improved, there is still lack of evidence that changes in PbO2 with values of end-capillary oxygen NIRS can reliably distinguish between intra- and extracra- tension derived from positron emission tomography (PET) nial changes in blood flow and oxygenation. Development found that changes in these values correlated well in of NIRS technology continues to improve the accuracy of response to a challenge of hyperventilation, confirming the equipment, and validation by prospective trials could that brain tissue sensors can be used as a reliable clinical qualify it as a reliable continuous non-invasive monitor of tool [27]. This study began to explore the hypothesis brain oxygenation in coming years [19]. that variable diffusion gradients existed between the end capillary and the extracellular compartment of the injured brain, which was confirmed in a follow-up study in which Brain tissue oxygenation monitoring the investigators performed end-capillary and extracellular measurements of oxygen tension in normoxic and hypoxic Measurement of PbO2 is increasingly being used as areas of tissue in response to hyperventilation (Fig. 1) and a monitoring modality in the neurosciences critical care examination of some of the tissue specimens revealed unit and as a marker of cerebral oxygenation in research perivascular oedema and endothelial swelling [28]. Neuromonitoring in the intensive care unit. Part II. Cerebral oxygenation monitoring and microdialysis 127
lished by a group of experts in clinical microdialysis, it was suggested that catheters should be placed in the tissue at risk in SAH patients (most likely the parent vessel ter- ritory), in the right frontal region in patients with diffuse injury after TBI, and in patients with focal mass lesions one catheter should be placed in the penumbra (pericontu- sional tissue) and a second placed in uninjured or ‘normal’ tissue [33]. The substances that could potentially be measured are innumerable, but the key substances can be categorised as follows [34]:
1. Energy-related metabolites, e. g. glucose, lactate, pyru- Fig. 1 Comparison of tissue and end-capillary pO2 (PtO2), cerebral vate, adenosine, xanthine. The lactate/pyruvate ratio is venous pO2 (PvO2) and diffusion gradient for oxygen (PvO2–PtO2) a better marker of ischaemia than lactate alone [35]. in normoxic (open bars;PtO2 >10 torr) and hypoxic (filled bars; γ ≤ 2. Neurotransmitters, e. g. glutamate, aspartate, -amino- PtO2 10 torr) ROIs. Note that the PvO2 is similar for the two butyric acid (GABA). groups, and the low tissue pO2 values are substantially due to dif- ferences in oxygen gradient between the microvasculature and the 3. Markers of tissue damage and inflammation,e.g.glyc- extracellular space (*p < 0.001) [27] erol, potassium, cytokines. 4. Exogenous substances, e. g. administered drugs.
As data continue to accrue from a number of centres Cerebral microdialysis has been applied to patients in using tissue oxygen sensors, this tool is now approaching many different clinical situations, including TBI, SAH, the threshold where it will change from being an interest- epilepsy, ischaemic stroke, tumours and during neuro- ing research adjunct to a useful clinical monitor. surgery [36]. In patients with severe brain injury derange- ments in metabolism have been associated with reductions in brain glucose and elevation of the lactate/pyruvate ratio Microdialysis during periods of intracranial hypertension and cerebral ischaemia. A high lactate/pyruvate ratio has been found The technique of cerebral microdialysis allows con- to correlate with the severity of clinical symptoms and tinuous on-line monitoring of changes in brain tissue fatal outcome after severe head injury. Wide variations in chemistry, achieved by inserting a catheter (diameter the concentration of the excitatory amino acids glutamate 0.62 mm) lined with polyamide dialysis membrane into and aspartate have also been detected, with extremely brain parenchyma, which is perfused with a physiological high levels in secondary ischaemia and contusions. solution (e. g. Ringer’s lactate) at ultra-low flow rates A rise in glycerol levels has been found in microdialysis (0.1–2.0 µl/min) using a precision pump. Molecules samples after severe head injury, possibly indicating that below the cut-off size of the semipermeable membrane tissue ischemia has progressed to cell damage. During (approximately 20,000 Da) diffuse from the extracellular aneurysm surgery, changes in concentration of glucose, space into the perfusion fluid, which is then collected into lactate, pyruvate and glutamate have been demonstrated vials that are changed every 10–60 min, allowing up to during cerebro-spinal fluid drainage, brain retraction and 70% equilibration across the dialysis membrane [29]. temporary clipping. Epileptic foci in the temporal lobe are Microdialysis catheter insertion does cause some dis- associated with elevated glutamate and reduced GABA ruption of local tissues and may cause small haemorrhages levels prior to seizures, and both amino acids are found to into the catheter tract, mild astrogliosis and macrophage increase during seizures. infiltration [30]. The catheter can be located in areas of un- Cerebral microdialysis has great potential for exploring injured brain or in tissue regarded as being “at risk” such as the pathophysiology of acute brain injury, pharmacokinet- in areas of vasospasm [31] or in the penumbral area around ics of drugs within the central nervous system and the re- a mass lesion [32]. In a recent consensus statement pub- sponse to therapeutic interventions. 128 A. Bhatia and A.K. Gupta
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Abstract Objective: In mechanical- preload assessment can be obtained ly ventilated patients the indices with fair accuracy, the clinical utility which assess preload are used with of volume responsiveness-guided increasing frequency to predict the fluid therapy still needs to be dem- hemodynamic response to volume onstrated. Indeed, it is still not clear expansion. We discuss the clinical whether any form of monitoring- utility and accuracy of some indices guided fluid therapy improves sur- which were tested as bedside indica- vival. tors of preload reserve and fluid re- sponsiveness in hypotensive patients Keywords Positive pressure under positive pressure ventilation. ventilation · Hypotension · Volume Results and conclusions: Although expansion · Cardiac index
Prediction is very difficult, especially about the future. diac output will increase or not with VE have been Niels Bohr sought after for many years. Presently, as few methods are able to assess ventricular volumes continuously and directly, static pressure measurements and echocardio- Introduction graphically measured ventricular end-diastolic areas are used as tools to monitor cardiovascular filling. Replacing Hypotension is one of the most frequent clinical signs static measurements, dynamic monitoring consisting in observed in critically ill patients. To restore normal assessment of fluid responsiveness using changes in sys- blood pressure, the cardiovascular filling (preload- tolic arterial pressure, and pulse pressure induced by defined as end-diastolic volume of both ventricular positive pressure ventilation have been proposed. The chambers), cardiac function (inotropism), and vascular present review analyses the current roles and limitations resistance (afterload) must be assessed. Hemodynamic of the most frequently used methods in clinical practice instability secondary to effective or relative intravascular to predict fluid responsiveness in patients undergoing volume depletion are very common, and intravascular mechanical ventilation (MV) (Table 1). fluid resuscitation or volume expansion (VE) allows res- One method routinely used to evaluate intravascular toration of ventricular filling, cardiac output and ulti- volume in hypotensive patients uses hemodynamic re- mately arterial blood pressure [1, 2]. However, in the sponse to a fluid challenge [3]. This method consists in Frank-Starling curve (stroke volume as a function of pre- infusing a defined amount of fluid over a brief period of load) the slope presents on its early phase a steep portion time. The response to the intravascular volume loading which is followed by a plateau (Fig. 1). As a conse- can be monitored clinically by heart rate, blood pressure, quence, when the plateau is reached, vigorous fluid re- pulse pressure (systolic minus diastolic blood pressure), suscitation carries out the risk of generating volume and urine output or by invasive monitoring with the mea- overload and pulmonary edema and/or right-ventricular surements of the right atrial pressure (RAP), pulmonary dysfunction. Thus in hypotensive patients methods able artery occlusion pressure (Ppao), and cardiac output. to unmask decreased preload and to predict whether car- Such a fluid management protocol assumes that the in-
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 133 DOI: 10.1007/978-3-642-01769-8_29, © Springer-Verlag Berlin Heidelberg 2009 353 134 K. Bendjelid and J.-A. Romand
travascular volume of the critically ill patients can be de- fined by the relationship between preload and cardiac output, and that changing preload with volume infusion affects cardiac output. Thus an increase in cardiac output following VE (patient responder) unmasks an hypovo- lemic state or preload dependency. On the other hand, lack of change or a decrease in cardiac output following VE (nonresponding patient) is attributed to a normovo- lemic, to an overloaded, or to cardiac failure state. Therefore, as the fluid responsiveness defines the re- sponse of cardiac output to volume challenge, indices which can predict the latter are necessary.
Static measurements for preload assessment Fig. 1 Representation of Frank-Starling curve with relationship be- tween ventricular preload and ventricular stroke volume in patient Measures of intracardiac pressures X. After volume expansion the same magnitude of change in pre- load recruit less stroke volume, because the plateau of the curve is According to the Frank-Starling law, left-ventricular pre- reached which characterize a condition of preload independency load is defined as the myocardial fiber length at the end
Table 1 Studies of indices used as bedside indicators of preload HES hydroxyethyl starch, RL Ringer’s lactate, Alb albumin, reserve and fluid responsiveness in hypotensive patients under ∆down delta down, ∆PP respiratory variation in pulse pressure, positive-pressure ventilation (BMI body mass index, CO cardiac LVEDV left-ventricular end diastolic volume, SPV systolic pres- output, CI cardiac index, SV stroke volume, SVI stroke volume in- sure variation, SVV stroke volume variation, TEE transesophageal dex, IAC invasive arterial catheter, MV proportion of patients me- echocardiography, Ppao pulmonary artery occlusion pressure, chanically ventilated, ↑ increase, ↓ decrease, PAC pulmonary ar- RAP right atrial pressure, RVEDV right-ventricular-end diastolic tery catheter, R responders, NR nonresponders, FC fluid challenge, volume, FC fluid challenge)
Variable Tech- n MV Volume (ml) Duration Definition Definition p: Refer- measured nique (%) and type of of FC of R of NR difference ence plasma substitute (min) in baseline values R vs. NR
Rap PAC 28 46 250 Alb 5% 20–30 ↑ SVI ↓ SVI or unchanged NS 37 Rap PAC 41 76 300 Alb 4.5% 30 ↑ CI CI ↓ or unchanged NS 18 Rap PAC 25 94.4 NaCl 9‰ + Until ↑Ppao ↑ SV ≥10% ↑ SV <10% 0.04 31 Alb 5% to ↑ Ppao Rap PAC 40 100 500 HES 6% 30 ↑ CI >15% ↑ CI <15% NS 36 Ppao PAC 28 46 250 Alb 5% 20–30 ↑ SVI ↓ SVI or unchanged NS 37 Ppao PAC 41 76 300 Alb 4.5% 30 ↑ CI CI ↓ or unchanged NS 18 Ppao PAC 29 69 300–500 RL ? bolus ↑ C0>10% C0 ↓ or unchanged <0.01 40 Ppao PAC 32 84 300–500 RL ? ↑ CI >20% ↑ CI <20% NS 41 Ppao PAC 16 100 500 HES 6% 30 ↑ CI >15% ↑ CI <15% 0.1 42 Ppao PAC 41 100 500 pPentastarch 15 ↑ SV ≥20% ↑ SV <20% 0.003 25 Ppao PAC 25 94.4 NaCl 9‰, Until ↑Ppao ↑ SV ≥10% ↑ SV <10% 0.001 31 Alb 5% to↑ Ppao Ppao PAC 40 100 500 HES 6% 30 ↑ CI >15% ↑ CI <15% NS 36 Ppao PAC 19 100 500–750 HES 6% 10 ↑ C0>10% ↑ SV <10% 0.0085 39 RVEDV PAC 29 69 300–500 RL ? bolus ↑ C0>10% C0 ↓ or unchanged <0.001 40 RVEDV PAC 32 84 300–500 RL ? ↑ CI >20% ↑ CI <20% <0.002 41 RVEDV PAC 25 94.4 NaCl 9‰, Until ↑Ppao ↑ SV ≥10% ↑ SV <10% 0.22 31 Alb 5% to↑ Ppao LVEDV TEE 16 100 500 HES 6% 30 ↑ CI >15% ↑ CI <15% 0.005 42 LVEDV TEE 41 100 500 Pentastarch 15 ↑ SV ≥20% ↑ SV <20% 0.012 25 LVEDV TEE 19 100 8 ml/kg HES 6% 30 ↑ CI >15% ↑ CI <15% NS 79 LVEDV TEE 19 100 500–750 HES 6% 10 ↑ C0>10% ↑ SV <10% NS 39 SPV IAC 16 100 500 HES 6% 30 ↑ CI >15% ↑ CI <15% 0.0001 42 SPV IAC 40 100 500 HES 6% 30 ↑ CI >15% ↑ CI <15% <0.001 36 SPV IAC 19 100 500–750 HES 6% 10 ↑ C0>10% ↑ SV <10% 0.017 39 ∆down IAC 16 100 500 HES 6% 30 ↑ CI >15% ↑ CI <15% 0.0001 42 ∆down IAC 19 100 500–750 HES 6% 10 ↑ C0>10% ↑ SV <10% 0.025 39 ∆PP IAC 40 100 500 HES 6% 30 ↑ CI >15% ↑ CI <15% <0.001 36 354 Fluid responsiveness in mechanically ventilated patients 135 of the diastole. In clinical practice, the left-ventricular that Ppao using PAC is a reliable indirect measurement end-diastolic volume is used as a surrogate to define left- of left atrial pressure [29, 30] in positive-pressure MV ventricular preload [4]. However, this volumetric param- patients. eter is not easily assessed in critically ill patients. In nor- mal conditions, a fairly good correlation exists between ventricular end-diastolic volumes and mean atrial pres- Right atrial pressure used to predict fluid responsiveness sures, and ventricular preloads are approximated by RAP and/or Ppao in patients breathing spontaneously [5, 6]. Wagner et al. [31] reported that RAP was significantly Critically ill patients often require positive pressure ven- lower before volume challenge in responders than in tilation, which modifies the pressure regimen in the tho- nonresponders (p=0.04) when patients were under posi- rax in comparison to spontaneous breathing. Indeed, dur- tive pressure ventilation. Jellinek et al. [32] found that a ing MV RAP and Ppao rise secondary to an increase in RAP lower than 10 mmHg predicts a decrease in cardiac intrathoracic pressure which rises pericardial pressure. index higher than 20% when a transient 30 cm H2O in- This pressure increase induces a decrease in venous re- crease in intrathoracic pressure is administrated. Presum- turn [7, 8] with first a decrease in right and few heart ing that the principle cause of decrease in cardiac output beats later in left-ventricular end-diastolic volumes, re- in the latter study was due to a reduction in venous re- spectively [9, 10]. Under extreme conditions such as turn [9, 33, 34, 35], RAP predicts reverse VE hemody- acute severe pulmonary emboli and/or marked hyperin- namic effect. Nevertheless, some clinical investigations flation, RAP may also rise secondary to an increase af- studying fluid responsiveness in MV patients have re- terload of the right ventricle. Moreover, under positive ported that RAP poorly predicts increased cardiac output pressure ventilation not only ventricular but also tho- after volume expansion [18, 36, 37]. Indeed, in these racopulmonary compliances and abdominal pressure studies RAP did not differentiate patients whose cardiac variations are observed over time. Thus a variable rela- output did or did not increase after VE (responders and tionship between cardiac pressures and cardiac volumes nonresponders, respectively). is often observed [11, 12, 13, 14]. It has also been dem- onstrated that changes in intracardiac pressure (RAP, Ppao) no longer directly reflect changes in intravascular Ppao used to predict fluid responsiveness volume [15]. Pinsky et al. [16, 17] have demonstrated that changes in RAP do not follow changes in right-ven- Some studies have demonstrated that Ppao is a good pre- tricular end-diastolic volume in postoperative cardiac dictor of fluid responsiveness [13, 31, 38]. Recently surgery patients under positive pressure ventilation. Bennett-Guerrero et al. [39] also found that Ppao was a Reuse et al. [18] observed no correlation between RAP better predictor of response to VE than systolic pressure and right-ventricular end-diastolic volume calculated variation (SPV) and left-ventricular end-diastolic area from a thermodilution technique in hypovolemic patients measured by TEE. However, several other studies noted before and after fluid resuscitation. The discordance be- that Ppao is unable to predict fluid responsiveness and to tween RAP and right-ventricular end-diastolic volume differentiate between VE-responders and VE-nonre- measurements may result from a systematic underesti- sponders [18, 25, 36, 37, 40, 41, 42]. The discrepancy mation of the effect of positive-pressure ventilation on between the results of these studies may partly reflect the right heart [16, 17]. Nevertheless, the RAP value differences in patients’ baseline characteristics (e.g., de- measured either with a central venous catheter or a pul- mographic differences, medical history, chest and lung monary artery catheter is still used to estimate preload compliances) at study entry. Furthermore, differences in and to guide intravascular volume therapy in patient location of the pulmonary artery catheter extremity rela- under positive pressure ventilation [19, 20]. tive to the left atrium may be present [43]. Indeed, ac- On the left side, the MV-induced intrathoracic pres- cording to its position, pulmonary artery catheter may sure changes, compared to spontaneously breathing, on- display alveolar pressure instead of left atrial pressure ly minimally alters the relationship between left atrial (West zone I or II) [44]. The value of Ppao is also influ- pressure and left-ventricular end-diastolic volume mea- enced by juxtacardiac pressure [45, 46] particularly if surement in postoperative cardiac surgery patients [21]. positive end-expiratory pressure (PEEP) is used [28]. However, several other studies show no relationship be- To overcome the latter difficulty in MV patients when tween Ppao and left-ventricular end-diastolic volume PEEP is used, nadir Ppao (Ppao measured after airway measured by either radionuclide angiography [12, 22], disconnection) may be used [46]. However, as nadir transthoracic echocardiography (TTE) [23], or trans- Ppao requires temporary disconnection from the ventila- esophageal echocardiography (TEE) [24, 25, 26]. The tor, it might be deleterious to severely hypoxemic pa- latter findings may be related to the indirect pulmonary tients. No study has yet evaluated the predictive value artery catheter method for assessing left atrial pressure of nadir Ppao for estimating fluid responsiveness in MV [27, 28], although several studies have demonstrated patients. 355 136 K. Bendjelid and J.-A. Romand
In brief, although static intracardiac pressure mea- high intra-abdominal pressure or when clinicians are re- surements such as RAP and Ppao have been studied and luctant to obtain off-PEEP nadir Ppao measurements [65]. used for many years for hemodynamic monitoring, their low predictive value in estimating fluid responsiveness in MV patients must be underlined. Thus using only in- Right-ventricular end-diastolic volume measured travascular static pressures to guide fluid therapy can by echocardiography used to predict fluid responsiveness lead to inappropriate therapeutic decisions [47]. TTE has been shown to be a reliable method to assess right-ventricular dimensions in patients ventilated with Measures of ventricular end-diastolic volumes continuous positive airway pressure or positive-pressure ventilation [66, 67]. Using this approach, right-ventricu- Radionuclide angiography [48], cineangiocardiography lar end-diastolic area is obtained on the apical four [49], and thermodilution [50] have been used to estimate chambers view [68]. When no right-ventricular window ventricular volumes for one-half a century. In intensive care is available, TEE is preferred to monitor right-ventricu- units, various methods have been used to measure ventricu- lar end-volume in MV patients [53, 55, 69, 70, 71]. The lar end-diastolic volume at the bedside, such as radionu- latter method has become more popular in recent years clide angiography [51, 52], TTE [23, 53, 54], TEE [55], due to technical improvements [72]. Nevertheless, no and a modified flow-directed pulmonary artery catheter study has evaluated right-ventricular size measurements which allows the measurement of cardiac output and right- by TTE or TEE as a predictor of fluid responsiveness in ventricular ejection fraction (and the calculation of right- MV patients. ventricular end-systolic and end-diastolic volume) [31, 41].
Left-ventricular end-diastolic volume measured Right-ventricular end-diastolic volume by echocardiography used to predict fluid responsiveness measured by pulmonary artery catheter used to predict fluid responsiveness TTE has been used in the past to measure left-ventricular end-diastolic volume and/or area [23, 67, 73, 74] in MV During MV right-ventricular end-diastolic volume mea- patients. However, no study has evaluated the left-ven- sured with a pulmonary artery catheter is decreased by tricular end-diastolic volume and/or area measured by PEEP [56] but is still well correlated with cardiac index TTE as predictors of fluid responsiveness in MV pa- [57, 58] and is a more reliable predictor of fluid respon- tients. Due to its greater resolving power, TEE easily and siveness than Ppao [40, 41]. On the other hand, other accurately assesses left-ventricular end-diastolic volume studies have found no relationship between change in and/or area in clinical practice [53, 75] except in patients right-ventricular end-diastolic volume measured by pul- undergoing coronary artery bypass grafting [76]. Howev- monary artery catheter and change in stroke volume in er, different studies have reported conflicting results two series of cardiac surgery patients [16, 18]. Similarly, about the usefulness of left-ventricular end-diastolic vol- Wagner et al. [31] found that right-ventricular end-diastol- ume and/or area measured by TEE to predict fluid re- ic volume measured by pulmonary artery catheter was not sponsiveness in MV patients. Cheung et al. [26] have a reliable predictor of fluid responsiveness in patients un- shown that left-ventricular end-diastolic area measured der MV, and that Ppao and RAP were superior to right- by TEE is an accurate method to predict the hemody- ventricular end-diastolic volume. The discrepancy be- namic effects of acute blood loss. Other studies have re- tween the results of these studies may partly reflect the ported either a modest [25, 42, 77] or a poor [78, 79] measurement errors of cardiac output due to the cyclic predictive value of left-ventricular end-diastolic volume change induced by positive pressure ventilation [59, 60, and area to predict the cardiac output response to fluid 61, 62], the inaccuracy of cardiac output measurement ob- loading. Recent studies have also produced conflicting tained by pulmonary artery catheter when the flux is low results. Bennett-Guerrero et al. [39] measuring left-ven- [63], and the influence of tricuspid regurgitation on the tricular end-diastolic area with TEE before VE found no measurement of cardiac output [64]. Moreover, as right- significant difference between responders and nonre- ventricular end-diastolic volume is calculated (stroke vol- sponders. Paradoxically, Reuter et al. [80] found that ume divided by right ejection fraction), cardiac output be- left-ventricular end-diastolic area index assessed by TEE comes a shared variable in the calculation of both stroke before VE predicts fluid responsiveness more accurately volume and right-ventricular end-diastolic volume, and a than RAP, Ppao, and stroke volume variation (SVV). In mathematical coupling may have contributed to the close the future three-dimensional echocardiography could correlation observed between these two variables. Never- supplant other methods for measuring left-ventricular theless, right-ventricular end-diastolic volume compared end-diastolic volume and their predictive value of fluid to Ppao may be useful in a small group of patients with responsiveness. In a word, although measurements of 356 Fluid responsiveness in mechanically ventilated patients 137 ventricular volumes should theoretically reflect preload dependence more accurately than other indices, conflict- ing results have been reported so far. These negative findings may be related to the method used to estimate end-diastolic ventricular volumes which do not reflect the geometric complexity of the right ventricle and to the influences of the positive intrathoracic pressure on left- ventricular preload, afterload and myocardial contractili- ty [81].
Dynamic measurements for preload assessment Fig. 2 Systolic pressure variation (SPV) after one mechanical Measure of respiratory changes in systolic pressure, breath followed by an end-expiratory pause. Reference line per- pulse pressure, and stroke volume mits the measurement of ∆up and ∆down. Bold Maximal and min- imal pulse pressure. AP Airway pressure; SAP systolic arterial Positive pressure breath decreases temporary right-ven- pressure tricular end-diastolic volume secondary to a reduction in venous return [7, 82]. A decrease in right-ventricular stroke volume ensues which become minimal at end pos- chanical breath. Using the systolic pressure at end expi- itive pressure breath. This inspiratory reduction in right- ration as a reference point or baseline the SPV was fur- ventricular stroke volume induces a decrease in left-ven- ther divided into two components: an increase (∆up) and tricular end-diastolic volume after a phase lag of few a decrease (∆down) in systolic pressure vs. baseline heart beats (due to the pulmonary vascular transit time (Fig. 2). These authors concluded that in hypovolemic [83]), which becomes evident during the expiratory patients ∆down was the main component of SPV. These phase. This expiratory reduction in left-ventricular end- preliminary conclusions were confirmed in 1987 by diastolic volume induces a decrease in left-ventricular Perel et al. [90] who demonstrated that SPV following a stroke volume, determining the minimal value of systolic positive pressure breath is a sensitive indicator of hypo- blood pressure observed during expiration. Conversely, volemia in ventilated dogs. Thereafter Coriat et al. [91] the inspiratory increase in left-ventricular end-diastolic demonstrated that SPV and ∆down predict the response volume determining the maximal value of systolic blood of cardiac index to VE in a group of sedated MV patients pressure is observed secondary to the rise in left-ventric- after vascular surgery. Exploring another pathophysio- ular preload reflecting the few heart beats earlier in- logical concept, Jardin et al. [92] found that pulse pres- creased in right-ventricular preload during expiration. sure (PP; defined as the difference between the systolic Furthermore, increasing lung volume during positive and the diastolic pressure) is related to left-ventricular pressure ventilation may also contribute to the increased stroke volume in MV patients. Using these findings, pulmonary venous blood flow (related to the compres- Michard et al. [35, 36,] have shown that respiratory sion of pulmonary blood vessels [84]) and/or to a de- changes in PP [∆PP=maximal PP at inspiration (PPmax) crease in left-ventricular afterload [85, 86, 87], which minus minimal PP at expiration (PPmin); (Fig. 2) and together induce an increase in left-ventricular preload. calculated as: ∆PP (%)=100 (PPmax-PPmin)/(Ppmax+ Finally, a decrease in right-ventricular end-diastolic vol- PPmin)/2] predict the effect of VE on cardiac index in ume during a positive pressure breath may increase left- patients with acute lung injury [35] or septic shock [36]. ventricular compliance and then left-ventricular preload The same team proposed another approach to assess [88]. Thus due to heart-lung interaction during positive SVV in MV patients and to predict cardiac responsive- pressure ventilation the left-ventricular stroke volume ness to VE [79]. Using Doppler measurement of beat- varies cyclically (maximal during inspiration and mini- to-beat aortic blood flow, they found that respiratory mal during expiration). change in aortic blood flow maximal velocity predicts These variations have been used clinically to assess fluid responsiveness in septic MV patients. Measuring preload status and predict fluid responsiveness in deeply SVV during positive pressure ventilation by continuous sedated patients under positive pressure ventilation. In arterial pulse contour analysis, Reuter et al. [80] have re- 1983 Coyle et al. [89] in a preliminary study demonstrat- cently demonstrated that SVV accurately predicts fluid ed that the SPV following one mechanical breath is in- responsiveness following volume infusion in ventilated creased in hypovolemic sedated patients and decreased patients after cardiac surgery. after fluid resuscitation. This study defined SPV as the difference between maximal and minimal values of sys- tolic blood pressure during one positive pressure me- 357 138 K. Bendjelid and J.-A. Romand
Systolic pressure variation used to predict by valve opening area during expiration. However, this fluid responsiveness finding may be biased, as expiratory flow velocity time integral is a shared variable in the calculation of both The evaluation of fluid responsiveness by SPV is based cardiac output and expiratory maximal aortic blood flow on cardiopulmonary interaction during MV [93, 94]. In velocity and a mathematical coupling may contribute to 1995 Rooke et al. [95] found that SPV is a useful moni- the observed correlation between changes in cardiac out- tor of volume status in healthy MV patients during anes- put and variation in maximal aortic blood flow velocity. thesia. Coriat et al. [91] confirmed the usefulness of SPV Finally, Reuter et al. [80] used continuous arterial pulse for estimating response to VE in MV patients after vas- contour analysis and found that SVV during positive cular surgery. Ornstein et al. [96] have also shown that pressure breath accurately predicts fluid responsiveness SPV and ∆down are correlated with decreased cardiac following VE in ventilated cardiac surgery patients [80]. output after controlled hemorrhage in postoperative car- Using the receiver operating characteristics curve, these diac surgical patients. Furthermore, Tavernier et al. [42] authors demonstrated that the area under the curve is sta- found ∆down before VE to be an accurate index of the tistically greater for SVV (0.82; confidence interval: fluid responsiveness in septic patients, and that a ∆down 0.64–1) and SPV (0.81; confidence interval: 0.62–1) value of 5 mmHg is the cutoff point for distinguishing than for RAP (0.45; confidence interval: 0.17–0.74) responders from nonresponders to VE. Finally, in septic (p<0.001) [97]. Concisely, dynamic indices have been patients Michard et al. [36] found that SPV is correlated explored to evaluate fluid responsiveness in critically ill with volume expansion-induced change in cardiac out- patients. All of them have been validated in deeply se- put. However, Denault et al. [81] have demonstrated that dated patients under positive-pressure MV. Thus such in- SPV is not correlated with changes in left-ventricular dices are useless in spontaneously breathing intubated end-diastolic volume measured by TEE in cardiac sur- patients, a MV mode often used in ICU. Moreover, regu- gery patients. Indeed, in this study, SPV was observed lar cardiac rhythm is an obligatory condition to allow despite no variation in left-ventricular stroke volume, their use. suggesting that SPV involves processes independent of changes in the left-ventricular preload (airway pressure, pleural pressure, and its resultant afterload) [81]. Conclusion
Positive pressure ventilation cyclically increases intra- Pulse pressure variation used to predict thoracic pressure and lung volume, both of which de- fluid responsiveness crease venous return and alter stroke volume. Thus VE which rapidly restore cardiac output and arterial blood Extending the concept elaborated by Jardin et al. [92], pressure is an often used therapy in hypotensive MV pa- Michard et al. [36] found that ∆PP predicted the effect of tients and indices which would predict fluid responsive- VE on cardiac output in 40 septic shock hypotensive pa- ness are necessary. RAP, Ppao, and right-ventricular end- tients. These authors demonstrated that both ∆PP and diastolic volume, which are static measurements, have SPV, when greater than 15%, are superior to RAP and been studied but produced conflicting data in estimating Ppao, for predicting fluid responsiveness. Moreover, preload and fluid responsiveness. On the other hand, ∆PP was more accurate and with less bias than SPV. SPV and ∆PP, which are dynamic measurements, have These authors proposed ∆PP as a surrogate for stroke been shown to identify hypotension related to decrease volume variation concept [93], which has not been vali- in preload, to distinguish between responders and nonre- dated yet. In another study these authors [35] included sponders to fluid challenge (Table 1), and to permit titra- VE in six MV patients with acute lung injury and found tion of VE in various patient populations. that ∆PP is a useful guide to predict fluid responsive- Although there is substantial literature on indices of ness. hypovolemia, only few studies have evaluated the cardi- ac output changes induced by VE in MV patients. More- over, therapeutic recommendations regarding unmasked Stroke volume variation to predict fluid responsiveness preload dependency states without hypotension need fur- ther studies. Finally, another unanswered question is re- Using Doppler TEE, Feissel et al. [79] studied changes lated to patients outcome: does therapy guided by fluid in left-ventricular stroke volume induced by the cyclic responsiveness indices improve patients survival? positive pressure breathing. By measuring the respiratory variation in maximal aortic blood flow velocity these au- Acknowledgements The authors thank Dr. M.R. Pinsky, Univer- thors predicted fluid responsiveness in septic MV pa- sity of Pittsburgh Medical Center, for his helpful advice in the preparation of this manuscript. The authors are also grateful for tients. Left-ventricular stroke volume was obtained by the translation support provided by Angela Frei. multiplying flow velocity time integral over aortic valve 358 Fluid responsiveness in mechanically ventilated patients 139
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Pinsky MR, Matuschak GM, Klain M 88:124–126 77. van Daele ME, Trouwborst A, van (1985) Determinants of cardiac aug- Woerkens LC, Tenbrinck R, Fraser mentation by elevations in intrathorac- AG, Roelandt JR (1994) Transesopha- ic pressure. J Appl Physiol geal echocardiographic monitoring 58:1189–1198 of preoperative acute hypervolemic 88. Taylor RR, Covell JW, Sonnenblick hemodilution. Anesthesiology EH, Ross J (1967) Dependence of ven- 81:602–609 tricular distensibility on filling of the opposite ventricle. Am J Physiol 213:711–718 Manu L. N. G. Malbrain Different techniques to measure intra-abdominal pressure (IAP): time for a critical re-appraisal
Abstract The diagnosis of intra-ab- debate. This review will focus on the dominal hypertension (IAH) or ab- previously described indirect IAP dominal compartment syndrome measurement techniques and will (ACS) is heavily dependant on the suggest new revised methods of IVP reproducibility of the intra-abdominal measurement less prone to error. pressure (IAP) measurement tech- Cost-effective manometry screening nique. Recent studies have shown techniques will be discussed, as well that a clinical estimation of IAP by as some options for the future with abdominal girth or by examiner’s feel microchip transducers. of the tenseness of the abdomen is far from accurate, with a sensitivity of Keywords Intra-abdominal around 40%. Consequently, the IAP pressure · Intra-abdominal needs to be measured with a more hypertension · Abdominal accurate, reproducible and reliable compartment syndrome · tool. The role of the intra-vesical Intra-vesical pressure pressure (IVP) as the gold standard for IAP has become a matter of
Introduction noncompliant bladder will raise intrinsic vesical pressure (IVP) and thus overestimate IAP [5, 6] (Fig. 1). By There is an exponential increase in studies on intra- constructing bladder pressure volume curves we found abdominal hypertension (IAH) and abdominal compart- that IVP was not raised when the volume instilled was ment syndrome (ACS) in the literature. There is still limited to 50–100 ml [7] (Fig. 2). This is in accordance controversy about the ideal method for measuring intra- with others who found that baseline IAP alters the amount abdominal pressure (IAP) [1, 2]. The intra-vesical route of volume in the bladder needed to increase IAP: the evolved as the gold standard. It, however, has consider- lower the baseline IAP, the higher the extra bladder able variability in the measurement technique, not only volume needed for the same IAP increase [6]. between individuals but also institutions. Common pitfalls The purpose of this report is: (1) to review the most are air bubbles in the system and wrong transducer commonly used indirect techniques for IAP measurement; positions. Variations in IAP from 6 to +30 mmHg have (2) to provide the reader with a full description and been reported previously [3]. A recent multicentre important (dis)advantages of each technique; (3) to snapshot study showed that the coefficient of variation describe some new or revised techniques; and (4) to was around 25%, even up to 66% in some centres, raising highlight the cost-effectiveness of each method. questions on the reproducibility of the measurement itself. This makes it, difficult to compare literature data [4]. The volumes reported in the literature for bladder priming before the IAP measurement are not uniform (ranging from 50 to 250 ml). Injecting over 50 ml in a
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 143 DOI: 10.1007/978-3-642-01769-8_30, © Springer-Verlag Berlin Heidelberg 2009 358 144 M.L.N.G. Malbrain
Fig. 2 Plot of the “insufflation” and “deflation” PV curve as a curve fit of the means of 13 measurements in six mechanically ventilated patients. The bladder PV curves were obtained by instilling sterile saline into the bladder with 25-ml increments. A lower inflection point can be seen at a bladder volume of 50– 100 ml and an upper inflection point (UIP) at a bladder volume of 250 ml. The difference in bladder pressure was 2.7€3.3 mmHg between 0 and 50 ml volume, 1.7€1.2 mmHg between 50 and 100 ml, 7.7€5.7 mmHg between 50 and 200 ml and 16.8€13.4 mmHg between 50 and 300 ml. See text for explanation
with sufficient time for adaptation, as seen with pregnan- cy, obesity, cirrhosis, or ovarian tumours, is an example of increased abdominal perimeter that is not necessarily accompanied by an increase in IAP. Other studies have shown that clinical IAP estimation by putting one or two Fig. 1 A Bladder PV curve in a patient with a compliant bladder. hands on the abdomen is also far from accurate, with a Note that pressures are higher during insufflation than during sensitivity of only around 40%. So, one needs to measure deflation. Note that regardless of the amount of saline instilled in it [10–12]. The question then arises: how? Since the the bladder the pressures are comparable: 10 mmHg at 50 ml, 11 mmHg at 100 ml and 12 mmHg at 200 ml. B Bladder PV curve abdomen and its contents can be considered as relatively in a septic patient with a poor bladder compliance. Note that non-compressive and primarily fluid in character, subject pressures are higher during insufflation than deflation. Note the to Pascal’s law, the IAP can be measured in nearly every significant difference in IAP value with regard to the amount of part of the abdomen. Different direct and indirect saline instilled in the bladder: 10 mmHg at 50 ml, 14 mmHg at 100 ml and 24 mmHg at 200 ml measurement methods have been reported. Table 1 lists the different techniques and their major advantages and disadvantages, with an overall score IAP assessment calculated by dividing twice the number of advantages by the total number of (dis)advantages reported. Table 2 lists In analogy with the paradigm “if you don’t take a the cost estimate in Euros for the different techniques, temperature you can’t find a fever” (in Samuel Shem, The with the cost of the initial set-up as well as the cost per house of god, Dell Publishing, ISBN: 0-440-13368-8), measurement. Cost estimations were based on the number one can state that “if you don’t measure IAP you cannot of measurements per day as well as the duration of the make a diagnosis of IAH or ACS”. Abdominal perimeter measurement period. cannot be used as an alternative method for IAP. In a recent study of 132 paired measurements in 12 ICU patients, we found a poor correlation between IAP and abdominal perimeter (R2=0.12, P=0.04) [8]. Clinically significant IAH may be present in the absence of abdominal distension [9]. Chronic abdominal distension 359 Different techniques to measure intra-abdominal pressure (IAP) 145
Table 1 Overview of the advantages (-) and disadvantages (+) of the different techniques for indirect IAP measurement. The overall score was calculated as the fraction of twice the number of advantages and the total number of (dis)advantages General information Bladder techniques Manometry Author Kron Iberti Cheatham Malbrain Harrahil Lee Malbrain Reference [13] [16, 17] [18] Current [26] [27] [28] Publication year 1984 1987, 1989 1998 2003 1998 2002 2002 Properties Fluid Fluid Fluid Fluid Fluid Fluid Fluid General — Volume 50 ml 250 ml 50 ml 50 ml ? ? 50 ml Manipulation +++ ++ + + - - - Difficult + - + - - - - Time consuming initial set-up +++ ++ + + - - - Time consuming next measurement +++ ++ - - - - - Cost of device initial set-up + + + + - - - Cost per measurement ++ ++ + + - - - Interference urine output + + + + - - - Glass syringe ------Technique No repeated measurements + + - - - - - No continuous trend + + + + + + + Not automated + + + + + + + Recalibration + + + + - - - Volume not standardised + + + + + + - Not accurate or reproducible + + + + + + + Not well validated -- - - + + + Air-bubbles + + + + + + + Multiple menisci -- - - + + + Bio-filter blocking ------+ MMC interference ------Hydrostatic fluid column Zero-reference problem + + + + - - - Over-under damping + + + + + + + Body position dependent ++ ++ ++ ++ ++ ++ ++ Risks Needle stick injury + + + - - - - Urinary infection + + + + - - - Sepsis ------Contra-indications Bladder trauma + + + + + + + Neurogenic bladder + + + + + + + Hematuria + + + + + + + Gastric trauma ------Other abdominal trauma ------Overall conclusion Disadvantages 30 26 21 19 13 13 13 Advantages 8 9 10 12 18 18 18 Overall score 34.8% 0.9% 48.8% 55.8% 73.5% 73.5% 73.5% Clinical indications None None Screening Intermittent None ? Quick monitoring screening
Bladder described by Kron and co-workers [13] and disrupts for each IAP measurement what is normally a closed sterile The original open system single measurement system. Thus, IAP measurement involves disconnecting technique [13] the patient’s Foley catheter and instilling 50–100 ml of saline using a sterile field. After reconnection, the urinary Description drainage bag is clamped distal to the culture aspiration port. For each individual IAP measurement a 16-gauche Traditionally the bladder has been used as the method of needle is then used to Y-connect a manometer or pressure choice for measuring IAP. The technique was originally 360 146 M.L.N.G. Malbrain
Table 1 (continued) General Information IVC Uterus Rectum Stomach Author Lacey Dowdle Shafik Collee Sugrue Malbrain Malbrain Reference [29] [31] [30] [20] [21, 22] Current Current Publication 1987 1997 1997 1993 1994, 2000 2003 2003 Properties Fluid Microchip Fluid-filled Fluid Air-filled Air-filled Air-filled balloon balloon balloon balloon General-Volume ? 50 ml 2 ml 1–2 ml 0.1 ml Manipulation ++ +++ +++ ++ + + - Difficult + ++ ++ + + + - Time taken for initial set-up ++ ++ ++ ++ ++ + + Time taken for next measurement - ++ ++ ++ + - - Cost of device initial set-up ++ ++++ ++ + +++ ++ ++ Cost per measurement -- - ++ - - - Interference urine output ------Glass syringe -- - - + + - Technique No Repeated measurements - + + + - - - No continuous trend - + + + - - - Not automated + + + + + + - Recalibration + + + + + + - Volume not standardised - + + + + + - Not accurate or reproducible + + + + - - - Not well validated +++ +++ ++ + + + + Air-bubbles + + + + - - - Multiple menisci ------Bio-filter blocking ------MMC interference -- - + + + - Hydrostatic fluid column Zero-reference problem + + + + - - - Over-under damping + + + + - - - Body position dependent + ++ ++ ++ - - - Risks Needle stick injury + ------Urinary infection ------Sepsis +++ ------Contra-indications Bladder trauma ------Neurogenic bladder ------Hematuria ------Gastric trauma -- - + + + + Other abdominal trauma - + + - - - - Overall conclusion Disadvantages 21 28 25 24 15 12 5 Advantages 16 13 13 11 18 19 26 Overall score 60.4% 48% 50.1% 47.8% 70.6% 76% 91.2% Clinical implications ? None ? Screening Research Research APP trend, Research transducer. The symphysis pubis is used as reference line. zero-reference at the symphysis pubis poses no problem, (See ESM addendum 1.) the problems come when the same pressure transducer is used for IAP and CVP, with zero-reference at the midaxillary line. Putting the patient upright with con- Advantages and disadvantage (Table 1) comitant rise in the transducer may lead to underestima- tion of IAP, while putting the patient in the Trendelenburg This technique implicates a lot of time-consuming position can lead to overestimation. The fact that manipulations that disrupt a closed sterile system at every recalibration needs to be done before every measurement measurement. It has all the problems that come along with augments the risk for errors. We have all seen the “magic” the hydrostatic convective fluid column. Even though drop or rise in CVP at changes of nurse shifts, the same 361 Different techniques to measure intra-abdominal pressure (IAP) 147
s can happen with IAP. Furthermore, a fluid-filled system
34.8; can produce artefacts that further distort the IAP pressure e 0.3 0.4 0.4 3.9 2.4 waveform. Failure to recognise these recording system artefacts can lead to interpretation errors [14]. It can oscillate spontaneously, and these oscillations can distort the IAP pressure curve. The performance of a resonant
25 per hour system is defined by the resonant frequency (this is the
e inherent oscillatory frequency) and the damping factor 2.2; male-male connector:
175; IAP catheter (Spiegel- (this is a measure of the tendency of the system to e e attenuate the pressure signal). Therefore, any fluid-filled system is prone to changes in body-position and over- or 0.6 0.4 0.4 0.4
12 times per day underdamping due to the presence of air-bubbles, a tubing 17.5; rectal/uterinel probe:
e that is too compliant or too long, etc. A rapid flush test should, therefore, always be performed before an IAP 1.36; nursing costs:
e reading in order to obtain an idea of the dynamic response 2.91.6 3.00.7 1.7 2.9 1.5 1.3 2.8 1.5 0.7 2.8 1.4 0.5 0.4 properties and to minimise these distortions and artefacts [16]. Confirmation of correct measurement can be done 55; tonometer (Datex): 1,250; conical connector: e by inspection of respiratory variations and by gently e 0.9 0.8 1.3 0.8 0.6 0.5 1.3 1.2 1.4 1.2 1.1 1.1 1.9 1.5 2.7 1.5 1.1 0.9 3weeks 4weeks 1week 2weeks 3weeks 4week applying oscillations to the abdomen that should be immediately transmitted and seen on the monitor with a quick return to baseline (Fig. 3). In case of a damped 0.3 0.3 0.3 0.3 0.3 0.3 4.1 3.9 3.91.0 4.1 0.7 3.91.0 0.6 3.8 0.7 1.0 0.6 3.8 0.6 1.0 0.4 0.6 0.4 2.7 2.6 2.5 2.7 2.5 2.5 15.3 10.2signal 7.7 the 15.3 flush 7.7 test 5.2 should be repeated. 0.31; sterile drapings:
e Other disadvantages are: it is an intermittent technique that interferes with urine output without the possibility of 6 times per day
100; Foleymanometer (Holtech): obtaining a continuous trend, it places the patient at e increased risk of urinary tract infection or sepsis, and subjects healthcare providers to the risk of needle stick 0.4; stopcock: oesophageal catheter (Ackrad): berg): e microchip transducer (Rehau): injuries and exposure to blood and body fluids [13]. In conclusion, the Kron technique has at the present time no clinical implications. 0.3; cost 0.53; 0.8 0.7 0.8 0.6 0.5 0.4 e e The closed system single measurement technique [16, 17] 3.82.6 3.4 2.33.77.5 3.2 2.1 2.5 5.1 3.4 2.1 1.9 3.9 3.0 1.7 2.5 5.1 2.9 1.6 1.3 2.7 0.9 Description The cost evaluation based on number of 6.2 3.2 2.2 1.8 2.2 1.3 4.5 3.4 3.1 2.9 3.1 3.6 2.3 1.9 1.7 1.8 1.4 5.9 4.8 4.4 4.3 4.4 Iberti and co-workers reported the use of a closed system 2 times per day 1week 2weeks 3weeks 4weeks 1week 2weeks drain and transurethral bladder pressure monitoring method [16, 17]. Using a sterile technique they infused an average 24.75; 50 ml of saline: 0.53; nasogastric tube:
e of 250 ml of normal saline through the urinary catheter to e purge catheter tubing and bladder. The bladder catheter is 0.3 0.4 0.4 0.4 0.4 0.4 0.2 4.9 2.5 1.8 1.4 1.8 0.2 5.2 2.7 1.8 1.4 1.8 0.1 91.4 45.7 30.5 22.9 30.5 Cost per measure- ment clamped and a 20-gauche needle is inserted through the culture aspiration port for each IAP measurement. The transducer is zeroed at the symphysis and mean IAP is read
Set-up cost after a 2-min equilibration period. (See ESM addendum 2)
0.023; Foley catheter: Advantages and disadvantages (Table 1) ence e It has the same disadvantages related to the hydrostatic fluid column as the Kron technique, and since it is not needle-free it also subjects health care workers to needle- Malbrain CurrentMalbrain 83.7 [28] 0.3 18.2 0.3 1.6 1.0 IbertiCheathamMalbrain [18] [17] CurrentMalbrainSugrue Current 31.3 34.7 30.2 [21] 101.7 1.3 1.0 2.7 0.1 202.7 3.7 0.3 4.8 7.4 stick 14.7 injuries [10, 11]. 0.36; needle: e Cost estimation (in Euros) of the different IAP measurement techniques: The advantage compared with the Kron technique is that it is simpler, less time-consuming, and there are fewer manipulations. In conclusion, the Iberti technique of initial set-up and next measurement, as well as cost projection Manometry LeeVena cavaMicrochip Lacey [27] Dowdle [29] [31] 1.2 1278.1 66.3 IAP measurements perwas day and based duration on of the measurement period. following estimates: transducer: Table 2 Technique Author Refer- Rectal Shafik [30] 70.1 Stomach Collee [20] 29.9 2.3 syringe: Bladder Kron. [13] 30.6 3.7 362 148 M.L.N.G. Malbrain
Fig. 3 Confirmation of correct IAP measurement can be done by inspection of respiratory variations and by gently applying oscillations to the abdomen that should be immediately transmitted and seen on the monitor with a quick return to the baseline has at the present time limited clinical implications (e.g. inserted in the drainage tubing connected to a Foley screening for IAH). catheter (Fig. 4A). A standard infusion set is connected to a bag of 1,000 ml of normal saline and attached to the first stopcock. A 60-ml syringe is connected to the second The closed system repeated measurement technique [18] stopcock and the third stopcock is connected to a pressure transducer via rigid pressure tubing. The system is flushed Description with normal saline and the pressure transducer is zeroed at the symphysis pubis (or the midaxillary line when the Cheatham and Safcsak reported a revision of Kron’s patient is in complete supine position). Figure 4B shows a original technique [18]. A standard intravenous infusion picture of the device in a patient with a close-up of the set is connected to 1,000 ml of normal saline, two manifold set with conical connectors. (See ESM adden- stopcocks, a 60-ml Luer-lock syringe and a disposable dum 4.) pressure transducer. An 18-gauche plastic intravenous infusion catheter is inserted into the culture aspiration port of the Foley catheter and the needle is removed. The Advantages and disadvantages (Table 1) infusion catheter is attached to the pressure tubing and the system flushed with saline. (See ESM addendum 3.) It has the same inconveniencies related to a fluid-filled system as described with the Kron, Iberti or Cheatham technique. This technique has the same advantages as the Advantages and disadvantages (Table 1) Cheatham technique, with a required nursing time less than 2 min per measurement, a minimized risk of urinary It has the same inconveniencies related to any fluid-filled tract infection and sepsis since it is a closed sterile system, system as described with the Kron and Iberti techniques. the possibility of repeated measurements and reduced It can pose problems after a couple of days because the cost. Since it is a needle-free system it does not interfere culture aspiration port membrane can become leaky or the with the culture aspiration port and the risk of injuries is catheter kinky, leading to false IAP measurement. The absent. This technique can be used for screening or for fact that the infusion catheter needs to be replaced after a monitoring for a longer period of time (2–3 weeks). couple of days could increase the infection risk and needle-stick injuries. This technique has minimal side effects and compli- The revised closed system repeated measurement cations, e.g. without an increased risk for urinary tract technique infection [19]. It is safer and less invasive, takes less than 1 min, is more efficient with repeated measurements In an anuric patient, continuous IAP recordings are possible and thus is more cost-effective [18]. This possible via the bladder using a closed system connected technique is ideal for screening and monitoring for a to the Foley catheter after the culture aspiration port or short period of time (a couple of days) because of leakage. directly to the Foley catheter using a conical connection piece connected to a standard pressure transducer via pressure tubing (Fig. 5). After initial “calibration” of the The revised closed system repeated system with 50 ml of saline and zeroing at the sypmhysis measurement technique pubis, the transducer is taped at the symphysis or thigh and a continuous IAP reading can be obtained. Daily Description calibration can be done in oliguric patients after voiding of rest diuresis. The technique of Cheatham and Safcsak was modified (Fig. 4), as follows. A ramp with three stopcocks is 363 Different techniques to measure intra-abdominal pressure (IAP) 149
Fig. 5 Close up view of a closed needle-free system for continuous intra-abdominal pressure measurement in an anuric patients, using a conic connection piece (conical connector with female or male lock fitting; B Braun, Melsungen, Germany — Ref. 4896629 or 4438450) connected to a standard pressure transducer via pressure tubing
measurement via the bladder maintain the patient’s Foley catheter as a closed system, limiting the risk of infection. Since these are needle-free systems they also avoid the risks of needle-stick injury and overcome the problems of leakage and catheter knick in the method described by Cheatham. They are more cost-effective, and facilitate repeated measurements of IAP.
Stomach
The classic intermittent technique [20]
Background and description
The IAP can also be measured by means of a nasogastric or gastrostomy tube and this method can be used when the patient has no Foley catheter in place, or when accurate bladder pressures are not possible due to the absence of free movement of the bladder wall. In case of bladder trauma, peritoneal adhesions, pelvic haematomas or Fig. 4 A A closed needle-free revised method for measurement of fractures, abdominal packing, or a neurogenic bladder, intra-abdominal pressure. A standard intravenous infusion set is connected to a bag of 1,000 ml of normal saline and attached to the IVP may overestimate IAP, and the procedure used for first stopcock. A 60-ml syringe is connected to the second stopcock the bladder can then be applied via the stomach [20]. (See and the third stopcock is connected to a pressure transducer via ESM addendum 5.) rigid pressure tubing. The system is flushed with normal saline and the pressure transducer is zeroed at the symphysis pubis. To measure IAP, the urinary drainage tubing is clamped distal to the ramp-device, 50 ml of normal saline is aspirated from the IV bag Advantages and disadvantages (Table 1) into the syringe and then instilled in the bladder. After opening the stopcocks to the pressure transducer mean IAP can be read from the The same inconveniences as with every fluid-filled bedside monitor. See ESM addendum 4 for explanation. B Mounted system apply. Another disadvantage is that gastric patient view of the device and close up of manifold and conical connection pieces pressures might interfere with the migrating motor complex or with nasogastric feeding. Furthermore all air needs to be aspirated from the stomach before measuring Conclusion IAP, something that is difficult to verify. The advantages are that it is cheap, does not interfere In conclusion, if one wants to use IVP as estimate for IAP with urine output, and the risks of infection and needle- the Cheatham or revised technique is preferred over the stick injuries are absent. This cost-effective technique is Kron or Iberti technique. The revised methods for IAP ideal for screening. 364 150 M.L.N.G. Malbrain
The semi-continuous technique [21, 22]
Background and description
Sugrue and co-workers assessed the accuracy of measur- ing simultaneous IVP and IAP via the balloon of a gastric tonometer during laparoscopic cholecystectomy [21]. They found a good correlation between both methods. This technique allows a trend to be obtained. We recently validated these results and found good correlation between the classic gastric method, the tonometer method and IVP [22]. Simultaneous IAPtono and PrCO2 mea- surement was also possible. (See ESM addendum 6.)
Advantages and disadvantages (Table 1)
Measurement via the tonometer balloon limits the risks and has major advantages over the standard intravesical method: no infection risk and no interference with estimation of urine output. Simultaneous measurement of IAP and PrCO2 is possible; however, only in an intermittent way. Since it is air-filled it has none of the disadvantages associated with fluid-filled systems: no problem with zero-reference, over- or underdamping or Fig. 6 A An oesophageal balloon catheter is inserted into the body position. A possible disadvantage is the effect on stomach (Oesophageal balloon catheter set, adult size with PTFE interpretation of IAP values by the migrating motor coated stylet; Ackrad Laboratories, Cranford, N.J., USA — Ref. 47- complex. Recording the “diastolic” value of IAP at end- 9005, see at http://www.ackrad.com/products/c-balloon_catheter. expiration can solve this problem. Other problems are that cfm or compliance catheter female or male, International Medical Products, Zuthpen, Netherlands, distributed by Allegiance — Ref. a 5-ml glass syringe is needed and that no data are 84310). A standard three-way stopcock is connected to the now available on effects of enteral feedings on these IAP “nasogastric” tube; one end is connected to a pressure transducer measurements. This technique could be used for study via arterial tubing. All air is evacuated from the balloon with a glass purposes and clinicians interested in simultaneous CO2 syringe and 1 ml of air reintroduced to the balloon. A glass syringe gap and IAP monitoring. is recommended to minimize the risk of pulling a negative pressure inside the catheter prior to reintroducing the 1 ml air. The balloon is connected via a “dry” system to the transducer, the transducer itself is not classically connected to a pressurized bag and not flushed The revised semi-continuous technique with normal saline in order to avoid air/fluid interactions. The transducer is zeroed to atmosphere and IAP is read end-expiratory. See text for explanation. B Close-up view of the oesophageal Description balloon catheter An oesophageal balloon catheter is inserted into the stomach. When the balloon is in the stomach, the whole expiratory. Figure 6B shows a close-up of the oe- respiratory IAP pressure wave will be positive and sophageal balloon catheter. (See ESM addendum 7.) increasing upon inspiration in case of a functional diaphragm. If the balloon is too high in the thorax the pressure will flip from positive to negative on inspiration Advantages and disadvantages (Table 1) measuring oesophageal or pleural pressure instead. A standard three-way stopcock is connected to a pressure A disadvantage is that the air in the balloon gets resorbed transducer (Fig. 6A). All air is evacuated from the balloon after a couple of hours (Fig. 7), so that “recalibration” of with a glass syringe and 1–2 ml of air reintroduced to the the balloon is necessary with a 2–5 ml glass syringe for balloon. The balloon is connected via a “dry” system to continuous measurement, this might cause inaccurate the transducer, the transducer itself is NOT classically measurement if the nurse waits too long for recalibration connected to a pressurized bag and not flushed with or if the re-instilled volume is not exactly the same as the normal saline in order to avoid air/fluid interactions. The previous one. It is less time-consuming and has all the transducer is zeroed to atmosphere and IAP is read end- advantages of an air-filled system (cfr tonometer). By 365 Different techniques to measure intra-abdominal pressure (IAP) 151
Fig. 7 A trend of 24-h IAP and APP recordings obtained with an Fig. 8 A continuous trend of 24-h IAP and APP recordings oesophageal balloon placed in the stomach (Ackrad). Note the obtained with the Spiegelberg balloon-tipped IAP catheter placed resorption of air after a couple of hours, with loss of IAP signal, in the stomach. Note the absence of resorption of air due to confirming the need for recalibration automated recalibration every hour. Note also the effect of CAPD fluid inflow on IAP. If IAP was measured only twice a day the fluctuations and peak pressures would have been missed using this technique the cost of IAP is further reduced depending on the catheter used. Moreover, a semi- continuous measurement of IAP as a trend over time is Advantages and disadvantages (Table 1) possible. The oesophageal balloon catheter price ranges from e15 (International Medical Systems, The Nether- This technique has no major disadvantage except that lands) to e55 (Ackrad, USA). This technique is ideal for validation in humans is still in its infant stage. The monitoring for a longer period of time; however, when advantages are those related to other gastric and air-filled using multiple tubes the risk of sinusitis or infection needs methods. In summary, it is simple, fast, accurate, to be evaluated in the future. reproducible, and fully automated, so that a real contin- uous 24-h trend can be obtained (Fig. 8). This technique is not suited for screening, but is best for continuous fully The continuous fully-automated technique automated monitoring for a long period of time. Since it is less prone to errors and most cost-effective if in place for Description: IAP measurement with the air-pouch system a longer period of time, this technique has a lot of potential in becoming the future standard for multicentre The IAP-catheter is introduced like a nasogastric tube; it research purposes. is equipped with an air pouch at the tip. The catheter has one lumen that connects the air-pouch with the IAP- monitor and one lumen that takes the guide wire for Conclusion introduction. The pressure transducer, the electronic hardware, and the device for filling the air-pouch are The revised methods via the stomach have the advantage integrated in the IAP-monitor. Once every hour the IAP- of being free from interference caused by wrong trans- monitor opens the pressure transducer to atmospheric ducer positions, since the creation of a conductive fluid pressure for automatic zero adjustment. The air-pouch is column is not needed as air is used as the transmitting then filled with a volume of 0.1 ml required for accurate medium. The last described fully automated technique pressure transmission. Initial validation in ICU patients also gives a continuous tracing of IAP together with and laparoscopic surgery showed good correlation with abdominal perfusion pressure (APP) in analogy with the standard IVP method [23]. Recently Schachtrupp and intracranial pressure and cerebral perfusion pressure, co-authors used the same technique to directly measure allowing both parameters to be monitored as a trend over IAP in a porcine model and found a very good correlation time. The APP is calculated by subtracting IAP from the between the air pouch system and direct insufflator mean arterial blood pressure. Recent data showed the pressure (R2=0.99) with a mean bias of 0.5€2.5 mmHg importance of APP as a superior marker for IAH to titrate and small limits of agreement ( 4.5 to 5.4 mmHg) [24]. better the resuscitation of patients with IAH and ACS, (See ESM addendum 8.) hence avoiding end-organ failure and associated morbid- ity and mortality [2, 25]. 366 152 M.L.N.G. Malbrain
Manometry The Foleymanometer technique [28]
The classic technique [1, 2, 26] Description
Description We recently tested a prototype (Holtech Medical, Copen- hagen, Denmark) for IAP measurement using the patients’ A quick idea of the IAP can also be obtained in a patient own urine as pressure transmitting medium [28]. A 50 ml without a pressure transducer connected by using his own container fitted with a bio-filter for venting is inserted urine as the transducing medium, first described by nurse between the Foley catheter and the drainage bag Harrahill [1, 2, 26]. One clamps the Foley catheter just (Fig. 9A). The container fills with urine during drainage; above the urine collection bag. The tubing is then held at when the container is elevated, the 50 ml of urine flows a position of 30–40 cm above the symphysis pubis and the back into the patient’s bladder, and IAP can be read from clamp is released. The IAP is indicated by the height (in the position of the meniscus in the clear manometer tube cm) of the urine column from the pubic bone. The between the container and the Foley catheter (Fig. 9B). meniscus should show respiratory variations. This rapid We found a good correlation between the IAP obtained estimation of IAP can only be done in case of sufficient via the Foleymanometer and the “gold standard” in 119 urine output. In an oliguric patient 50 ml saline can be paired measurements (R2=0.71, P<0.0001). The analysis injected as priming. (See ESM addendum 9.) according to Bland and Altman showed that both measurements were almost identical with a mean bias of 0.17€0.8(SD) mmHg (95% CI 0.03–0.3). (See ESM Advantages and disadvantages (Table 1) addendum 11.)
It has all the inconveniencies that come along with a fluid-filled system as described before. However, since it Advantages and disadvantages (Table 1) is needle-free it poses no risks for injuries. It allows repeated measurements, is very inexpensive and fast with It has the same inconveniencies and advantages as the minimal manipulation. Since the volume re-instilled into other manometry techniques. It allows repeated measure- the bladder is not constant raising questions on accuracy ments, is very cost-effective and fast, with minimal and reproducibility, it has limited clinical implications. manipulation. The great advantage with the Foley- manometer is that the volume re-instilled into the bladder is standardised at 50 ml; therefore, it is preferred over the The U-tube technique [27] other manometry techniques. A major drawback is the possibility of occasional blocking of the bio-filter, leading Description to overestimation of IAP in some cases and the presence of air-bubbles in the manometer tube, producing multiple In a recent animal study, Lee and co-workers compared menisci leading to misinterpretation of IAP. Further direct insufflated abdominal pressure with indirect blad- refinement and multicentric validation needs to be done der, gastric and inferior vena cava pressures [27]. IVP was before being used in a clinical setting. measured by both the standard and U-tube technique. With the U-tube technique, the catheter tubing was raised approximately 60 cm above the animal to form a U-tube Conclusion manometer, and IVP was measured as the height of the meniscus of urine from the pubic symphysis. The authors The manometry techniques give a rapid and cost-effective found a good correlation between the U-tube pressure and idea of the magnitude of IAP and may be as accurate as other direct and indirect techniques. (See ESM adden- other direct and indirect techniques. They can easily be dum 10.) done two-hourly together with and without interfering with urine output measurements. Moreover, the risk of infection and needle stick injury is absent. Since they Advantages and disadvantages (Table 1) need to be validated in a multicentre setting they are not ready for general clinical usage at the present moment. It has the same advantages and inconveniences as the classic “Harrahill” technique, as with the previous technique the clinical validation is poor. The major advantage of this technique is that the volume re-instilled into the bladder is more stable (but still not well defined), so it can be used as a quick screening method. 367 Different techniques to measure intra-abdominal pressure (IAP) 153
Rectal pressure
Description
Rectal pressures are used routinely as estimate for IAP during urodynamic studies to calculate the transmural detrusor muscle pressure as IVP minus IAP [29, 30]. Rectal pressures can be obtained by means of an open rectal catheter with a continuous slow irrigation (1 ml/ min), but special fluid-filled balloon catheters are used more routinely, although are more expensive. (See ESM addendum 12.)
Advantages and disadvantages (Table 1)
The major problem with the open catheter is that residual faecal mass can block the catheter-tip opening leading to overestimation of IAP. Other disadvantages of this technique are that it is more difficult, implicates more manipulation, is intermittent, and cannot be used in patients with lower gastro-intestinal bleeding or profound diarrhoea. There is also a great reluctance among nurses to use it. Since it is fluid-filled, it has all the problems associated with a hydrostatic fluid column, but since it is needle-free it decreases patient and healthcare worker infections or injuries. The fluid-filled balloon catheters are more expensive and, even though could theoretically stay in place for a longer period of time, interfere with gastro-intestinal transit and can cause erosions and even necrosis of the anal sphincter and rectal ampulla. Finally these techniques have not been validated in the ICU setting. This technique has no clinical implications in the ICU setting.
Uterine pressure
Description
Basically this technique is mostly done with the same catheters as for the rectal route. Uterine pressures are used routinely by gynaecologists during pregnancy and labour. Most classically a standard so-called “intra-uterine pres- sure catheter” (IUPC) is used for this purpose [31]. Uterine pressures are mostly obtained by means of a closed special fluid-filled balloon catheter (as for rectal pressure). (See ESM addendum 12.)
Advantages and disadvantages (Table 1) Fig. 9 A The Holtech Foleymanometer: second prototype consists of a 50 ml container fitted with a bio-filter for venting inserted The major disadvantages of this technique are the same as between the Foley catheter and the drainage bag. B The use of the Holtech Foleymanometer: schematic drawing. The container fills for rectal pressures: i.e. it is more difficult, implicates with urine during drainage (position 1); when the container is more manipulation, is intermittent, and cannot be used on elevated (position 2), the 50 ml of urine flows back into the patients with gynaecological bleeding or infection. Since patient’s bladder, and IAP can be read from the position of the it is also fluid-filled it has all the problems associated with meniscus in the clear manometer tube between the container and the Foley catheter 368 154 M.L.N.G. Malbrain a hydrostatic fluid column, but is needle-free. Finally, this Microchip transducer-tipped catheters technique has not been validated in specific ICU patient populations. This technique has no clinical implications in Description the ICU setting. Different types of catheters tipped with microchip trans- ducers are nowadays available on the market. They can Inferior vena cava pressure either be placed via the rectal, uterine, vesical or gastric route. These catheters can either have a 360 membrane Description pressor sensor in the organ (rectum, uterus, bladder, stomach) connected to an external transducer in a The inferior vena cava pressure (IVCP) has been reusable cable or they can have a fibre-optic in vivo suggested as an estimation for IAP. Basically it uses the pressure transducer in the tip of the catheter itself. These same techniques as described previously but applied to an catheters provide true zero in-situ calibration. By discon- IVC catheter. A normal central venous line is inserted into necting and checking for zero on the monitor, clinicians the inferior vena cava via the left or right femoral vein. can instantly validate and check the zero status of the The intra-abdominal position of the catheter is confirmed monitor and the transducer [31]. Recently, Schachtrupp by portable lower abdomen X-ray, and confirmation of a and co-workers found a good correlation between IAP rise in IAP following external abdominal pressure. A calculated be a piezoresistive pressure measurement and three-way stopcock is connected to the distal lumen, one direct insufflator pressure (R2=0.92), with a difference of end is connected to a pressure transducer via arterial 1.6€4.8 mmHg; however, the limits of agreement were tubing and the other end is connected to a pressurized large ( 8 to 11.2 mmHg) [24]. This might have been due infusion bag of 1,000 ml saline. The transducer is zeroed to an unknown measurement drift due to the fact that the at the midaxillary line with the patient in the supine device cannot be zeroed to the environment when placed position and IAP is read end-expiratory as with CVP. intra-abdominally. (See ESM addendum 13.)
Advantages and disadvantages (Table 1) Advantages and disadvantages (Table 1)
The major disadvantage of this technique is the risk of The major disadvantages of this technique is that it is very (possible catheter-related) bloodstream infections and expensive, with catheter-price ranging from e1,000 to septic shock. The initial placement is more time-consum- e1,500. These catheters are said to be re-usable a couple ing. It has also the problems inherent to fluid-filled systems of times after cleaning with soap and water and gas and poses potential injury to the patient and healthcare sterilisation, but no data on ICU patients are available. workers. The major advantages are that a continuous trend These catheters are mostly used during urodynamic can be obtained, it does not interfere with urine output, and studies and labour for a limited period of time (hours); it could be used in bladder-trauma patients. Finally this none of them have been tested in ICU patients for longer technique has not been validated in specific ICU patient periods of time (days to weeks). The major advantages are populations. In an animal study comparing different that a continuous trend can be obtained, it is less time- methods of indirect IAP measurement, Lacey and co- consuming, and it does not interfere with urine output. workers found a good correlation between bladder and This technique has no clinical implications in the ICU inferior vena cava pressure with direct intraperitoneal IAP setting. measurement, but not with gastric, femoral or rectal pressure [29]. Lee and co-workers also found a good correlation in 30 patients during laparoscopy [27]. A recent Reproducibility of IAP measurement study in man, comparing superior vena cava pressure (SVCP) with common iliac venous pressure (CIVP) in As stated previously, the intra-vesical route evolved as the various conditions of IAP and PEEP showed that the gold standard. However, considerable variability in the difference between CIVP and SVCP was not affected by measurement technique has been noted and the common the IAP, which implies that CIVP does not reflect IAP pitfalls are briefly addressed below. correctly [32]. The most likely explanation is the differing anatomy and experimental model used to induce increased 1. Malpositioning of the pressure transducer with regard to IAP in canine studies. In humans both CVIP and SVCP the symphysis pubis after repositioning of the patient. increase as IAP increases [32]. Recently, Joynt and co- This may lead to over- and underestimation of IAP, workers also found a good correlation between SVCP and which is commonly seen at changes of nurse shifts. IVCP regardless of IAH [33]. This technique has limited 2. All fluid-filled systems connected to a pressure implications in the ICU setting. transducer have their own dynamic response properties 369 Different techniques to measure intra-abdominal pressure (IAP) 155
that can create distortions or artefacts in the IAP sured IAP during laparoscopy. In a recent study, Yol pressure waveform, leading to signal over- or under- and co-workers compared bladder pressure with direct damping [14, 15]. insufflation pressure during laparoscopic cholecystec- 3. It is the most used and validated technique, but with tomy in 40 patients and he found a very good inadequate accuracy and reproducibility. The inaccu- correlation between the two measurements (R=0.973, racy can come from the presence of air-bubbles in any P<0.0001) [32]. This was also shown by Fusco and co- fluid-filled system leading to over- or underestimation. workers, who compared direct laparoscopic insuffla- If the measurement itself is inaccurate, this also tion pressure with bladder pressures measured with implies that it is not reproducible. However, when bladder volumes of 0, 50, 150 and 200 ml [5]. He the pressure transducer position is consistently too found that there was a good correlation across the IAP high or too low with a fully compliant transducer range from 0 to 25 mmHg between direct and indirect system of high intrinsic resonant frequency the IAP methods with all tested volumes. A bladder volume of value obtained will be too low or too high, respec- 0 ml demonstrated the lowest bias, but when consid- tively, but may be reproducible. In order to get an idea ering only elevated IAPs (25 mmHg) a bladder volume of these reproducibility problems with bladder pres- of 50 ml revealed the lowest bias. He concluded that sure we performed a multicentre snapshot study (four intravesicular pressure closely approximates IAP and IAP measurements each every 6 h) on a given day [4]. that instilling 50 ml of saline improved the accuracy of The mean IAP was 10.2€2.7 mmHg, (range 7.6€4 to the bladder pressure in measuring elevated IAPs. 12.7€5.7). Analysis according to Bland and Altman However Johna and co-workers recently found that showed a global bias of IAP within 24 h (difference intravesicular pressure did not reflect actual intra- between minimum and maximum value) of 5.1€3.8 abdominal insufflation pressure (limited up to (SD) mmHg (95% CI 4.3–5.9); the limits of agreement 15 mmHg) during laparoscopy [34]. He concluded were 2.5 to 12.7 mmHg. The bias differed from that further research is needed to identify possible centre to centre between 2.4 and 6.2 mmHg, with one variables that may play a role in the relationship outlier bias value as high as 11 mmHg, raising between the urinary bladder and abdominal cavity questions as to the reproducibility of the measurement pressures, providing better means for diagnosing ACS. technique used in that centre and making it difficult to Further reading shows that the methodology of this compare literature data [4]. The mean coefficient of study was poor. variation (defined as the standard deviation divided by 6. Although many articles have validated IVP against the mean IAP) was 25%, which is comparable to daily direct insufflation pressures, it is difficult to extrapolate fluctuations in other pressures, like central venous these single observer comparisons in patients undergo- pressure or pulmonary artery occlusion pressure. ing general anesthesia and paralysis to a mixed ICU However, this coefficient ranged from 4% to 66% population of patients not under muscle relaxation as between centres. Since the literature provides no data well as subject to other confounding factors (nurse on 24-h continuous IAP-measurement in the ICU, it is shifts, position, zero reference, etc.). Direct IAP not possible to determine whether these variations or measurement via a laparoscopic insufflator is prone fluctuations in IAP during one study day were normal to errors by flow dynamics, resulting in rapid increases or related to the measurement technique used. in pressure during insufflation. The Verres needle 4. The bladder “gold standard” measurement techniques opening can be blocked by tissue or fluid leading to reported are not uniform; most authors recommend to over- or underestimation of IAP and pressures can be inject 50 ml [1, 2], others 0 ml [16], 100 ml [13, 23], influenced by muscle relaxation. Laparoscopy remains 200 ml (data from internet: Brenda Morgan, Clinical an artificial environment, this makes it even more Educator, CCTC on http://critcare.lhsc.on.ca/education/ difficult to validate indirect IAP measurement methods. abdcompt.html, last revised 2001) or even 250 ml [17] 7. Baseline IAP and the volume instilled in the bladder of saline into the bladder. In fact, in the initial article are important. Gudmundsson and co-workers found from Iberti and co-workers, data are presented from a recently in an animal study that the IAP increase by canine model without stating the volume instilled in the instilling Ringer’s solution into the abdominal cavity bladder. The only statement was that “the bladder was correlated well with intra-vesical pressures [6]. It was continuously emptied between measurements” [16]. In also found that IVP as an estimation for IAP is affected a following study, Iberti and co-workers presented by the amount of fluid in the bladder that should not human data stating, “using a sterile technique an exceed 10–15 ml. If the baseline IAP is lower than average of 250 ml of normal saline was infused through 8 mmHg, a 131-ml extra bladder volume is needed to the urinary catheter to gently fill the bladder and increase IAP by 2 mmHg; however, if baseline IAP is eliminate air in the drainage catheter” [17]. 20 mmHg, only 39-ml extra bladder volume is needed 5. Conflicting results are reported in the literature for the same IAP increase [6]. We recently came to the regarding the validation of IVP versus directly mea- same conclusions: by analysing bladder pressure 370 156 M.L.N.G. Malbrain
volume curves we found that IVP significantly Many of these drawbacks are not only true for the increased depending on the volume instilled. The bladder but are also present when IAP is estimated via IVP rose from 4.2€3.2 mmHg at the baseline to other routes. Not much has been studied on the effects of 6.9€5 mm Hg with 50 ml and 23.7€16.1 at 300 ml spontaneous breathing, mechanical ventilation, the pres- (P<0.0001, ANOVA) [7]. If IVP is used as an estimate ence of expiratory muscle activity, auto-PEEP, and for IAP, the volume instilled in the bladder should be curarisation on IAP measurement via the different routes. between 50 and 100 ml; however, in some patients Definitions for IAH and ACS stand or fall by the with a low bladder compliance IVP can be raised at correct measurement of IAP and its reproducibility. low bladder volumes. Ideally a bladder PV curve Recent literature data put the bladder pressure in question should be constructed for each individual patient as the so-called gold standard for abdominal pressure [5, before using IVP as an estimation for IAP. This study 6, 34–36]. makes it difficult to compare the literature data. It raises not only questions with regard to the previously published definitions and IAP cut-offs, but it also puts Conclusion the IVP in question as the so-called gold standard. Ideally the bladder should be fully emptied before an This review has undertaken an analysis of the advantages IAP measurement, but how can you be really sure? and disadvantages, as well as a cost projection, for each 8. Body position is important. Putting a patient in IAP measurement technique and supports the view that: different body positions has significant effects on IAP (1) there is no gold standard; (2) it is difficult to compare (Fig. 10). This is in contradiction with the hypothesis the different techniques; (3) cost-effectiveness is an issue; that the abdominal compartment is primarily fluid in (4) IVP can be used as an estimation for IAP as a character and should follow the law of Pascal, since screening method to identify patients at risk via manom- IAP would then remain constant regardless of body etry; (5) IVP can be used as an estimation for IAP for position as fluid is not compressible. The abdomen initial follow-up either with the Cheatham or revised should in fact be looked at as a “fluidlike” compart- bladder technique; (6) for (multicentre) study purposes, ment with different components that may influence IVP surgical patients, trauma patients, patients at risk for IAH (the intrinsic weight of the organs, the presence of and difficult ICU patients, like mechanically ventilated ascites, the air in the bowel, etc.). Assessment of IAP patients with one or more other organ failures (assessed should, therefore, always be done in the complete by SOFA score), it is preferable to switch to a continuous supine position. The upright position significantly method for IAP monitoring via the stomach and focus increases IAP compared with the supine. The effects therapy on optimising IAP and APP. on IAP being more pronounced in obese patients [35]. Acknowledgements I am indebted to my wife, Ms. Bieke Depr , for her patience, advice and technical assistance with the prepa- ration of this manuscript, and to my three sons for providing a quiet writing environment. I also thank Dr. Rao Ivatury and Julia Wendon for their English editing of the manuscript. Part of this work was presented at: the 14th Annual Congress of the European Society of Intensive Care Medicine, Geneva, Switzerland, 30 September–3 October 2001; the 22nd International Symposium on Intensive Care and Emergency Medicine, Brussels, Belgium, 19–22 March 2002; the 13th Symposium Intensivmedizin and Inten- sivpflege, Bremen, Germany, 19–21 February 2003; the 23rd International Symposium on Intensive Care and Emergency Medicine, Brussels, Belgium, 18–21 March 2003; the 16th Annual Congress of the European Society of Intensive Care Medicine, Amsterdam, The Netherlands, 5–8 October 2003. This study was supported by Holtech Medical, Denmark (contact Bo Holte at [email protected]). There was no financial support from Holtech other than making the product (Foleymanometer) available, free of charge. This study was supported by Ackrad Medical, USA (contact Charles Noto at [email protected]). There was no financial support from Ackrad other than making five oesophageal balloon catheters available, free of charge. This study was supported by Spiegelberg, Germany (contact Andreas Spiegelberg at [email protected]). There was no financial support from Spiegelberg other than making the gastric balloon IAP-catheters Fig. 10 Boxplot of mean IAP values in different body positions. and IAP-monitors available for study purposes, free of charge. The IAP was significantly higher in the anti-Trendelenburg and upright position versus the supine, and significantly lower in the Trendelenburg position versus the supine (P<0.0001, one-way Anova) 371 Different techniques to measure intra-abdominal pressure (IAP) 157
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Abstract Increases in tissue partial able marker of tissue perfusion. pressure of carbon dioxide (PCO2) Clinical studies have demonstrated can reflect an abnormal oxygen sup- that high PslCO2 values and, espe- ply to the cells, so that monitoring cially, high gradients between PslCO2 tissue PCO2 may help identify circu- and arterial PCO2 (DPsl-aCO2) are latory abnormalities and guide their associated with impaired microcircu- correction. Gastric tonometry aims at latory blood flow and a worse prog- monitoring regional PCO2 in the nosis in critically ill patients. Al- stomach, an easily accessible organ though some questions remain to be that becomes ischemic quite early answered about sublingual capnome- when the circulatory status is jeop- try and its utility, this technique could ardized. Despite substantial initial offer new hope for tissue PCO2 enthusiasm, this technique has never monitoring in clinical practice. been widely implemented due to various technical problems and arti- Keywords Sublingual capnometry · facts during measurement. Experi- Gastric tonometry · Tissue PCO2 · mental studies have suggested that Microvascular blood flow · sublingual PCO2 (PslCO2) is a reli- Outcome · Critically ill patients
Introduction the shortcomings that preclude the widespread use of gastric tonometry. Tissue hypoperfusion is a common pathophysiological Here we review current knowledge about sublingual process leading to multiple organ dysfunction and death capnometry, its applicability and its limitations, as a tech- [1–4]. The major objectives in the management of acute- nique to evaluate organ perfusion in acutely ill patients. ly ill patients are to prevent, detect and correct tissue dysoxia as soon as possible to minimize organ damage [5]. Unfortunately, none of the currently available moni- The saga of gastric tonometry toring systems are very reliable at the bedside. Systemic hemodynamic and oxygenation parameters lack sensibil- Current hemodynamic monitoring techniques, including ity and specificity [5–7], especially in sepsis [8, 9]. the pulmonary artery catheter, are quite invasive and carry The possibility of detecting early signs of tissue hy- a risk of complications [10, 11] and higher costs [12], poperfusion by regional monitoring led to a great interest with controversial benefit [13, 14]. The measurement of in gastric tonometry. However, much of the enthusiasm arterial lactate concentrations may not reflect early al- was tempered by technical or artifactual problems and terations and have their own limitations [7, 15, 16]. difficulties in demonstrating the utility of gastric tonom- Gastric tonometry has raised a lot of interest [17, 18] etry-derived variables as therapeutic guides. Sublingual based on three important concepts: (a) tissue hypercarbia capnometry has emerged in recent years as a potential is a marker of mismatch between blood flow and oxy- alternative to monitoring tissue perfusion without some of gen demand [19]; (b) introduction of a gastric tube is a
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 159 DOI: 10.1007/978-3-642-01769-8_31, © Springer-Verlag Berlin Heidelberg 2009 2158 160 A.T. Maciel, J. Creteur and J.-L. Vincent
common procedure in acutely ill patients and (c) the gut tion between aerobic and anaerobic production of CO2 in mucosa is exquisitely susceptible to hypoperfusion [20]. the body is quite difficult [32]. A number of studies have indicated that gastric tonome- try-derived variables have prognostic value [9, 21, 22]. Changes in gastric mucosal PCO2 (PgCO2) may precede Carbon dioxide content-partial pressure alterations in systemic variables [23–25] and the PCO2 of carbon dioxide relationship gap (the difference between PgCO2 and arterial PCO2) may represent a valuable monitoring system [21, 22, 26]. The relation between CCO2 and PCO2 follows a curvi- Unfortunately, gastric tonometry has serious limita- linear shape so that changes in PCO2 are not always as- tions, even after the advent of gas tonometry [27, 28], sociated with similar changes in CCO2. Some physio- including interruption of enteral feeding and concomitant logical variables can also interfere with this relationship, use of H2-blockers [28]. All these drawbacks reduce the such as hemoglobin concentration and its oxygen satu- clinical utility of the stomach as a practical place for ration [40], pH and temperature: none of which are of routine tissue PCO2 measurement. established clinical significance [41, 42].
Physiological concepts to interpret tissue Monitoring tissue partial pressure partial pressure of carbon dioxide of carbon dioxide in sites other than the stomach
Blood flow as the main determinant Tissue hypercapnia is ubiquitous in shock states. The of tissue carbon dioxide content (CCO2) methodological limitations of gastric tonometry prompted a search for alternative sites of tissue PCO2 monitoring. Tissue CCO2 is determined by three variables: arterial Walley et al. [43] proposed, in an experimental model of CCO2 (CaCO2), regional blood flow and tissue CO2 hemorrhagic shock in pigs, that small bowel (jejunum) production (aerobic or anaerobic). In stable respiratory tonometry is more accurate than gastric tonometry in conditions when CaCO2 is constant, tissue CCO2 reflects detecting gut ischemia, and sigmoid tonometry has been the balance between tissue blood flow and local CO2 studied as a surrogate monitor of gastrointestinal isch- production. In low flow states, CCO2 increases as a re- emia, especially useful in aorto-iliac surgery—in which sult of the “CO2 stagnation phenomenon” [29], even in left ischemic colitis is a well known complication [44– the absence of dysoxia. Studies comparing ischemic and 46]. Sato et al. [47] demonstrated, in a rodent model of hypoxic hypoxia in animal models [30, 31] have dem- hemorrhagic shock, that the esophagus luminal PCO2 onstrated that the reduction in blood flow is the main (PeCO2) was a reliable surrogate for the PgCO2. determinant of tissue CO2 accumulation, since even in In addition to the gastrointestinal tract, experimental severe dysoxic conditions induced by pure hypoxic hyp- studies have used tonometry to detect hypoperfusion in oxia (a condition in which blood flow is maintained), CO2 other places in the body including the brain [48], bladder accumulation has not occurred [31]. However, while [49], muscle [50] and peritoneum [51]. However, these mechanistically interesting, the hypoxic hypoxia model is sites are not practical for routine use and, in the search for not clinically relevant. a place in the body where tissue PCO2 could be easily and rapidly measured in a non-invasive and more practical way, Nakagawa et al. [52] suggested that the sublingual Aerobic and anaerobic production of carbon dioxide mucosa could be a valuable site.
Carbon dioxide production occurs in both aerobic and anaerobic situations [32–35]. Increases in aerobic me- Relevant aspects of sublingual anatomy tabolism are associated with higher CO2 production by and physiology the cells, which is generally associated with parallel in- creases in blood flow, so that tissue PCO2 does not in- The sublingual mucosa is a highly vascularized surface crease (“washout phenomenon”). When oxygen delivery supplied by the sublingual arteries, which stem from the decreases and reaches a critical value, aerobiosis can no lingual arteries, branches of the external carotid arteries. longer be sustained and anaerobic production of CO2 by Indeed, in addition to the esophagus, the sublingual region the cells increases as a result of buffering of excess pro- is not part of the splanchnic area. However, alterations in tons by bicarbonate ions and decarboxylation of meta- sublingual blood flow may occur in response to feeding, bolic intermediates [36]. However, during tissue dysoxia, with increased production of saliva by sublingual glands. total CO2 production may be decreased [37–39] because This process is mediated mainly by the parasympathetic the fall in aerobic CO2 production can be greater than the nervous system in response to many factors, including increase in anaerobic CO2 production. In fact, a distinc- 2159 Tissue capnometry 161 direct tactile stimulus and as a reflex response to the sion, such as mean arterial pressure, cardiac index and presence of food in the stomach or proximal intestine. arterial lactate concentration. It is important to note that the septic shock model used in this study was character- ized by a hypodynamic status. Sublingual partial pressure Povoas et al. [53] demonstrated similar phenomena in of carbon dioxide measurement pigs during bleeding and re-infusion, with a close corre- lation between PgCO2 and PslCO2 values. In another study Experimental and clinical studies regarding sublingual in rats [58], hemorrhage resulted in a decrease in blood capnometry have used essentially two different devices: flow in several organs, including the sublingual region, MI-720 CO2 electrode (Microelectrodes; Londonderry, and these decreases were associated with simultaneous NH, USA) and CapnoProbe SL Monitoring System increases in PslCO2. (Nellcor; Pleasanton, CA, USA). As with gut mucosal PCO2 [59–62], arterial PCO2 MI-720 is a CO2 electrode that needs to be calibrated (PaCO2) also influences PslCO2. Pernat et al. [54] showed in standard gases with known percent values of CO2 be- that acute changes in PaCO2 induced by hypo- and hy- fore use. Although not originally designed to be used perventilation in rats influence PslCO2 under physiologi- under the tongue, it is the device that has been used in cal conditions and during hemorrhagic shock. Hence, most relevant experimental studies regarding PslCO2 changes in PslCO2 should be interpreted in relation to the measurement [52–54] and also in the first clinical study concurrent PaCO2; the gradient (DPsl-aCO2) rather than reported [55]. Weil et al. [55] made some modifications to PslCO2 per se must be considered. the device in such a way that it fits better in the human sublingual space and avoids contact with room air, which can interfere badly with measurements. Clinical studies The CapnoProbe was specially designed for the mea- surement of PslCO2 and has been used in most of the Four clinical studies using sublingual capnometry in crit- clinical studies on this subject [7, 56, 57]. It consists of a ically ill patients have been reported [7, 55–57] (Table 1). disposable PslCO2 sensor, which is actually a CO2-sensing Weil et al. [55] reported the first clinical, prospective in- optode. The optode comprises a CO2-permeable silicone vestigation on sublingual capnometry. These authors capsule filled with a fluorescent dye in a buffer solution, measured PslCO2 and simultaneous values of arterial blood at the distal end of an optical fiber. The fluorescent in- pressure, heart rate and arterial lactate concentrations in 46 dicator is excited by light conducted through the optical patients admitted to the emergency room, intensive care fiber and changes in the projected light caused by changes unit (ICU) or trauma service with life-threatening illness in fluorescent emission are monitored by the optical fiber. or injuries, 26 of whom were considered to be in shock on These changes occur as a consequence of parallel changes the basis of a systolic pressure less than 100 mmHg and in the pH of the solution, which is a result of the presence physical signs of circulatory failure at the time of admis- of CO2 and formation of carbonic acid (H2CO3). Light sion. The authors found higher PslCO2 values in the shock signals are then transferred via the optical fiber to an group and suggested that a PslCO2 threshold value of instrument where they are converted to a numerical value 70 mmHg was predictive of the severity of the circulato- of PCO2. If properly placed under the tongue with the ry failure and the likelihood of hospital survival. Initial mouth shut, exposure to the environmental air and light is PslCO2 values were highly correlated with arterial lactate minimal. A few minutes are necessary for calibration and concentrations but decreased more promptly during ef- equilibration, which are made in a liquid solution with a fective treatment, suggesting that decreases in PslCO2 known concentration of CO2. The capability range of occur faster and closer to the real time of hemodynamic measurement with this device is from 30 to 150 mmHg. improvement than arterial lactate concentrations. They concluded that sublingual capnometry was a reliable method for diagnosis and quantitation of severity of cir- Current experience with sublingual partial pressure culatory failure in humans. of carbon dioxide measurement Marik [56] also measured PslCO2 in hemodynamically unstable patients during the first 24 h of ICU admission. Experimental studies Initial DPsl-aCO2 values were statistically higher in non- survivors than in survivors but the PslCO2 values were The first evidence that sublingual capnometry may be not, suggesting that DPsl-aCO2 is a better prognostic factor useful in the diagnosis and quantitation of circulatory than PslCO2. In a similar study design, Rackow and co- shock came from the work of Nakagawa et al. [52]. These workers [57] also found higher DPsl-aCO2 in non-sur- investigators observed, during hemorrhagic and septic vivors than in survivors, but this time measured at 24 h shock in rats, that changes in PslCO2 were parallel to after the start of the study. These authors observed that the changes in PgCO2 and systemic markers of hypoperfu- correlation between PslCO2 and the other indexes of tissue 2160 162 A.T. Maciel, J. Creteur and J.-L. Vincent
Table 1 Summary of clinical studies using sublingual capnometry
Author(s)/year Number of Diagnosis Time of PslCO2 measurement PslCO2/DPsl-aCO2 survivors, p value patients non-survivors
Weil et al, 46 21 trauma ICU, ER or TS admission, PslCO2 (admission), 58.4€11.3, <0.001 1999 [55] 14 infection every 30 min, (total 6 h) 92.6€26.6 6 cardiac emergency 5 miscellaneous Marik, 2001 22 15 severe sepsis/septic ICU admission, every 4–6 h, DPsl-aCO2 (admission), 9.2€5.0, 0.04 [56] shock (total 24 h) 17.8€11.5 7 cardiogenic shock Rackow et al, 25 19 sepsis 0, 1, 3, 6, 12, 24 h after Swan- DPsl-aCO2 (at 24 h), 14€3, 29€4 <0.05 2001 [57] 6 cardiac failure Ganz insertion Marik and 54 21 severe sepsis/septic 0, 4, 8 h after Swan-Ganz DPsl-aCO2 (at the time of Swan- 0.0004 Bankov, 2003 shock insertion Ganz insertion), 19.0€12.8, [7] 9 cardiogenic shock 35.3€18.3 8 major abdominal surgery 8 polytrauma 5 hypovolemic shock 3 severe pancreatitis
PslCO2 sublingual partial pressure of carbon dioxide, DPsl-aCO2 sublingual-arterial partial pressure of carbon dioxide gradient, ICU intensive care unit, ER emergency room, TS trauma service
Table 2 Well-established facts, Well-established 1. PslCO2 depends on PaCO2, sublingual tissue CO2 production and regional limitations and unanswered facts blood flow questions about sublingual cap- 2. Low blood flow is the main determinant of CO accumulation in tissues nometry 2 3. Measurement of PslCO2 is non-invasive and easily obtained in cooperative or sedated patients 4. High DPsl-aCO2 values in critically ill patients predict a poor prognosis Limitations and 1. Current physiological concepts preclude DPsl-aCO2 as a sensitive and specific questions to be marker of dysoxia answered 2. Possible differences in DPsl-aCO2 patterns in hypodynamic and hyperdynamic shock 3. Cut-off values between normal and pathological values are hard to define 4. DPsl-aCO2-guided therapy has not yet been shown to be beneficial
PslCO2 sublingual partial pressure of carbon dioxide, PaCO2 arterial partial pressure of carbon dioxide, CO2 carbon dioxide, DPsl-aCO2 gradient between PslCO2 and PaCO2
perfusion was greater in patients with cardiac failure than DPsl-aCO2 seems to be mainly determined by sublingual with sepsis. Marik and Bankov [7] recently confirmed microcirculatory blood flow. that DPsl-aCO2 is a good outcome predictor. They ob- served that patients with an initial DPsl-aCO2 higher than 25 mmHg have a high mortality rate. In their study, de- Limitations, controversies and unanswered questions spite optimization of traditional hemodynamic end points, the DPsl-aCO2 decreased but remained higher in the non- With the currently available data on sublingual capnom- survivors than in the survivors. When they excluded DPsl- etry, some questions (Table 2) remain and need proper aCO2 from the analysis, PslCO2 became the most signif- evaluation and consideration. icant predictor of outcome by multivariate analysis. Based on this, they concluded that, in their study, PslCO2 alone might be suitable for management, obviating the need for Drawbacks of tissue partial pressure of carbon dioxide blood gas analysis to calculate DPsl-aCO2. measurement in the sublingual mucosa By simultaneously monitoring PslCO2 with Capno- Probe and sublingual microcirculation with the use of Although more practical than the stomach for measure- the Orthogonal Polarization Spectral imaging technique ment of tissue PCO2, some potential disadvantages need (Cytoscan, Cytometrics, Philadelphia, PA, USA), our to be discussed. First, since tactile stimuli can increase group was able to demonstrate a significant correlation sublingual blood flow and production of saliva, the between PslCO2 and the percentage of perfused sublingual presence of the device itself under the tongue can increase capillaries in 12 septic shock patients [63, 64]. Hence, sublingual blood flow. Most acutely ill patients are not 2161 Tissue capnometry 163
Fig. 1 Results from a 73-year- old woman admitted to the ICU with subarachnoid hemorrhage. Cardiac output was felt to be inadequate in the presence of an increased arterial lactate con- centration and a high PslCO2 (around 60 mmHg). Mean arte- rial pressure (MAP), cardiac output (CO), mixed venous oxygen saturation (SvO2) and sublingual PCO2 (PslCO2) were continuously monitored. A fluid challenge resulted in increases in MAP, CO, and SvO2 and decreases in PslCO2 . Since ar- terial PCO2 remained constant (38 mmHg), decreases in the sublingual-arterial PCO2 gradi- ent (DPsl-aCO2) were equally significant. Arterial lactate concentration normalized in the subsequent hours
fed orally so that the direct interference of food on sub- analysis, including the pitfalls of the temperature cor- lingual measurement is not a major problem, as it is for rection of blood gases. Since sublingual and arterial PCO2 gastric tonometry. However, enteral feeding could theo- are measured by different equipment and at different retically interfere indirectly with sublingual blood flow temperatures, a methodological error may be introduced through reflex mechanisms, as previously mentioned. It [66]. is important to remember that the sublingual mucosa is sometimes used for drug administration but this should be avoided during sublingual PCO2 monitoring. In addition, Normal values of sublingual partial pressure CO2 production by bacteria of the oral flora and inter- of carbon dioxide ference of saliva and its composition as well as vomitus in the measurement of the PslCO2 value are potential areas There is no large study evaluating the normal value of of concern, but their effects are probably negligible. PslCO2. Weil et al. [55] measured PslCO2 in five healthy The devices clinically available for PslCO2 measure- human volunteers with the MI-720 CO2 electrode and the ment measure the value intermittently. However, since range was from 43 to 47 mmHg. PslCO2 seems to respond fast to changes in hemodynamic conditions, intermittent measurements are not very prac- tical for use in critically ill patients. For this reason, a Sublingual partial pressure of carbon dioxide system that measures PslCO2 continuously would be more measurement in different types of shock appropriate. This system has already been developed (CapnoProbe SL Model 2000 Sensor; Optical Sensor, Most experimental studies on sublingual capnometry have MN, USA) but is still not clinically available. Fig. 1 included hypodynamic types of circulatory shock. Even in shows an example of the use of this device in a single models of septic shock, the cardiac index started to fall at patient. the beginning of the experiment [52]. This has been a Another important aspect of the measurement of tissue limitation of models using a bolus intravenous injection of PCO2 in the sublingual mucosa is that, since it is not part bacteria (or endotoxin) [67]. Most of the clinical studies of the splanchnic area, elevations in PslCO2 may not occur did not evaluate different types of shock separately [7, 55, as fast as in the stomach in progressive shock states. 56], yet it is possible that different types of shock modify Hence, it may not serve as a “canary of the body” [65]. In PslCO2 values in different ways. This may also contribute addition, PslCO2 should always be interpreted in relation to the variability in the correlations between PslCO2 and to the arterial PCO2. This latter measurement is subject to other markers of tissue perfusion in the various studies, as bias and imprecisions related to blood gas sampling and suggested by Rackow et al. [57]. 2162 164 A.T. Maciel, J. Creteur and J.-L. Vincent
Fig. 2 Results from a 20-year- old man admitted to the ICU with fulminant hepatic failure and severe sepsis, showing a hyperdynamic status. A Cardiac output (CO) and mixed venous oxygen saturation (SvO2) were recorded every 5 min. Note the progressive increase in CO and oral temperature (arrows) with a stable SvO2. B Continuous sublingual PCO2 (PslCO2) monitoring and intermittent sublingual-arterial PCO2 gradi- ent (DPsl-aCO2) measurement. Note that although CO in- creased, PslCO2 and DPsl-aCO2 also increased. Arterial lactate concentration was around 2 mmol/l and mean arterial pressure around 65–70 mmHg (no vasoactive agent) through- out the monitoring period. The clinical condition deteriorated in the hours after the end of the monitoring period progressing to septic shock (fungal in ori- gin) and multiple organ failure. The patient died 2 days later
What is the behavior of sublingual partial pressure flow; adequate perfusion, although essential, is not always of carbon dioxide in hyperdynamic sepsis? a guarantee of normal aerobic cell metabolism, especially in sepsis. We have reported high values of PslCO2 in hemody- namically stabilized septic shock patients [63, 64], even when cardiac output increased (Fig. 2). The most feasible Should treatment be guided by gradients explanation for increases in DPsl-aCO2 despite increases in between sublingual partial pressure of carbon dioxide systemic blood flow is compromised microvascular blood and arterial partial pressure of carbon dioxide? flow in patients with sepsis [68–71], including in the sublingual mucosa [63, 72]. Low microvascular blood No study exists on the efficacy of DPsl-aCO2-guided flow may occur despite high systemic blood flow due to therapy. A high value for DPsl-aCO2 suggests a mismatch shunts in “weak microcirculatory units” [73, 74] and this between blood flow (especially in the microcirculation) is mainly responsible for CO2 accumulation and increases and oxygen demand in all types of shock, a situation that in PslCO2 despite the presence of a high cardiac index. usually precedes the occurrence of dysoxia itself and Distributive abnormalities of macrocirculatory and mi- multiple organ failure. However, care must be taken since crocirculatory blood flow play a key role in the impair- the literature already has good examples of very pro- ment of sepsis-related oxygen extraction [75] and, prob- mising monitoring techniques, such as pHi measurement, ably, also in tissue CO2 accumulation. PslCO2 seems to which, although useful as a prognostic index [76, 77], is correlate well with the microcirculatory alterations re- still controversial as a therapeutic guide, having been ported in sepsis [63, 64], so it could be used as a reliable shown to be beneficial in some studies [18, 78, 79], but marker to quantify these alterations. not in others [80, 81]. Since interpretation of DPsl-aCO2 is It is reasonable to speculate that in all types of shock, not always easy to achieve, the best approach at this even in hyperdynamic sepsis, compromised blood flow moment is to analyze its value in conjunction with the and impairment in tissue perfusion are a common end traditional hemodynamic parameters in current use. point. Hence, tissue PCO2 is expected to increase in all these situations, whatever the etiology or mechanism. However, dysoxia may occur despite maintained blood 2163 Tissue capnometry 165
Conclusion terpretation is not always easy to achieve since some variables can potentially interfere with the measurement, Sublingual capnometry has emerged in recent years as even when it is made in the sublingual mucosa; (b) the a promising technique for non-invasive monitoring of sublingual mucosa may not be as susceptible to ischemia hemodynamic disturbances. Experimental and clinical as the gastrointestinal tract, so that it may not be com- studies have indicated that: (a) acute and severe reduc- promised so early in progressive shock states; (c) there tions in blood flow are associated with significant PCO2 may be differences in PslCO2 kinetics in different types elevation in virtually all tissues; (b) sublingual tissue is a of shock; (d) the absence of a “gold standard” monitor potential site for measurement of PCO2 non-invasively, of dysoxia to compare with; (e) no well-established which is the great advantage of this method; (c) PaCO2 normal and pathological DPsl-aCO2 values; and (f) it is must be taken into account when interpreting PslCO2; (d) still uncertain if correction of DPsl-aCO2 improves prog- higher PslCO2 values and, more specifically, higher DPsl- nosis. Nevertheless, since PslCO2 measurement is tech- aCO2 values correlate with altered sublingual microcir- nically simple and non-invasive, new studies should culatory blood flow and an increased risk of death in be encouraged to define the precise role of sublingual critically ill patients. PCO2 measurement in the management of critically ill With our current knowledge, some questions and patients. limitations are still present: (a) correct tissue PCO2 in-
References
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Abstract Background: Early hemo- sociated with an increase in capillary dynamic assessment of global pa- refill time. The temperature gradients rameters in critically ill patients fails peripheral-to-ambient, central-to-pe- to provide adequate information on ripheral and forearm-to-fingertip skin tissue perfusion. It requires invasive are validated methods to estimate monitoring and may represent a late dynamic variations in skin blood intervention initiated mainly in the flow. Commonly used optical meth- intensive care unit. Noninvasive ods for peripheral monitoring are monitoring of peripheral perfusion perfusion index, near-infrared spec- can be a complementary approach troscopy, laser Doppler flowmetry that allows very early application and orthogonal polarization spec- throughout the hospital. In addition, troscopy. Continuous noninvasive This study was in part supported by mate- as peripheral tissues are sensitive to transcutaneous measurement of oxy- rials provided by Hutchinson Technology alterations in perfusion, monitoring gen and carbon dioxide tensions can and a grant from Philips USA. Both authors of the periphery could be an early be used to estimate cutaneous blood received a grant US $12,000 from Philips USA and $10,000 from Hutchinson Tech- marker of tissue hypoperfusion. This flow. Sublingual capnometry is a nology. review discusses noninvasive meth- noninvasive alternative for gastric ods for monitoring perfusion in pe- tonometry. ripheral tissues based on clinical signs, body temperature gradient, Keywords Body temperature optical monitoring, transcutaneous gradient · Hemodynamic assessment · oximetry, and sublingual capnometry. Noninvasive monitoring · Peripheral Discussion: Clinical signs of poor tissue perfusion · Sublingual peripheral perfusion consist of a cold, capnometry · Transcutaneous pale, clammy, and mottled skin, as- oximetry
Introduction the microcirculation [1, 2, 3]. In addition, it often requires invasive monitoring techniques that usually limit early An important goal of hemodynamic monitoring is the initiation, typically after the patient has been admitted to early detection of inadequate tissue perfusion and oxy- the intensive care unit (ICU). genation to institute prompt therapy and guide resuscita- To address these limitations there have been many tion, avoiding organ damage. In clinical practice tissue attempts to perform measurements of blood flow and oxygenation is frequently assessed by using conventional oxygenation in peripheral tissues [4, 5]. In circulatory global measurements such as blood pressure, oxygen failure blood flow is diverted from the less important derived variables, and blood lactate levels. However, the tissues (skin, subcutaneous, muscle, gastrointestinal tract) assessment of global hemodynamic parameters fails to to vital organs (heart, brain, kidneys). Thus monitoring reflect increased blood lactate levels, the imbalance be- perfusion in these less vital tissues could be an early tween oxygen demand and oxygen supply, or the status of marker of vital tissue hypoperfusion. Second, the assess-
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 169 DOI: 10.1007/978-3-642-01769-8_32, © Springer-Verlag Berlin Heidelberg 2009 1317 170 A. Lima and J. Bakker ment of perfusion in peripheral tissues is more easily obtainable using noninvasive monitoring techniques, thus FCD gradient facilitating earlier initiation. Tc-index Monitoring of peripheral perfusion and oxygenation 2 ; does not need any intravascular catheter, transesophageal oxygen partial 2 probe insertion, blood component analysis or penetration 2 Psl-aCO of the skin. Also, it can be performed directly (clinical , 2 evaluation and body temperature gradient) or by signal PtcO processing (optical monitoring; transcutaneous oximetry; sublingual capnometry). This review discusses several available noninvasive methods to monitor peripheral perfusion and oxygenation (Table 1). orthogonal polarization spectroscopy, Clinical assessment sublingual tissue PCO 2 OPS Laser Doppler flowmetry, ) , 2 During circulatory failure the global decrease in oxygen 3 PslCO aa carbon dioxide partial pressure in the skin,
supply and redistribution of blood flow caused by in- LDF creased vasoconstriction results in decreased perfusion in 2 Necessity to frequently changerequires the blood sensor gas position; analysis Requires specific software to display the variables Requires blood gas analysis to obtain PaCO Limitations Not accurate during patient motion Observer-related bias; semiquantitative measure of perfusion normal and pathological values not yet defined organ systems. Some organs, including the brain, heart, Difficult interpretation in distributive shock At least two temperaturethe probes variations required; in does real not time reflect Small sampling volume forment; cutaneous does blood not flow reflect measure- heterogeneity of blood flow and kidney, have vasomotor autoregulation that maintains PtcCO cytochrome
blood flow in low blood pressure states. However, the and arterial PCO 3 cutaneous circulation is deprived of autoregulation, and 2
the sympathetic neurohumoral response predominates, Cytaa resulting in a decrease in skin perfusion and temperature in these conditions. Skin temperature is measured using the dorsal surface of the examiner hands or fingers be- between PslCO pressure in the skin, functional capillary density, saturation, cause these areas are most sensitive to temperature per- transcutaneous oxygen index, ; early detection 2 noninvasively
ception. Patients are considered to have cool extremities if 2 all examined extremities are cool to the examiner, or only PFI /PtcCO
the lower extremities are cool despite warm upper ex- 2 tremities, in the absence of peripheral vascular occlusive
disease. Clinical signs of poor peripheral perfusion consist tissue oxygen capillary refill of a cold, pale, clammy, and mottled skin, associated with 2 deoxygenated he- StO
an increase in capillary refill time. In particular, skin CRT temperature gradient temperature and capillary refill time have been advocated Hb as a measure of peripheral perfusion [6, 7, 8, 9, 10, 11].
Capillary refill time (CRT) has been introduced into dTp-a the assessment of trauma, and a value less than 2 s is considered normal [12]. This is based on the assumption of peripheral hypoperfusion Assessment of oxygenation incan all be vascular applied compartments; toconsumption measure regional blood flow and oxygen Direct measurement of PtcO Direct measurement of tissue PCO Advantage Easily obtainable; reflect realflow time changes in peripheral blood Direct visualization of the microcirculation Depends only on physicalfor examination; hemodynamic valuable monitoring adjunct in circulatory shock Validated method to estimateflow dynamic variations in skin blood Useful method to evaluateresponses endothelium-dependent vascular that a delayed return of a normal color after emptying the total hemoglobin, capillary bed by compression is due to decreased pe- ripheral perfusion. CRT has been validated as a measure HbT of peripheral perfusion with significant variation in chil- 2 dren and adults. Schriger and Baraff [8] in a study on a Near-infrared spectroscopy, forearm-to-fingertip skin-temperature gradient, , and HbT 2
normal population reported that CRT varied with age and 2 2 /PtcCO 3 sex. It was found that a CRT of 2 s was a normal value for NIRS 2 most young children and young adults, but the lowest 2 Tskin-diff Tc-index PslCO StO variations Cytaa Variable FCD Psl-aCO skin CRT dTc-p dTp-a Tskin-diff Hb, HbO Microvascular blood flow CRT was substantially higher in healthy women (2.9 s) PtcO and in the elderly (4.5 s). Using these normal variations it oxygenated hemoglobin,
was further shown that a prolonged CRT did not predict a 2
450-ml blood loss in adult blood donors or hypovolemic temperature gradient central-to-peripheral, HbO
states in patients admitted to the emergency room [10]. Measurement methods to study peripheral perfusion (
Several clinical studies have reported a poor correlation dTc-p between CRT, heart rate, blood pressure, and cardiac peripheral perfusion index, time, peripheral-to-ambient, Sublingual capnometry moglobin, Table 1 Method OPS Body temperature gradient Pulse oximetry PFI Clinical assessment Warmth and coolness NIRS LDF output [6, 7, 10]. However, prolonged CRT in pediatric Transcutaneous oximetry 1318 Noninvasive monitoring of peripheral perfusion 171 patients has been found to be a good predictor of dehy- and the heat conduction from the core decreases, and dration, reduced stroke volume, and increased blood therefore the central temperature rises and the dTc-p in- lactate levels [6, 11]. In adult patients following cardiac creases. A gradient of 3–7 C occurs in patients with stable surgery no significant relationship between cardiac index hemodynamics [19]. Hypothermia, cold ambient temper- and CRT was found during the first 8 h following ICU ature (<20 C) [20], and vasodilatory shock limits the use admission [7]. of dTc-p as an estimate of peripheral perfusion. Forearm- Distal extremity skin temperature has also been related to-fingertip skin-temperature gradient (Tskin-diff) has to the adequacy of the circulation. Kaplan et al. [9] also been used as an index of peripheral circulation to compared distal extremity skin temperature (evaluated by identify the initiation of thermoregulatory vasoconstric- subjective physical examination) with biochemical and tion in patients following surgery [21]. Fingertip tem- hemodynamic markers of hypoperfusion in adult ICU perature is measured with the temperature probe attached patients. This study found that patients with cold pe- to the ventral face of the finger. The use of Tskin-diff is riphery (including septic patients) had lower cardiac based on assumption that the reference temperature is a output and higher blood lactate levels as a marker of more skin site exposed to the same ambient temperature as the severe tissue hypoxia. In another study Hasdai et al. [13] fingertip. It has been applied in conditions where an showed the importance of the physical examination in ambient temperature is not stable, such as in patients determining the prognosis of patients with cardiogenic undergoing surgery [21, 22, 23]. A change in ambient shock. This study reported the presence of a cold and temperature therefore affects similarly forearm and fin- clammy skin to be an independent predictor of 30-day gertip temperature, producing little influence in the gra- mortality in patients with cardiogenic shock complicating dient. Basically, when vasoconstriction decreases finger- acute myocardial infarction. tip blood flow, finger skin temperature decreases, and The findings of these studies show that skin tempera- Tskin-diff increases. Experimental studies have suggested ture together with CRT are a valuable adjunct in hemo- a Tskin-diff threshold of 0 C for the initiation of vaso- dynamic monitoring during circulatory shock, and should constriction, and a threshold of 4 C for severe vasocon- be the first approach to assess critically ill patient. Not striction in anesthetized patients [22, 23]. much is known about the clinical applicability of these The body temperature gradient was first applied to variables after the patient has been admitted to the in- assess patients with circulatory shock and to differentiate tensive care unit [14]. central heat retention caused by fever from peripheral vasoconstriction [15, 16, 24]. A number of studies have examined the correlation between body temperature gra- Temperature gradients dient and global hemodynamic variables in hypovolemic, septic and cardiogenic shock, but these have produced Since Joly and Weil [15] and Ibsen [16] studied the toe conflicting results [15, 25, 26, 27, 28, 29, 30, 31]. Hen- temperature as an indicator of the circulatory shock, body ning et al. [28] studied dTp-a in patients with circulatory temperature gradients have been used as a parameter of failure associated with hypovolemia and low cardiac peripheral perfusion. In the presence of a constant envi- output. An increase in dTp-a to more than 4–6 C over ronmental temperature a change in the skin temperature is 12 h was observed in survivors, and a good relationship the result of a change in skin blood flow [17]. The tem- between the lowest dTp-a and the highest blood lactate perature gradients peripheral-to-ambient (dTp-a) and levels was found in hypovolemic patients at time of ad- central-to-peripheral (dTc-p) can better reflect cutaneous mission. In assessing the potential value of dopamine as a blood flow than the skin temperature itself. Considering a therapeutic agent to treat circulatory shock Ruiz et al. [25] constant environment condition, dTp-a decreases and showed that survival is associated with an increase in dTc-p increases during vasoconstriction. The peripheral dTp-a of more than 2 C, and that dTp-a is correlated to skin temperature is measured using a regular temperature increases in cardiac output and a reduction in blood lac- probe attached to the ventral face of the great toe. This tate levels. In examining the value of dTp-a for assessing site is more convenient for peripheral temperature mea- peripheral perfusion in cardiogenic shock Vincent et al. surement because of the negligible local heat production [27] found that a cardiac index below 1.8 l/min 1 m 2 is and the distal location from other monitoring devices associated with a decrease in dTp-a below 5 C, and that [18]. The concept of the dTc-p is based on the transfer of the increase in dTp-a occurs earlier than the increase in heat from the body core to the skin. The heat conduction skin oxygen partial pressure during recovery; this corre- to the skin by the blood is also controlled by the degree of lation was not found in septic shock. No relationship has vasoconstriction of the arterioles and arteriovenous been observed between dTc-p and cardiac output in adults anastomoses. High blood flow causes heat to be con- with diverse causes of shock [31] or in children after open ducted from the core to the skin, whereas reduction in heart surgery [26, 29, 30]. One reason for the inaccurate blood flow decreases the heat conduction from the core. relationship between body temperature gradient and During vasoconstriction the temperature of the skin falls global hemodynamic parameters could be related to an 1319 172 A. Lima and J. Bakker unstable environment, as skin temperature depends also on ambient temperature, and the thermoregulatory re- sponse is suppressed in anesthetized patients [32]. In addition, global hemodynamic parameters may not be sensitive enough to reflect changes in peripheral blood flow in critically ill patients [33, 34]. Tskin-diff may be an alternative, but its use in these conditions has not yet been defined.
Optical monitoring
Optical methods apply light with different wave lengths directly to tissue components using the scattering char- acteristics of tissue to assess various states of these tissues [35]. At physiological concentrations the molecules that absorb most light are hemoglobin, myoglobin, cyto- chrome, melanins, carotenes, and bilirrubin. These sub- stances can be quantified and measured in intact tissues using simple optical methods. The assessment of tissue Fig. 1 The pulsation of arterial blood causes a pulsating volume variation. Peripheral perfusion index (PFI) is calculated as the ratio oxygenation is based on the specific absorption spectrum between the arterial pulsatile component (IP) and the nonpulsatile of oxygenated hemoglobin (HbO2), deoxygenated hemo- component (INP). I0 Source light intensity; I light intensity at the globin (Hb) and cytochrome aa3 (cytaa3). Commonly detector used optical methods for peripheral monitoring are per- fusion index, near-infrared spectroscopy, laser-Doppler flowmetry, and orthogonal polarization spectral. calculated as the ratio between the pulsatile component (arterial compartment) and the nonpulsatile component (other tissues) of the light reaching the detector of the Peripheral perfusion index pulse oximetry, and it is calculated independently of the patient’s oxygen saturation (Fig. 1). A peripheral perfu- The peripheral perfusion index (PFI) is derived from the sion alteration is accompanied by variation in the pulsatile photoeletric plesthysmographic signal of pulse oximetry component, and because the nonpulsatile component does and has been used as a noninvasive measure of peripheral not change, the ratio changes. As a result the value dis- perfusion in critically ill patients [36]. Pulse oximetry is a played on the monitor reflects changes in peripheral monitoring technique used in probably every trauma, perfusion. critically ill and surgical patient. The principle of pulse Studies with body temperature gradient suggest that oximetry is based on two light sources with different PFI can be a direct indicator of peripheral perfusion. A wavelengths (660 nm and 940 nm) emitted through the PFI of 1.4 has been found to be correlated best with hy- cutaneous vascular bed of a finger or earlobe. The Hb poperfusion in critically ill patients using normal values absorbs more light at 660 nm and HbO2 absorbs more in healthy adults [36]. A good relationship between light at 940 nm. A detector at the far side measures the Tskin-diff and PFI is observed in anesthetized patients to intensity of the transmitted light at each wavelength, and identify the initiation of thermoregulatory vasoconstric- the oxygen saturation is derived by the ratio between the tion [37]. The PFI reflects changes in dTc-p and Tskin- red light (660 nm) and the infrared light (940 nm) ab- diff and therefore vascular reactivity in adult critically ill sorbed. As other tissues also absorb light, such as con- patients [36, 38]. Another study has shown that PFI can be nective tissue, bone, and venous blood, the pulse oximetry used to predict severity of illness in neonates, with a distinguishes the pulsatile component of arterial blood cutoff value of1.24 [39]. The inclusion of PFI into the from the nonpulsatile component of other tissues. Using a pulse oximetry signal is a recent advance in clinical two-wavelength system the nonpulsatile component is monitoring. However, more studies are needed to define then discarded, and the pulsatile component is used to its clinical utility. calculate the arterial oxygen saturation. The overall he- moglobin concentration can be determined by a third wavelength at 800 nm, with a spectrum that resembles Near-infrared spectroscopy that of both Hb and HbO2. The resulting variation in in- tensity of this light can be used to determine the variation Near-infrared spectroscopy (NIRS) offers a technique for in arterial blood volume (pulsatile component). The PFI is continuous, noninvasive, bedside monitoring of tissue 1320 Noninvasive monitoring of peripheral perfusion 173
Fig. 2 A Diagram of a distal tip of the NIRS optical cable. B With 25 mm spacing (d) between emission and detection probes, approx. 95% of the detected optical signal is from 23 mm of tissue penetration oxygenation. As with pulse oximetry, NIRS uses the principles of light transmission and absorption to measure the concentrations of hemoglobin, oxygen saturation (StO2), and cytaa3 noninvasively in tissues. NIRS has a greater tissue penetration than pulse oximetry and pro- vides a global assessment of oxygenation in all vascular compartments (arterial, venous, and capillary). Tissue penetration is directly related to the spacing between il- lumination and detection fibers. At 25 mm spacing ap- prox. 95% of the detected optical signal is from a depth of 0 to 23 mm (Fig. 2). NIRS has been used to assess forearm skeletal muscle oxygenation during induced re- active hyperemia in healthy adults and produces repro- ducible measurements of tissue oxygenation during both Fig. 3 Quantitative NIRS measurements during arterial occlusion. After release of the occluding cuff blood volume increases rapidly, arterial and venous occlusive events [40]. Using the ve- resulting in an increase in HbO2 and a quick washout of Hb, fol- nous and arterial occlusion methods NIRS can be applied lowed by a hyperemic response. Oxygen consumption is calculated to measure regional blood flow and oxygen consumption as the rate of decrease in HbO2 (dotted line) by following the rate of HbO2 and Hb changes [40, 41, 42]. In the venous occlusion method a pneumatic cuff is inflated to a pressure of approx. 50 mmHg. Such a pres- during hypoxemia. The absorption spectrum of cytaa3 in sure blocks venous occlusion but does not impede arterial its reduced state shows a weak peak at 70 nm, whereas the inflow. As a result venous blood volume and pressure oxygenated form does not. Therefore monitoring changes increase. NIRS can reflect this change by an increase in in its redox state can provide a measure of the adequacy HbO2, Hb, and total hemoglobin. In arterial occlusion of oxidative metabolism. Despite the potential clinical method, the pneumatic cuff is inflated to a pressure of applications of NIRS, some limitations still exist. The approx. 30 mmHg greater than systolic pressure. Such a contribution of the cytaa3 signal is small, and its inter- pressure blocks both venous outflow and arterial inflow. pretation remains controversial, requiring more rigorous Depletion of local available O2 is monitored by NIRS as a development [43]. There is no a gold standard to which decrease in HbO2 and a simultaneous increase in Hb, NIRS data can be directly compared, and one of the whereas total Hb remains constant. After release of the reasons is that a variety of NIRS equipment is commer- occluding cuff a hyperemic response is observed (Fig. 3). cially available with different working systems. Blood volume increases rapidly, resulting in an increase In both small- and large-animal models of hemorrhagic in HbO2 and a quick washout of Hb. In addition to blood shock and resuscitation NIRS has demonstrated sensitiv- flow and evaluation of HbO2 and Hb changes, NIRS can ity in detecting skeletal muscle and visceral ischemia [44, assess cytaa3 redox state. Cytaa3 is the final receptor in 45, 46, 47]. As a noninvasive measure of peripheral the oxygen transport chain that reacts with oxygen to perfusion NIRS has been applied in superficial muscles form water, and approx. 90% of cellular energy is derived (brachioradialis muscle, deltoid muscle, tibialis anterior) from this reaction. Cytaa3 remains in a reduced state of trauma ICU patients to monitor the adequacy of tissue 1321 174 A. Lima and J. Bakker
Fig. 4 OPS optical schematic. A The light passes through the first polarizer and is reflected back through the lens. B The polarized light reflecting from the surface is eliminated, and the depolarized light forms an image of the microcirculation on a videocamera (charge-cou- pled device, CCD)
oxygenation and detect a compartment syndrome [48, 49, Orthogonal polarization spectral 50, 51, 52]. The use of NIRS in deltoid muscle during resuscitation of severe trauma patients has recently been Orthogonal polarization spectral (OPS) is a noninvasive reported [48, 49]. Cairns et al. [49] studied trauma ICU technique that uses reflected light to produce real-time patients and reported a strong association between ele- images of the microcirculation. The technical character- vated serum lactate levels and elevated cytaa3 redox state istics of the device have been described elsewhere [54]. during 12 h of shock resuscitation and development of Light from a source passes through the first polarizer, and multiple organ failure. More recently Mckinley et al. [48] it is directed towards the tissue by a set of lens. As the showed a good relationship between StO2, systemic light reaches the tissue, the depolarized light is reflected oxygen delivery and lactate in severely trauma patients back through the lenses to a second polarizer or analyzer during and after resuscitation over a period of 24 h. A and forms an image of the microcirculation on the charge- recent study with septic and nonseptic patients used NIRS coupled device, which can be captured through a single to measure both regional blood flow and oxygen con- videotape (Fig. 4). The technology has been incorporated sumption after venous occlusion [53]. In this study septic into a small hand-held video-microscope which can be patients had muscular oxygen consumption twice that of used in both research and clinical settings. OPS can assess nonseptic patients, but oxygen extraction was similar in tissue perfusion using the functional capillary density both groups, emphasizing oxygen extraction dysfunction (FCD), i.e., the length of perfused capillaries per obser- in sepsis. Another study observed no relationship between vation area (measured as cm/cm2). FCD is a very sensi- forearm blood flow, measured by NIRS, and systemic tive parameter for determining the status of nutritive vascular resistance in septic shock patients [41]. These perfusion to the tissue and it is an indirect measure of findings demonstrate the ability of NIRS to reflect mi- oxygen delivery. One of the most easily accessible sites in crocirculatory dysfunction in skeletal muscle in septic humans for peripheral perfusion monitoring is the mouth. shock. The potential to monitor regional perfusion and OPS produces excellent images of the sublingual micro- oxygenation noninvasively at the bedside makes clinical circulation by placing the probe under the tongue. application of NIRS technology of particular interest in Movement artifacts, semiquantitative measure of perfu- intensive care. sion, the presence of various secretions such as saliva and blood, observer-related bias, and inadequacy of sedation 1322 Noninvasive monitoring of peripheral perfusion 175 to prevent patients from damaging the device are some of the limitations of the technique. The use of sublingual tissues with OPS provides in- formation about the dynamics of microcirculatory blood flow, and therefore it can monitor the perfusion during clinical treatment of circulatory shock. It has been used to monitor the effects of improvements in microcirculatory blood flow with dobutamine and nitroglycerin in volume resuscitated septic patients [55, 56]. OPS has been applied in the ICU to study the properties of sublingual micro- circulation in both septic shock and cardiogenic shock [2, 56, 57, 58]. In septic patients it has been shown with OPS that microvascular alterations are more severe in patients with a worse outcome, and that these microvascular al- terations can be reversed using vasodilators [2]. In pa- Fig. 5 Schematic diagram of laser Doppler flowmetry. When the tients with cardiac failure and cardiogenic shock the tissue is illuminated by a laser source (1), 93–97% of the light is number of small vessels and the density of perfused either absorbed by various structures or undergoes scattering (a, b). vessels are lower than in controls, and the proportion of The remaining 3–7% is reflected by moving red blood cells (c, d) and returns to the second optical fiber (2). Microvascular perfusion perfused vessels is higher in patients who survived than in is defined as the product of mean red blood cells (RBC) velocity patients who did not survive [57]. Using OPS during the and mean RBC concentration in the volume of tissue under illu- time course of treatment of patients with septic shock, mination from the probe Sakr et al. [58] demonstrated that the behavior of the sublingual microcirculation differs between survivors and nonsurvivors. Although alterations in the sublingual mi- such as diabetes mellitus, essential hypertension, athero- crocirculation may not be representative of other micro- sclerosis, and sepsis [61]. A major limitation of this vascular beds, changes in the sublingual circulation technique is that it does not take into account the het- evaluated by capnometry during hemorrhagic shock have erogeneity of blood flow as the velocity measurements been related to changes in perfusion of internal organs represent the average of velocities in all vessels of the such as the liver and intestine [59]. Thus OPS could be of window studied. In addition, skin blood flow signal varies use in the monitoring of tissue perfusion. markedly depending on probe position. No current laser Doppler instrument can present absolute perfusion values (e.g., ml/min per 100 g tissue) and measurements are Laser Doppler flowmetry expressed as perfusion units, which are arbitrary. LDF is useful in evaluating endothelium-dependent Laser Doppler flowmetry (LDF) is a noninvasive, con- vascular responses in the skin microcirculation during tinuous measure of microcirculatory blood flow, and it either reactive hyperemia [61, 62] or the noninvasive lo- has been used to measure microcirculatory blood flow in cal application of acetylcholine or sodium nitroprusside many tissues including neural, muscle, skin, bone, and [63, 64, 65]. This characteristic of LDF was used in intestine. The principle of this method is to measure the critically ill patients to evaluate endothelial dysfunction in Doppler shift—the frequency change that light undergoes sepsis. Observational studies have shown that the hyper- when reflected by moving objects, such as red blood cells. emic response in septic patients is decreased, and a rela- LDF works by illuminating the tissue under observation tionship between changes in vasculature tone and severity with a monochromatic laser from a probe. When the tis- of sepsis has been described [66, 67, 68]. In addition, sue is illuminated, only 3–7% is reflected. The remaining restored vasomotion in patients with sepsis evaluated by 93–97% of the light is either absorbed by various struc- LDF seems to be associated with a favorable prognosis tures or undergoes scattering. Another optical fiber col- [67]. The ability of LDF to assess abnormalities of skin lects the backscattered light from the tissue and returns it blood flow control in sepsis could be of clinical use for to the monitor (Fig. 5). As a result LDF produces an early detection of microcirculatory derangements in high- output signal that is proportional to the microvascular risk patients. perfusion [60]. Depending on the device and the degree of invasiveness it can be used to assess blood flow in mus- cle, gastric, rectal, and vagina mucosae. As a noninvasive PO2 and PCO2 transcutaneous measurements measure of peripheral blood flow, however, its use is limited to the skin [60]. LDF has been applied to obtain Continuous noninvasive measurement of oxygen and information on the functional state of the skin microcir- carbon dioxide tensions is possible because both gases culation during reactive hyperemia in several conditions, can diffuse through the skin, and thus their partial pres- 1323 176 A. Lima and J. Bakker sures can be measured in transcutaneous tissue. Normally patients with shock. These authors reported that at cardiac the skin is not very permeable to gases, but at higher index values higher than 2.2 l min 1 m 2 the tc-index temperatures the ability of the skin to transport gases is averages 0.79, at 1.5–2.2 l min 1 m 2 it is 0.48, and at improved. Oxygen sensors for transcutaneous electro- values lower than 1.5 l min 1 m 2 it is 0.12. However, the chemical measurements are based on polarography: a relationship between tc-index and cardiac index may not typical amperometric transducer in which the rate of a exist in hyperdynamic shock. Reed et al. [75] studied chemical reaction is detected by the current drained PtcO2 at different cardiac indices. In this study 71 mea- through an electrode. The sensor heats the skin to 43– surements were made in 19 patients, and a low tc-index 45 C. The skin surface oxygen tension is increased as a was seen in 71% of the patients with a cardiac index 1 2 result of three effects: (a) heating the stratum corneum higher than 4.2l min m . PtcO2 and PtcCO2 monitoring beyond 40 C changes its structure, which allows oxygen has been used as an early indicator of tissue hypoxia and to diffuse faster; (b) the local oxygen tension is increased subclinical hypovolemia in acutely ill patients [77, 78]. by shifting the oxygen dissociation curve in the heated Tatevossian et al. [78] studied 48 severely injured patients dermal capillary blood; and (c) by dermal capillary hy- during early resuscitation in the emergency department peremia. These transcutaneous sensors enable us directly and operating room. The sequential patterns of PtcO2 and to estimate arterial oxygen pressure (PaO2) and arterial PtcCO2 were described throughout initial resuscitation. carbon dioxide pressure (PaCO2), and it has been suc- Nonsurvivors had lower PtcO2 values and higher PtcCO2 cessfully used for monitoring PaO2 and PaCO2 in both values than survivors. These differences were evident neonates and in adults [69, 70, 71]. Newborn infant is even early after the patient’s arrival. The authors reported suitable because of its thin epidermal layer. However, in a critical tissue perfusion threshold of PtcO2 50 mmHg for adults the skin is thicker, and differences in the skin cause more than 60 min and PtcCO2 60 mmHg for more than the transcutaneous oxygen partial pressure (PtcO2)tobe 30 min. Patients who failed to avoid these critical lower than PaO2. The correlation between PtcO2 and thresholds had 89% to 100% mortality. This technology PaO2 also depends on the adequacy of blood flow. The has not gained widespread acceptance in clinical practice low blood flow caused by vasoconstriction during shock as the time needed for calibration limits its early use in overcomes the vasodilatory effect of PtcO2 sensor. This the emergency department, and critical PtcO2 and PtcCO2 causes a mild tissue hypoxia beneath the PtcO2 sensor. values have not been established. The lack of the PtcO2 ability to accurately reflect the PaO2 in low flow shock enables us to estimate cutaneous blood flow through the relationship between the two Sublingual capnometry variables. Some studies have suggested the use of a transcutaneous oxygen index (tc-index), i.e., the changes Measurement of the tissue-arterial CO2 tension gradient in PtcO2 relative to changes in PaO2 [69, 72, 73, 74, 75]. has been used to reflect the adequacy of tissue perfusion. When blood flow is adequate, PtcO2 and PaO2 values are The gastric and ileal mucosal CO2 clearance is been the almost equal, and the tc-index is close to 1. During low primary reference for measurements of regional PCO2 flow shock the PtcO2 drops and becomes dependent on gradient during circulatory shock [79]. The regional PCO2 the PaO2 value, and tc-index decreases. A tc-index greater gradient represents the balance between regional CO2 than 0.7 has been reported to be associated with hemo- production and clearance. During tissue hypoxia CO2 is dynamic stability [69, 72, 74, 75]. Transcutaneous carbon produced by hydrogen anions buffered by tissue bicar- dioxide partial pressure (PtcCO2) has been also used as an bonate, which adds to the amount of CO2 produced by index of cutaneous blood flow. Differences between normal oxidative metabolism. The amount of CO2 pro- PaCO2 and PtcCO2 have been explained by local accu- duced, either aerobically or because of tissue hypoxia, mulation of CO2 in the skin due to hypoperfusion. Be- will be cleared if blood flow is maintained. In low flow cause of the diffusion constant of CO2 is about 20 times states CO2 increases as a result of stagnation phenomenon greater than O2, PtcCO2 has been showed to be less [80]. Gastric tonometry is a technique that can be used to sensitive to changes in hemodynamics than PtcO2 [76]. assess the adequacy of gut mucosal blood flow to me- One of the main limitations of this technique is the ne- tabolism. The methodological limitations of gastric to- cessity of blood gas analysis to obtain the tc-index and nometry required a search for a tissue in which PCO2 can PaCO2. In addition, the sensor position must be changed be measured easily in a noninvasive approach. Compa- every 1–2 h to avoid burns. After each repositioning a rable decreases in blood flow during circulatory shock period of 15–20 min is required for the next readings, have been also demonstrated in the sublingual tissue which limits its use in emergency situations. PCO2 (PslCO2) [81, 82]. The currently available system The ability of PtcO2 to reflect tissue perfusion in for measuring PslCO2 consists of a disposable PCO2 critically ill adult patients has been applied using the tc- sensor and a battery powered handheld instrument. The index. Tremper and Shoemaker [72] found a good cor- instrument uses fiberoptic technology to transmit light relation (r=0.86) between tc-index and cardiac index in through the sensor placed between the tongue and the 1324 Noninvasive monitoring of peripheral perfusion 177 sublingual mucosa. Carbon dioxide diffuses across a this technique includes the necessity of blood gas analysis semipermeable membrane of the sensor and into a fluo- to obtain PaCO2. In addition, normal vs. pathological Psl- rescent dye solution. The dye emits light that is propor- aCO2 values are not well defined. tional to the amount of CO2 present. This light intensity is analyzed by the instrument and displayed as a numeric PslCO2 value. Conclusion Clinical studies have suggested that PslCO2 is a reli- able marker of tissue hypoperfusion [83, 84, 85, 86]. Weil The conventional systemic hemodynamic and oxygen- et al. [86] applied PslCO2 in 46 patients with acutely life ation parameters are neither specific nor sensitive enough threatening illness or injuries admitted to the emergency to detect regional hypoperfusion. In clinical practice a department or ICU. In this study 26 patients with physical more complete evaluation of tissue oxygenation can be signs of circulatory shock and high blood lactate levels achieved by adding noninvasive assessment of perfusion had higher PslCO2 values, and a PslCO2 threshold value in peripheral tissues to global parameters. Noninvasive of 70 mmHg was predictive for the severity of the cir- monitoring of peripheral perfusion could be a comple- culatory failure. Similarly as PCO2 in the gut mucosal, mentary approach that allows very early application PslCO2 is also influenced by PaCO2 [87]. Hence the throughout the hospital, including the emergency depart- gradient between PslCO2 and PaCO2 (Psl-aCO2) is more ment, operating room, and hospital wards. Such approach specific for tissue hypoperfusion. This was shown in the can be applied using both simple physical examination study by Marik and Bankov [85] who determined the and new current technologies, as discussed above. Al- prognostic value of sublingual capnometry in 54 hemo- though these methods may reflect variations in peripheral dynamic unstable critically ill patients. In this study Psl- perfusion with certain accuracy, more studies are needed aCO2 was a sensitive marker for tissue perfusion and a to define the precise role of such methods in the man- useful endpoint for the titration of goal-directed therapy. agement of the critically ill patients. Finally, evidence for Psl-aCO2 differentiated better than PslCO2 alone between clinical and cost effectiveness of these methods is an survivors and nonsurvivors, and a difference of more than important aspect that needs a formal technology assess- 25 mmHg indicated a poor prognosis. One limitation of ment.
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57. De Backer D, Creteur J, Dubois MJ, 68. Sair M, Etherington PJ, Peter WC, 78. Tatevossian RG, Wo CC, Velmahos Sakr Y, Vincent JL (2004) Microvas- Evans TW (2001) Tissue oxygenation GC, Demetriades D, Shoemaker WC cular alterations in patients with acute and perfusion in patients with systemic (2000) Transcutaneous oxygen and severe heart failure and cardiogenic sepsis. Crit Care Med 29:1343–1349 CO2 as early warning of tissue hypoxia shock. Am Heart J 147:91–99 69. Hasibeder W, Haisjackl M, Sparr H, and hemodynamic shock in critically ill 58. Sakr Y, Dubois MJ, De Backer D, Klaunzer S, Horman C, Salak N, Ger- emergency patients. Crit Care Med Creteur J, Vincent JL (2004) Persistent mann R, Stronegger WJ, Hackl JM 28:2248–2253 microcirculatory alterations are associ- (1991) Factors influencing transcutane- 79. Fiddian-Green RG, Baker S (1987) ated with organ failure and death in ous oxygen and carbon dioxide mea- Predictive value of the stomach wall pH patients with septic shock. 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Int Anesthesiol Clin 25:67–96 of tissue oxygenation in critically ill tylcholine and ultraviolet light. FASEB 75. Reed RL, Maier RV, Landicho D, patients. Crit Care Med 31:818–822 J 8:247–251 Kenny MA, Carrico CJ (1985) Corre- 86. Weil MH, Nakagawa Y, Tang W, Sato 65. Blaauw J, Graaff R, van Pampus MG, lation of hemodynamic variables with Y, Ercoli F, Finegan R, Grayman G, van Doormaal JJ, Smit AJ, Rakhorst G, transcutaneous PO2 measurements in Bisera J (1999) Sublingual capnometry: Aarnoudse JG (2005) Abnormal endo- critically ill adult patients. J Trauma a new noninvasive measurement for thelium-dependent microvascular reac- 25:1045–1053 diagnosis and quantitation of severity of tivity in recently preeclamptic women. 76. Tremper KK, Shoemaker WC, Shippy circulatory shock. Crit Care Med Obstet Gynecol 105:626–632 CR, Nolan LS (1981) Transcutaneous 27:1225–1229 66. Hartl WH, Gunther B, Inthorn D, PCO2 monitoring on adult patients in 87. Pernat A, Weil MH, Tang W, Yam- Heberer G (1988) Reactive hyperemia the ICU and the operating room. Crit aguchi H, Pernat AM, Sun S, Bisera J in patients with septic conditions. Sur- Care Med 9:752–755 (1999) Effects of hyper- and hypoven- gery 103:440–444 77. Waxman K, Sadler R, Eisner ME, Ap- tilation on gastric and sublingual PCO 67. Young JD, Cameron EM (1995) Dy- plebaum R, Tremper KK, Mason GR (2). J Appl Physiol 87:933–937 namics of skin blood flow in human (1983) Transcutaneous oxygen moni- sepsis. Intensive Care Med 21:669–674 toring of emergency department pa- tients. Am J Surg 146:35–38 François Jardin Ultrasonographic examination Antoine Vieillard-Baron of the venae cavae
We have thus proposed to use the SVC collapsibility index, calculated as maximal expiratory diameter minus minimal inspiratory diameter, divided by maximal expira- tory diameter, as an index of fluid responsiveness in me- chanically ventilated patients exhibiting circulatory fail- ure [4]. This requires recording of a long-axis view of the vessel using a multiplane transesophageal probe, by cou- pling motion mode with two-dimensional mode. Our mea- surements in a group of 66 patients with septic shock as reported in a previous issue, demonstrated that a SVC col- lapsibility index higher than 36% predicts a positive re- sponse to volume expansion, marked by a significant in- crease in Doppler cardiac output, with 90% sensitivity and 100% specificity [4]. We also found a bimodal distribu- There are two venae cavae in humans. The superior vena tion for the SVC collapsibility index: most patients exhib- cava (SVC) comprises the connection of the left and ited either a partial or complete collapse of the vessel or right brachiocephalic veins and ends on the top of the the absence of significant change in its diameter during in- right atrium, after entering the pericardium. The inferior flation. This confirms our hypothesis that the SVC can be vena cava (IVC) comprises the connection of the left and compared to a “Starling resistor” which obeys the all-or- right iliac veins and ends on the floor of right atrium, nothing law. after crossing the diaphragm. Whereas the SVC is an Ultrasonographic examination of the IVC can be per- intrathoracic vessel, the IVC is an intraabdominal one, its formed by a transthoracic, subcostal approach [5, 6]. Mea- short intrathoracic part being purely virtual. Both venae cavae provide venous return to the right heart, approx. 25% via the SVC and 75% via IVC [1, 2]. Ultrasonographic examination of the SVC can be performed by a transesophageal approach [3]. To remain open this collapsible vessel requires a distending pressure greater than the critical pressure producing collapse, i.e. its closing pressure. Because lung inflation increases pleural pressure more than right atrial pressure, the distending pressure of the SVC, i.e. right atrial pressure minus pleural pressure, is reduced by lung inflation, and may become insufficient to maintain the vessel open in a hypovolemic Fig. 1 Simultaneous recordings of tracheal pressure (T), pulmonary patient (Fig. 1). This collapsible vessel can be compared capillary wedge pressure (PCWP), right atrial pressure (RA), and esophageal pressure (E, as a surrogate for pleural pressure). During to a “Starling resistor.” The influence of SVC zone condi- lung inflation (inspiration) pleural pressure increases more than right tions on respiratory changes in SVC diameter is illustrated atrial (or central venous) pressure, leading to an inspiratory decrease with clinical examples in Fig. 2. in venous distending pressure (arrows)
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 181 DOI: 10.1007/978-3-642-01769-8_33, © Springer-Verlag Berlin Heidelberg 2009 204 182 F. Jardin and A. Vieillard-Baron
Fig. 2 Left Schematic representation of the superior vena cava (SVC) as a Starling resistor, with an inflow pressure (the upper body mean systemic pressure, MSP), an outflow pressure (the central venous pressure, itCVP), and an external pressure (the pleural pressure, Ppl). Right panel Cli nical examples illustrating the three zone conditions. Top panel (condition 1) Inflow pressure becomes lower than the pleural pressure during lung inflation, which produces a complete collapse of the whole vessel. This setting is illustrated by ultrasonographic examination of the venae cavae in a hypovolemic patient exhibiting low MSP. Middle panel (condition 2) the outflow pressure is reduced, and lung inflation produces a localized collapse at entry into the right atrium. This setting is illustrated (right) by ultrasonographic examination after clamping of the inferior vena cava during a surgical procedure, a maneuver which suddenly decreases CVP but does not change MSP. Bottom panel (condition 3) Outflow pressure is much greater than the external pressure, and the SVC remains fully open during lung inflation. This setting is illustrated (right) by ultrasonographic examination of the venae cavae after volume expansion
surement of IVC diameter in different positions has proven useful in separating normal subjects from patients with el- evated right atrial pressure [7]. In their famous study of venous return Guyton et al. [8] observed in dogs that neg- ative right atrial pressure from 0 down to –4 mm Hg in- creases venous return, but then beyond –4mm Hg, further increase in the negative pressure causes no more increase in the venous return. Guyton et al. explained this failure by the collapse of the IVC when entering the thoracic cavity, illustrating the inability of a collapsible vessel to transmit a negative pressure. To our knowledge, the first demon- stration of the reality of this phenomenon in humans was provided by our group in asthmatic patients [9] (Fig. 3).
Fig. 4 M mode echocardiography of the inferior vena cava (IVC) in a spontaneously breathing healthy volunteer (above)andiname- chanically ventilated patient (below). Cyclic changes in IVC diame- ters are opposite, the largest value being observed during expiration Fig. 3 An example of M mode echocardiography of the inferior vena in spontaneous breathing, and during inspiration in positive pressure cava (IVC) in spontaneously breathing asthmatic patients. Note the breathing short duration of inspiration, accompanied by a collapse of the ves- sel, and the increased duration of the expiration (compare Fig. 4, above) 205 Ultrasonographic examination of the venae cavae 183
30 2 spontaneous breathing these changes are abolished by vena cava dilatation produced by a high volume status, 25 and/or a high right atrial pressure, the inferior vena cava staying on the horizontal part of its pressure-diameter 20 1 relationship (Fig. 5). Cyclic respiratory changes in IVC 15 diameter can thus be observed only with a normal or low volume status in a mechanically ventilated patient. In 10 r = .79 the past, these changes were poorly correlated with atrial
IVC Diam mm p = .0000 5 pressure during mechanical ventilation [11]. Lack of IVC diameter variation in a mechanically ventilated patient 0 exhibiting circulatory failure rules out the patient’s ability 0 5 10 15 20 25 30 to respond fluid in more than 90% of cases [12]. CVP mmHg Feissel et al. [12] first proposed the use of cyclic respiratory changes in IVC diameter to detect fluid Fig. 5 Simultaneous measurement of central venous pressure (CVP) and inferior vena cava diameter (IVC diam) recorded at responsiveness in a mechanically ventilated patient, and end-expiration in 108 mechanically ventilated patients. The pres- their original findings are reported in a recent issue. sure/diameter relationship for the vessel is characterized by an initial Expressing respiratory variability in IVC diameter as ascending part (arrow 1), where the index of compliance (slope of maximal inspiratory diameter minus minimal expiratory diameter/pressure curve) does not change, and a final horizontal part (arrow 2), where the index of compliance progressively decreases, diameter, divided by the average value of the two diame- reflecting distension ters, they found that a 12% increase in inferior vena cava diameter during lung inflation allowed discrimination be- tween responders and non-responders to volume loading, In a healthy subject breathing spontaneously, cyclic with a positive predictive value of 93% and a negative changes in pleural pressure, which are transmitted to the predictive value of 92% [12]. The great merit of this work right atrial pressure, produce cyclic changes in venous is to propose a noninvasive parameter to evaluate volume return, with an inspiratory acceleration, inducing an loading. Moreover, this echocardiographic measurement inspiratory decrease in IVC diameter of approx. 50% is very easy at the bedside, and requires only minimal (Fig. 4, above) [5]. This cyclic change in vena cava experience in echocardiography (Fig. 6). The findings of diameter is abolished, however, when the vessel is dilated Feissel et al. are confirmed in an identical study by Barbier because, although some inspiratory increase in venous et al. [13], which appears in the same issue. It remains to return persists, the vessel actually stays on the horizontal be seen whether this index is still reliable in patients with part of its pressure-diameter relationship (Fig. 5). This a significant increase in intra-abdominal pressure, which is the case when cardiac tamponade [10] or severe right could limit IVC diameter variations. ventricular failure is present [6]. Another phenomenon occasionally observed in the In a mechanically ventilated patient, the inspiratory IVC during mechanical ventilation is backward flow, phase produces an increase in pleural pressure, which is which is not caused by tricuspid regurgitation but by transmitted to the right atrial pressure, thus reducing the cyclic compression of the right atrium by lung inflation. venous return. As a result respiratory changes in IVC di- Such a sudden compression boosts blood backward from ameter are reversed, compared with those observed during the right atrium to the IVC and does not concern tricuspid spontaneous breathing, with an inspiratory increase, and valve competency [14]. This backward flow might explain an expiratory decrease (Fig. 4, below). However, regarding in part the inaccuracy of the thermodilution method in
Fig. 6a,b Ultrasonographic examination of the superior (a) and inferior (b)ve- nae cavae in the same mechanically ventilated patient, who exhibited hypoten- sion. Transesophageal echocardiography demonstrated a partial collapse of the SVC at each inflation, whereas echocardiogra- phy by a subcostal approach demonstrated a marked increase in IVC diameter. After blood volume expansion cardiac index significantly increased, hypotension was corrected, and variations in vena cava diameter disappeared. TP: tracheal pressure 206 184 F. Jardin and A. Vieillard-Baron
measuring cardiac output in mechanically ventilated sponsiveness in mechanically ventilated patients exhibit- patients [14]. ing circulatory failure. In our opinion, a complete evalua- In conclusion, ultrasonographic examination of the ve- tion of volume status in these patients should include both nae cavae provides new and accurate indices of fluid re- IVC and SVC examination.
References 1. Mellander S, Johanson B (1968) 6. Moreno F, Hagan A, Holmen J, Pryor 11. Jue J, Chung W, Schiller N (1992) Does Control of resistance, exchange and A, Strickland R, Castle H (1984) inferior vena cava size predict right capacitance functions in the peripheral Evaluation of size and dynamics of atrial pressure in patients receiving circulation. Pharmacol Rev 20:117–196 theinferiorvenacavaasanindexof mechanical ventilation. J Am Soc 2. Rushmer R (1970) Peripheral vascular right-sided cardiac function. Am J Echocardiogr 5:613–619 control. In Rushmer R (ed) Cardio- Cardiol 52:579–585 12. Feissel M, Michard F, Faller JP, Teboul vascular dynamics. WB Saunders, 7. Nakao S, Come P, McKay R, Ransil B JL (2004) The respiratory variation in Philadelphia, pp 113–147 (1987) Effects of positional changes on inferior vena cava diameter as a guide 3. Vieillard-Baron A, Augarde R, Prin S, inferior vena caval size and dynamics to fluid therapy. Intensive Care Med Page B, Beauchet A, Jardin F (2001) and correlations with right-sided cardiac 30:1834–1837 Influence of superior vena caval zone pressures. Am J Cardiol 59:125–132 13. Barbier C, Loubières Y, Schmit conditions on cyclic changes in right 8. Guyton A, Lindsey A, Abernathy A, C, Hayon J, Ricôme JL, Jardin F, ventricular outflow during respiratory Richardson T (1957) Venous return Vieillard-Baron A (2004) Respiratory support. Anesthesiology 95:1083–1088 at various right atrial pressures and changes in inferior vena cava diameter 4. Vieillard-Baron A, Chergui K, Rabiller the normal venous return curve. Am J are helpful in predicting fluid respon- A, Peyrouset O, Page B, Beauchet A, Physiol 189:609–615 siveness in ventilated septic patients. Jardin F (2004) Superior vena caval 9. Jardin F, Farcot JC, Boisante L, Prost JF, Intensive Care Med 30:1740–1746 collapsibility as a gauge of volume Guéret P, Bourdarias JP (1982) Mech- 14. Jullien T, Valtier B, Hongnat JM, status in ventilated septic patients. anism of paradoxal pulse in bronchial Dubourg O, Bourdarias JP, Jardin F Intensive Care Med 30:1734–1739 asthma. Circulation 66:887–894 (1995) Incidence of tricuspid regurgi- 5. Mintz G, Kotler M, Parry W, Iskandrian 10. Himelman R, Kircher B, Rockey D, tation and vena caval backward flow A, Kane S (1981) Real-time inferior Schiller N (1988) Inferior vena cava in mechanically ventilated patients. vena caval ultrasonography: normal and plethora with blunted respiratory re- A color Doppler and contrast echocar- abnormal findings and its use in assess- sponse: a sensitive echocardiographic diographic study. Chest 107:488–493 ing right heart function. Circulation sign of cardiac tamponade. J Am Coll 64:1018–1025 Cardiol 12:1470–1477 Xavier Monnet Passive leg raising Jean-Louis Teboul
provided that its effects are assessed by a real-time measurement of cardiac output.
Keywords Fluid responsiveness · Passive leg raising · Vol- ume expansion · Cardiac preload
Physiological changes in hemodynamics during PLR Lifting the legs in the event of circulatory collapse is a rescue maneuver that has been used for years by first-aid rescuers. Passive leg raising (PLR) has recently gained interest as a test for monitoring functional hemodynamic and assessing fluid responsiveness since it is a simple way to transiently increase cardiac preload. Lifting the legs passively from the horizontal plane in a lying subject obviously induces a gravitational transfer of blood from the lower part of the body toward the central circulatory Abstract Objective: To assess whether the passive leg compartment and especially toward the cardiac cavities. raising test can help in predicting fluid responsiveness. Using radiolabeled erythrocytes a physiological study in Design: Nonsystematic review of the literature. Results: humans demonstrated that the volume of blood contained Passive leg raising has been used as an endogenous fluid in the calves was reduced during PLR, a reduction corre- challenge and tested for predicting the hemodynamic sponding to the transfer of approx. 150 ml blood [1]. Thus response to fluid in patients with acute circulatory failure. PLR recruits a part of blood contained in the venous reser- This is now easy to perform at the bedside using methods voir and converts unstressed volume to stressed volume. that allow a real time measurement of systolic blood In turn PLR increases right cardiac preload, likely through flow. A passive leg raising induced increase in descending an increase in the mean circulatory pressure which is the aortic blood flow of at least 10% or in echocardiographic driving pressure for venous return. If the right ventricle is subaortic flow of at least 12% has been shown to predict preload responsive, the increase in systemic venous return fluid responsiveness. Importantly, this prediction remains results in an increase in right cardiac output and hence very valuable in patients with cardiac arrhythmias or in the left ventricular filling. Clinical studies conducted spontaneous breathing activity. Conclusions: Passive leg in various hemodynamic conditions have reported an raising allows reliable prediction of fluid responsiveness increase in pulmonary artery occlusion pressure [2–5], left even in patients with spontaneous breathing activity or ventricular end-diastolic dimension [2, 6], E wave of the arrhythmias. This test may come to be used increasingly mitral flow [2, 3, 7], and left ventricular ejection time [8] at the bedside since it is easy to perform and effective, during PLR, supporting the evidence that the volume of
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 185 DOI: 10.1007/978-3-642-01769-8_34, © Springer-Verlag Berlin Heidelberg 2009 186 X. Monnet and J.-L. Teboul blood transferred to the heart during PLR is sufficient to increase left cardiac preload. Nonetheless, if the preload reserve of the right heart is limited, the increase in right cardiac preload should not result in an increased flow toward the left ventricle, and thus PLR should not increase left-side preload in such cases. The response to PLR of the markers of right preload (e. g., central venous pressure) and of left preload may therefore differ. Fig. 1 Postural change during passive leg raising. If at baseline the As a result of the increase in left ventricular preload patient is not lying horizontally but is in semirecumbent position, PLR may ultimately result in an increase in cardiac out- PLR consists of a simple pivoting of the entire bed. Compared to put, depending on the degree of left ventricular preload a case in which the trunk of the patient lies horizontally at baseline, reserve. Interestingly, Wong and colleagues [9] reported this method is advantageous because (a) it does not change the hip that the increase in stroke volume induced by a 45° leg angle, and (b) it may induce the transfer of a larger volume of blood lifting in healthy subjects was of larger magnitude after withdrawal of 500 ml blood, suggesting that PLR affects cardiac output differently according to the central volume patients with hypovolemic than in those with septic shock. status and thus the degree of cardiac preload reserve. An However, in volume-depleted patients with high volume important point is that the PLR-induced increase in cardiac responsiveness even a moderate increase in preload can preload vanishes completely when the legs are returned result in a significant change in cardiac output. In support to horizontal position [5, 8, 10, 11]. Therefore PLR can of this, the increase in cardiac output in normal subjects be considered as a brief and completely reversible “self- in response to PLR has been shown to be increased after volume challenge”. It must also be stressed that the effect blood removal [12]. of PLR on cardiac output—when it occurs—is not always sustained when the leg elevation is prolonged. In septic shock patients capillary leak may account for this atten- PLR for testing fluid responsiveness uation. In a study including critically ill patients with cir- in the critically ill culatory failure we observed that the increase in the blood flow of the descending thoracic aorta induced by PLR in Facing a hemodynamic failure, the clinician is often “preload-dependent” patients occurred in few seconds and tempted to give fluid in order to increase cardiac output was maximal approx. 1 min after starting the PLR maneu- by fueling the reservoir in which the heart is pumping. ver [8]. In patients who did not have a sustained response However, fluid administration does not always result to PLR the response to volume infusion also was not sus- in cardiac output enhancement. This comes from the tained. Thus the hemodynamic effects of PLR should be curvilinearity of the Frank–Starling relationship: if the assessed during the time frame of 30–90 s after the onset heart is operating on the initial and steep part of the curve, of the test. it should have some preload reserve, and any increase in Postural changes during PLR are important to consider. cardiac preload results in an increase in stroke volume. If the trunk is in the semirecumbent position before the In this case the patient “responds” positively to fluid maneuver, PLR consists in pivoting the entire body, with administration (Fig. 2). In contrast, if the heart is operating the legs lifted up and the trunk ultimately in the horizontal on the distal and flat part of the Frank–Starling curve position. With this method one would expect that PLR (absence of preload reserve), no significant increase in induces the transfer of a larger blood volume than if the stroke volume is expected from volume loading. In this trunk is initially lying horizontally since not only the case fluid administration may induce harmful effects (e. g., venous blood of the legs but also that contained into the lung inflation, worsening of gas exchange in the case of large splanchnic compartment is mobilized in such a case pulmonary injury, worsening of tissue oxygen transfer) (Fig. 1; Electronic Supplementary Material, ESM). This that would not be counterbalanced by any hemodynamic should increase the total amount of blood that is mobilized benefit. Thus the need has risen to find diagnostic tools during the postural maneuver. for predicting which shocked patients will respond to fluid The response to PLR may also depend upon the ability administration [13]. of the venous reservoir to be recruited. In a patient who Predicting fluid responsiveness solely on the basis of is vasoconstricted because of hypovolemic/cardiogenic measures of preload must be discouraged. Not only one shock the venous reservoir is likely reduced, and the but a family of Frank–Starling curves rely cardiac preload volume recruited by the PLR would be expected to be less. and stroke volume according to individual factors such as By contrast, in a patient with a vasodilatory state such cardiac contractility (Fig. 2). Accordingly, a given value of as septic shock a higher unstressed volume is expected preload could be associated with preload reserve in pa- to be recruited by PLR. Based on this hypothesis, PLR tients with normal cardiac contractility but with absence should theoretically increase right ventricle preload less in of preload reserve in the case of patients with profoundly Passive leg raising 187
Conflicting results have subsequently been reported [24], perhaps because the test is effective only in cases of no forced expiration [26]. PLR is an alternative means to predict the hemody- namic response to fluid administration since it can be used as a “self-volume challenge” at the bedside [27]. In mechanically ventilated patients fully adapted to their ventilator PLR-induced changes in stroke volume have been found to be closely correlated with the changes in stroke volume induced by a subsequent 300 ml colloid infusion [5]. Importantly, the hemodynamic changes induced by PLR are not affected by arrhythmias or by ventilator triggering. Therefore the PLR can be still used in circumstances where heart–lung interaction indices are Fig. 2 Challenging the Frank–Starling curve with the passive leg misleading. In a study including 71 shocked patients mon- raising (PLR). In patients with circulatory failure it is not possible itored by esophageal Doppler we investigated whether the to predict the response to volume administration because not just response of descending aortic blood flow to PLR predicts one but numerous curves rely stroke volume and cardiac preload. fluid responsiveness [8]. Interestingly, PLR increased the PLR induces a change in preload that enables to challenge the rela- tionship. If the increase in cardiac preload occurring during the test aortic flow time—a marker of left cardiac preload—to the ( from A to B) produces a large increase in stroke volume ( from a’ same proportion in both responders and nonresponders, to b’), preload responsiveness is likely and the patient should re- suggesting that this test actually performs as a volume spond to fluid administration. If the increase in stroke volume during challenge. The changes in the descending aortic blood the test is of small amplitude ( from a to b), preload responsiveness observed during a PLR test were closely correlated with is unlikely and fluid administration should be avoided those induced by the subsequent volume expansion. Moreover, a PLR-induced increase in aortic blood flow by more than 10% predicted a fluid-induced increase in impaired contractility because they are on the steep part of aortic blood flow by more than 15% (i. e., fluid respon- their cardiac function curve. Numerous studies now sup- siveness) with very good sensitivity and specificity [8] port the evidence that static measures of cardiac preload (Fig. 3). In the subgroup of patients fully adapted to are not appropriate to assess preload reserve [14, 15]. In their ventilator the response to PLR performed equally to this regard cardiac filling pressures such as central venous pulse pressure respiratory variation in predicting volume pressure and pulmonary artery occlusion pressure cannot responsiveness [8]. More importantly, in the subgroup of differentiate between patients responding and patients not patients who triggered their ventilator or who experienced responding to fluid administration [16]. Fluid responsive- arrhythmias we found that the aortic blood flow response ness assessment must be rather based on the response to to PLR to predict fluid responsiveness retained its predic- dynamic tests which induce transient changes in cardiac tive value while pulse pressure variation was no longer preload [17]. reliable [8]. These findings emphasize the specific interest Since mechanical ventilation is able to induce cyclic of PLR under conditions where heart–lung interactions changes in cardiac preload, the respiratory variation in stroke volume has been proposed to assess preload reserve [17]. Accordingly, the respiratory variations in surrogates of stroke volume such as arterial pulse pressure [18], Doppler subaortic flow [19], pulse contour derived stroke volume [20, 21], descending aortic blood flow [22], and even pulse oximetry wave [23] have been demonstrated to predict fluid responsiveness in the criti- cally ill. Nonetheless, such heart–lung interaction indices can be used in only specific conditions, such as regular sinus cardiac rhythm and full adaptation of the patient to the ventilator as during deep sedation or coma. If not, the irregularity of the cardiac rhythm or of the respiratory cycle also account for variability in stroke volume such that fluid responsiveness can no longer be predicted by Fig. 3 Typical waveform of aortic blood flow during a passive leg raising (PLR) test and volume expansion in a patient with preload the variations in stroke volume [8, 24]. In patients with reserve. In this patient with an acute circulatory failure the increase spontaneous ventilation respiratory variation in the central in aortic blood flow observed during PLR can predict the positive venous pressure has been proposed as an alternative [25]. response to volume expansion 188 X. Monnet and J.-L. Teboul indices cannot be interpretable. Recently two studies 10–15% increase in cardiac output found as a predict- performed in patients with spontaneous breathing activity ing cutoff [30]. PLR-induced changes in arterial pulse demonstrated that an increase in echocardiographic stroke pressure [5, 11], descending aorta blood flow [8, 31], volume by more than 12% in response to PLR well pulse contour-derived stroke volume [32], and pulsed distinguished between responders and nonresponders to Doppler-derived velocity–time integral [11, 28] have been fluid administration [11, 28]. In addition, stroke volume proposed to be used for this purpose. In patients monitored response to PLR performed far better than static ultrasono- with esophageal Doppler we found that PLR-induced graphic indices of cardiac filling such as left ventricular changes in arterial pulse pressure were less accurate than end-diastolic area and Doppler estimates of left ventricular PLR-induced changes in descending aorta blood flow [8] filling pressure [11]. in predicting fluid responsiveness in critically ill patients. As with any method for predicting response to fluid This is probably explained by the fact that the descending administration, the cutoff value found for the PLR effects aorta blood flow is a more direct estimate of cardiac output should not be considered as a magic number. Furthermore, than arterial pulse pressure [33]. Given the good sensitivity sensitivity and specificity values are not absolute. They and specificity values reported in recent clinical studies should be interpreted differently depending upon the clin- it is likely that other real-time hemodynamic assessment ical context. For instance, the risk of giving fluid unduly methods such as transthoracic echocardiography (pulsed may be more dangerous in patients with acute lung injury Doppler subaortic flow) [11, 28] and pulse contour cardiac or acute respiratory distress syndrome. In these cases the output monitor [32] can be also appropriately used for physician should administer fluid if the effects of PLR on quantifying the short-term hemodynamic response to the cardiac output estimate are clearly above the proposed PLR. The third requirement is to ensure that there is cutoff value. actually a change in preload in response to PLR before trying to determine whether there is an increase in cardiac output or preload. In the case of increase in cardiac Practical aspects of the PLR test preload with PLR the absence of increase in stroke volume should indicate that the patient is not fluid responsive. A simple way to perform PLR is to transfer the patient On the other hand, in the case of insufficient increase from the 45° semirecumbent to the PLR position by using in preload with PLR (insufficient volume recruitment) the automatic pivotal motion of the patient’s bed [8] the absence of PLR-induced increase in stroke volume (Fig. 1; see ESM). In addition to its ease of use, this cannot be interpreted. In such cases the PLR cannot be method allows PLR to be performed rapidly without used to predict volume responsiveness. Thus it should inducing hip flexion and femoral catheters motion. This be recommended to follow the changes in a marker of is important since such procedures should avoid any cardiac preload as a prerequisite to a correct interpretation pain-induced sympathetic stimulation that can result in of the PLR test [34]. Central venous pressure, duration erroneous interpretation of the hemodynamic effects of of the aortic flow measured by esophageal Doppler, or PLR. Accordingly, when performed in such a way, PLR end-diastolic dimensions at echocardiography can be used did not increase heart rate, suggesting that no confusing for this purpose. Finally, the level of the intra-abdominal sympathetic alteration occurred during the test [8]. Ad- pressure may be important to consider since it can impede ditionally, keeping the thorax in the horizontal position, the PLR-induced blood transfer when elevated. This point and not lower, may avoid the risk of gastric inhalation. may be one of those that should be addressed by further Nevertheless, it is reasonable to avoid PLR in patients studies concerning PLR. with head trauma since it can increase the intracerebral In summary, the physiological effects of PLR consist pressure. Elastic compression stocking may also alter the of an increase in venous return and cardiac preload. The venous volume recruited by the PLR [29]. PLR thus acts as a self-volume challenge which is easy- Another important point concerns the conditions to-perform and completely reversible. It has gained an that must be fulfilled for correct measurement and in- increasing interest in the field of functional hemodynamic terpretation of PLR effects. The first condition is that it monitoring since it can help to detect fluid responsive- be a real-time cardiovascular assessment able to track ness in critically ill patients even in cases of ventilator hemodynamic changes in the time frame of PLR effects, spontaneous triggering or cardiac arrhythmias. Its optimal i. e., 30–90 s [30] (see ESM). The second is that the use requires a real-time cardiovascular assessment device limits of precision in the technique used for assessing able to quantify accurately the short-term hemodynamic the response of cardiac output to PLR be far below the response. Passive leg raising 189
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Abstract Abnormalities of sleep are ties, and the cause for the remainder is extremely common in critically ill pa- not known; severity of underlying dis- tients, but the mechanisms are poorly ease is likely an important factor. Me- understood. About half of total sleep chanical ventilation can cause sleep time occurs during the daytime, and disruption, but the precise mechanism circadian rhythm is markedly dimin- has not been defined. Sleep disruption ished or lost. Judgments based on in- can induce sympathetic activation and spection consistently overestimate elevation of blood pressure, which sleep time and do not detect sleep dis- may contribute to patient morbidity. In ruption. Accordingly, reliable poly- healthy subjects, sleep deprivation can graphic recordings are needed to mea- decrease immune function and pro- sure sleep quantity and quality in criti- mote negative nitrogen balance. Mea- cally ill patients. Critically ill patients sures to improve the quantity and exhibit more frequent arousals and quality of sleep in critically ill patients awakenings than is normal, and de- include careful attention to mode of creases in rapid eye movement and mechanical ventilation, decreasing slow wave sleep. The degree of sleep noise, and sedative agents (although fragmentation is at least equivalent to the latter are double-edged swords). that seen in patients with obstructive sleep apnea. About 20% of arousals Keywords Sleep · Critical illness · and awakenings are related to noise, Mechanical ventilation · Artificial 10% are related to patient care activi- respiration · Arousal
Introduction know little of the sleep experienced by a critically ill pa- tient. But we do know that sleep is commonly disrupted In his roman-a-clef, “Ravelstein”, the Nobel Laureate in critically ill patients [2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, Saul Bellow [1] describes being admitted to an intensive 13, 14, 15, 16], and that sleep disruption may adversely care unit and receiving mechanical ventilation: affect patient outcome [8, 17]. In this review, we discuss “I was now the dying man. My lungs had failed. A the nature of sleep disturbances in critically ill patients, machine did my breathing for me. Unconscious, I had no potential causes, and possible therapies. more idea of death than the dead have. But my head (I assume it was my head) was full of visions, delusions, and hallucinations. These were not dreams or night- Normal sleep and circadian rhythm mares. Nightmares have an escape hatch....” Despite the obvious importance of sleep and its desir- Healthy young adults experience two distinct states of ability in a patient with a serious illness, we know noth- sleep: rapid eye movement (REM) sleep and non-REM ing of the visions, hallucinations and dreams experienced (NREM) sleep. REM sleep accounts for about 25% of by a critically ill patient such as Bellow. Indeed, we sleep time and is characterized by episodic bursts of rapid
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 191 DOI: 10.1007/978-3-642-01769-8_35, © Springer-Verlag Berlin Heidelberg 2009 198 192 S. Parthasarathy and M.J. Tobin
Table 1 Studies of sleep in critically ill patients
More than 24 h Number of Patient type Sleep staging Arousals and Mechanical patients awakenings ventilation per hour (%)
Polysomnography performed over 24 h Hilton [2] 10 Medical Yes Not listed Not listed Aurell [3] 9 Postoperative Yes Not listed Some patients Gottschlich [4] 11 Burn patients Yes >63 100 Cooper [5] 20 Medical Yes 39 100 Freedman [6] 22 Medical Yes >11 100 Valente [7] 24 Head trauma Yes Not listed 100 Gabor [8] 7 Medical Yes 22 100 Polysomnography performed only at nighttime Johns [9] 5 Postoperative Yes Not listed Not listed Orr 10 9 Postoperative Yes Not listed Not listed Broughton [11] 12 Medical Yes >21 NA Knill [12] 12 Postoperative Yes >21 Not listed Edwards [13] 21 Medical Yes Not listed 95 Aaron [14] 6 Medical Yes >19 Not listed Parthasarathy [15] 11 Medical Yes 58 100 Richards [16] 64 Medical Not listed Not listed 0 Polysomnography not performed Woods [18] 4 Postoperative Not listed Helton [19] 62 Not listed Not listed Tweedie [20] 15 Medical and postoperative 80 Kong [21] 60 Medical 100 Hurel [22] 223 Medical and postoperative 0 Freedman [23] 203 Medical and postoperative 0 Simini [24] 162 Medical and postoperative 0 Treggiari [25] 40 Postoperative 0 Walder [26] 17 Postoperative 60 Shilo [27] 8 Medical 50 Olson [28] 843 Medical and postoperative Not listed Topf [29] 97 Postoperative Not listed Nelson [30] 100 Medical 60 Mundigler [31] 24 Medical and postoperative 100 McKinley [32] 14 Medical and postoperative 0 eye movements, irregularities in respiration and heart rate, ical clock regulates several physiological, behavioral, and and paralysis of major muscle groups with the exception biochemical rhythms. Hormone secretion (cortisol, growth of the diaphragm and upper airway muscles. NREM sleep hormone), body temperature, immune function, coronary is divided into four stages (1, 2, 3 and 4). The progression artery muscle tone, and bronchial smooth muscle tone, to of sleep from stage 1 through to stage 4 is accompanied name a few, exhibit marked circadian variability. by a progressive increase in the arousal threshold (the ability to wake in response to a stimulus). Stage 1 occurs at sleep onset and is also a transitional state between sleep Abnormalities of sleep in critically ill patients stages. Up to 50% of the night is spent in stage 2 sleep, which is characterized by spindles and K complexes on Just as with ambulatory patients, sleep in critically ill pa- the electroencephalograph (EEG). Progression of stage 2 tients is assessed in terms of quantity, distribution over is accompanied by the gradual appearance of high-voltage 24 h, and lack of continuity. Also assessed is the type slow wave activity on the EEG (greater than 75 µV and and depth of sleep—rapid eye movement (REM) and less than 2 Hz). When such slow-wave activity exceeds non-REM (stages 1, 2, 3 and 4)—and the pattern from 20% of the time in a 30-s epoch, sleep is categorized as day to day in the distribution of sleep over a 24-h period stage 3; when it exceeds 50%, sleep is categorized as (circadian rhythm). Accurate measurement of sleep stage 4. Slow wave sleep is considered the most restor- quantity and quality requires reliable polygraphic record- ative. NREM sleep normally cycles with REM sleep every ings. Judgments based on inspection consistently overes- 90 min. The cycling of sleep and wakefulness, in turn, is timate sleep time [3] and do not detect sleep disruption regulated by a biological clock that operates over a 24-h [3, 13]. Table 1 classifies research reports on sleep in period (circadian rhythm). In addition to sleep, the biolog- critically ill patients into studies involving polysomno- 199 Sleep in the intensive care unit 193 graphic recordings over 24 h [2, 3, 4, 5, 6, 7, 8], poly- somnographic recordings during nighttime alone [9, 10, 11, 12, 13, 14, 15, 16], and studies without polysomno- graphic recordings [18, 19, 20, 21, 22, 23, 24, 25, 26, 27, 28, 29, 30, 31, 32]. Also indicated is the type of patient population, whether patients were receiving mechanical ventilation, and whether sleep stages and disruption were adequately reported. Of the 28 studies listed in Table 1, 15 employed polysomnography [2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16], and 7 included continuous re- cordings for 24 h or longer [2, 3, 4, 5, 6, 7, 8]. These studies reveal that almost half of total sleep time in criti- cally ill patients can occur during the daytime [5, 8]. Investigators differ in their conclusions as to whether critically ill patients are sleep deprived. Three groups of investigators found that critically ill patients have a nor- mal or near normal total sleep time, an average of 7–10.4 h a day [4, 5, 6]. Three other groups of investiga- tors found a decrease in total sleep time, 3.6–6.2 h a day [2, 3, 8]. The investigators in one of the studies revealing decreased sleep time had deliberately restricted sedatives and hypnotics [3], although patients received sedatives in the other two studies that revealed sleep deprivation [2, 8]. Even in the studies revealing adequate amounts of Fig. 1 Sleep stages, along the vertical axis, over a 24-h period in sleep, the investigators noted large variations in total three critically ill patients with disrupted sleep. The hypnogram in sleep time among the patients. Cooper and co-workers patient 1 (top) reveals a normal nocturnal sleep pattern. Patients 2 found that some patients slept for hardly an hour and (middle) slept for 65% of time, predominantly stages 1 and 2, and other patients for nearly 15 of 24 h [5] (Fig. 1). Total wakened repeatedly. Patient 3 (bottom) had isolated episodes of stage 1 sleep but was awake for most of 24 h. (Modified from [5] sleep time in the study of Freedman and co-workers var- with permission) ied from 1.7 to 19.4 h [6]. Patients falling in the lowest quartile for total sleep time in these studies are clearly suffering from major sleep deprivation. In addition to 16], making it impossible to compare studies in that re- variation in sleep quality from patient to patient, sleep spect (Table 1). The degree of sleep fragmentation in quality may vary from night to night within a patient as a studies of critically ill patients, however, is equivalent to result of changes in acuity of illness [33], pain, and seda- that in patients with obstructive sleep apnea [34]. tive and analgesic infusions. As such, sleep deprivation Sleep is normally divided into rapid eye movement occurs in many, if not all, critically ill patients. To (REM) and non-REM (NREM) sleep. Critically ill pa- achieve better clarification of the frequency and severity tients spend 6% or less of sleep time in REM sleep as of sleep deprivation, longitudinal studies in a large num- opposed to the normal of 25% [5, 6, 12]. The decrease in ber of patients are needed; it will be essential to control REM sleep has been attributed to medications (narcotics) for the effects of sedation, analgesia, and acuity of ill- [12], lack of sustained sleep needed to reach REM sleep ness when conducting such studies. [6], disturbance of circadian rhythm, underlying disease, In 11 critically ill patients, Parthasarathy and Tobin and endotoxin release [35, 36]. The reduction in REM [15] noted 19 arousals (abrupt shifts in EEG frequency sleep might also be an adaptive response to critical ill- lasting more than 3 s) and 35 awakenings (EEG features ness because REM is a time of sympathetic-parasympa- compatible with wakefulness) per hour. Total sleep dis- thetic imbalance and increased susceptibility to breath- ruption, 54 arousals and awakenings per hour, was more ing abnormalities. Critically ill patients also experience than twice that seen in healthy individuals similarly inst- less of stages 3 and 4 of NREM, which are characterized rumented. Cooper and co-workers [5] also reported fre- by stable respiratory control and are devoid of sympa- quent sleep disruption, with 42 arousals and awakenings thetic-parasympathetic imbalances. per hour, and Gabor and co-workers [8] reported some- Critically ill patients may not exhibit the EEG fea- what less frequent disruption, 22 arousals and awaken- tures of sleep and wakefulness conventionally seen in ings per hour. With the exception of the three preceding ambulatory patients [5]. Cooper and co-workers found studies [5, 8, 15], the remaining investigators who ob- that 7 of 20 mechanically ventilated patients were in co- tained EEG recordings in critically ill patients did not ma and 5 patients did not exhibit EEG characteristics of specify the sum of arousals and awakenings [3, 7, 9, 10, stage 2 sleep (spindles or K complexes). Four patients 200 194 S. Parthasarathy and M.J. Tobin exhibited pathological wakefulness (a combination of despite achieving adequate levels of sedation. Severe behavioral correlates of wakefulness and EEG features sleep fragmentation may also occur in mechanically ven- of slow wave sleep), occupying 26–68% of the 24-h re- tilated patients despite sedatives and analgesics [4, 5]. cording. Only 8 of the 20 patients demonstrated EEG Some of the discrepancies between bedside assess- characteristics of sleep, and even these patients had an ment of sedation and subjective scoring of sleep may re- average of 39 arousals and awakenings per hour [5] flect known limitations in the Ramsay sedation scale (Fig. 1). [43]. Kong and co-workers studied the efficacy of mid- Obtaining reliable EEG recordings is difficult in criti- azolam and isoflurane in reducing plasma levels of cate- cally ill patients. Electrical interference (60 Hz) arising cholamines when similar levels of sedation (on the Ram- from equipment such as infusion pumps or ventilators say scale) were achieved. Although both agents achieved [37] is common; interference also arises from muscle comparable levels of sedation, isoflurane, but not mid- contractions in agitated patients [38]. To achieve satis- azolam, lowered the plasma levels of catecholamines factory EEG signals, which may consist of only a few from baseline [21]. The persistently elevated catechola- micro volts, it is necessary to apply electrodes to appro- mines in the patients receiving midazolam may have pro- priate areas of the scalp; the skin also requires careful duced sleep disruption, although the explanation is no preparation to ensure low contact impedance (preferably more than a possibility because polysomnography was less than 5 Ohms). To further minimize interference, all not performed. wires between a patient and preamplifier must be as Benzodiazepines, narcotic analgesics, and propofol short as possible [37]. Additional challenges in conduct- are commonly used to sedate critically ill patients [39]. ing research studies are avoiding a change in sedative Benzodiazepines improve behavioral aspects of sleep. medications, curtailing unnecessary visits by hospital They decrease the time needed to fall asleep, decrease personnel, and minimizing agitation. awakenings, increase sleep duration, and increase sleep A few investigators have studied circadian rhythms in efficiency (duration of sleep as a percentage of time in critically ill patients. Mundeglier and co-workers [31] bed). Benzodiazepines, however, also increase the num- measured urinary 6-sulfatoxymelatonin every 4 h over ber of spindles, increase cortical EEG frequency (at low 24 h. Compared with 7 non-septic critically ill patients doses), decrease EEG amplitude and frequency (at high and 21 healthy volunteers, the amplitude of circadian doses), and suppress REM and slow wave sleep [44]. Al- fluctuation in this melatonin metabolite was markedly though the clinical importance of these EEG alterations lower in 17 critically ill patients suffering from septic is not totally clear, an ideal hypnotic should not disturb shock. the normal sleep pattern. Narcotics can also suppress REM sleep, cause a dose-dependent slowing of EEG, and suppress slow wave sleep—the most restorative Relationship between sedation and sleep stage of sleep [12, 44, 45]. In sum, a medicated state may resemble sleep on the surface, but may not provide Critically ill patients are often given sedatives to in- the physiological benefits associated with true sleep. crease patient comfort, decrease anxiety and agitation, and promote amnesia and sleep [25, 39]. Continuous in- fusion of sedatives, however, may prolong the duration Factors contributing to sleep disruption of mechanical ventilation by 2.5 days and prolong ICU stay by 3.5 days [40]. The effect of sedative agents on Noise and hospital staff the depth of sedation has been rigorously studied [39, 41, 42], although little is known about its effect on sleep The level of noise in the ICU ranges from 50 to 75 dB, quality in critically ill patients [43]. Over a 5-day period, with peaks of up to 85 dB [8, 26, 46, 47, 48, 49, 50, 51, 40 non-intubated critically ill patients were randomized 52]. This level of noise is comparable to that in a factory to nocturnal midazolam and propofol [25]. On a 10-point (80 dB) or a busy office (70 dB), and is louder than noise self-rating scale, both groups reported a tendency to- in a bedroom (40 dB) [51]. (The decibel scale is logarith- wards improved sleep quality: from 6.3 to 7.2. The infu- mic, and an increase of 10 dB represents a doubling of sions were titrated to achieve a score of 3 or greater on noise.) When studying the relationship between ICU the Ramsay sedation scale (a score of 3 indicates that a noise and sleep disruption, investigators commonly at- patient is asleep but awakens with a brisk response to a tribute arousals to noise when they occur within 3 s of a glabellar tap or a loud auditory stimulus) [42]. Self-per- measurable (greater than 15 dB) increase in noise [5, 6]. ception of sleep quality was not different for propofol In these studies, 11–20% of arousals were attributed to and midazolam (range 0.1–9.7; mean of 7.2). Some pa- noise [5, 6]. Because critically ill patients have frequent tients continued to rate sleep quality close to zero on the arousals and awakenings (20–68 per hour, Table 1) some fifth day. These data indicate that self-perception of arousals may mistakenly be attributed to noise. In a sleep quality can be poor with high dosages of sedatives study of healthy volunteers subjected to audio recordings 201 Sleep in the intensive care unit 195 of ICU noise, a greater than normal number of awaken- ings and less REM and total sleep time were observed [50, 53]. Findings in healthy subjects, however, may not apply to critically ill patients, who may have a higher arousal threshold secondary to sleep deprivation, seda- tive agents, or coma. Gabor and co-workers [8] recorded audio and video signals in synchrony with polysomnography in seven pa- tients receiving mechanical ventilation. Twenty percent of the arousals and awakenings were related to noise peaks, and only 10% were related to patient care activi- ties. The cause of 68% of arousals and awakenings could not be identified [8].
Fig. 2 Sleep fragmentation (left panel) and sleep efficiency (right Mechanical ventilation panel) during assist-control ventilation and pressure support with and without dead space. Sleep fragmentation, measured as the About 40% of patients in an ICU receive mechanical number of arousals and awakenings, was greater during pressure support (solid bars) than during assist-control ventilation (hatched ventilation [54], but investigations into the precise mech- bars) or pressure support with dead space (open bars). Sleep effi- anisms of the effect of mechanical ventilation on sleep ciency (right panel) was also lower during pressure support (solid are only commencing. Mechanically ventilated patients bars) than during assist-control ventilation (hatched bars) or pres- experience considerable sleep disruption, with as many sure support with dead space (open bars). (Modified from [15] as 20–63 arousals and awakenings per hour [4, 5, 8]. At with permission) first glance, a comparison of mechanically ventilated pa- tients with spontaneously breathing critically ill patients lator mode. In these 11 patients, the most important deter- should provide a reasonable method for investigating the minant of apneas was the difference between PCO2 dur- effect of mechanical ventilation on sleep (Table 1). Such ing resting breathing and the patient’s apnea threshold. comparisons might prove misleading for a number of When a patient’s resting PCO2 was close to the apnea reasons. First, acuity of illness may be greater in venti- threshold, central apneas were more likely to develop. lated patients than in spontaneously breathing patients. The addition of dead space caused a further increase in Second, spontaneously breathing patients are vulnerable resting PCO2 above the apnea threshold and decreased to obstructive apneas, which will be prevented by an en- the sum of arousals and awakenings from 83 to 44 events dotracheal tube. Third, factors associated with ventila- per hour (in the patients who developed central apneas tion, such as masks, tracheal tubes, suctioning, mouth during pressure support). Sleep efficiency (time asleep as guards, nasogastric tubes, and physical restraints, may a percentage of study duration) increased from 63 to 81% contribute to sleep fragmentation [55]. Fourth, sedatives with the addition of dead space (Fig. 2). and analgesics are more likely during mechanical venti- lation. An attractive way to study the effect of mechani- cal ventilation on sleep might be to study tracheostomi- Other factors zed patients while connected and disconnected from a ventilator over a short time period. Factors that contribute to sleep abnormalities in critically Notwithstanding methodological concerns with the ill patients include acute illness [2, 3, 11, 12], pain, light, studies, data suggest that the mode of ventilation can in- and patient discomfort [17]. Noxious stimuli that contrib- fluence sleep quality [56, 57]. Meza and co-workers [56] ute to patient discomfort and arousal include increased showed that pressure support induces central apneas in respiratory effort [58, 59], hypoxemia [58], and hyper- healthy subjects during sleep. In a study of 11 critically ill capnia [58]. Swings in intrathoracic pressures are potent patients during one night of sleep, Parthasarathy and To- stimuli for inducing arousals in healthy subjects [60] and bin observed greater sleep fragmentation during pressure in patients with upper airway resistance syndrome [34]. support than during assist-control ventilation: 79 versus 54 arousals and awakenings per hour (Fig. 2). Six of the 11 patients developed central apneas during pressure sup- Clinical implications port, but not during assist-control ventilation [15]. Heart failure was more common in the patients who developed Clinical outcomes apneas than in the patients without apneas: 83% versus 20%. The findings emphasize that research on sleep in Sleep fragmentation may influence morbidity and mor- critically ill patients needs to be controlled for the venti- tality in critically ill patients. Patients in coma and pa- 202 196 S. Parthasarathy and M.J. Tobin
Fig. 3 Respiratory rate during assist-control ventilation (AC) and pressure support (PS) in 11 critically ill patients. For each mode, the lines connect the mean value for each patient during wakeful- Fig. 4 Inspiratory time (left panel) and expiratory time (right pan- ness (W, left) and sleep (S, right). Compared with wakefulness, el) during assist-control ventilation (AC) and pressure support group mean respiratory rate was lower during sleep (closed sym- (PS) in 11 critically ill patients. The lines connect the mean value bols) than during wakefulness (open symbols). The difference be- for each patient during wakefulness (W, left) and sleep (S, right). tween sleep and wakefulness was greater for pressure support than During pressure support, group mean inspiratory time and expira- for assist-control ventilation. (Modified from [15] with permis- tory time were greater during sleep (closed symbols) than during sion) wakefulness (open symbols). The difference between sleep and wakefulness was greater for pressure support than for assist-con- trol ventilation. (Modified from [15] with permission) tients who lack well-defined EEG characteristics of stage 2 sleep have higher acute physiological scores than do to respiratory rate, which provides reasonable guidance patients with identifiable but fragmented sleep [5]. Some as to a patient’s inspiratory effort [64, 65]. If, however, investigators have reported no association between the physicians titrate pressure support to respiratory rate acuity of illness and sleep disruption [6]. As such, the while the patient is asleep, patient effort will increase contribution of acuity of illness to sleep disturbances is considerably on awakening. unclear. Animal data suggest that sleep deprivation may Changes in ventilator settings are commonly based on lead to death [61]. It is thought that death is unlikely to arterial blood gas measurements. End-tidal CO2 was result with sleep deprivation in human subjects [62, 63], greater in 11 critically ill patients during sleep than dur- but the consequence of sleep deprivation has been stud- ing wakefulness: by 11% during pressure support and by ied only in healthy subjects and not in critically ill pa- 5% during assist-control ventilation. Patients who re- tients. peatedly slip in and out of sleep display marked fluctua- Among 24 patients with post-traumatic coma, 5 of 6 tions in end-tidal CO2. The coefficient of variation of patients who had organized sleep patterns survived as end-tidal CO2 was 8.7% during pressure support and opposed to 3 of 7 patients who had low voltage theta- 4.7% during assist-control ventilation [15]. In some pa- delta or mixed frequency activity without definable fea- tients receiving pressure support, end-tidal CO2 can be as tures of sleep; functional outcome was also better in the much as 7 mmHg higher during sleep than during wake- patients with organized sleep patterns [7]. Freedman and fulness. Differences in PCO2 between sleep and wakeful- co-workers found that 5 of 22 patients exhibited EEG ness of this magnitude may cause physicians to change features of mild to moderate encephalopathy before oth- ventilator settings when a change is not necessary. Con- er features of sepsis manifested [6]; none of the non-sep- sequently, under-ventilation or over-ventilation may re- tic patients demonstrated such EEG features. sult [66]. Compared with wakefulness, sleep caused a 23% increase in inspiratory time and a 126% increase in expiratory time in patients receiving pressure support Ventilator settings (Fig. 4). The increase in inspiratory time that accompa- nied change from wakefulness to sleep was also associat- Physicians typically adjust ventilator settings during the ed with an increase in tidal volume, and the likely ac- daytime and without knowing whether a patient is asleep companiment of hypocapnia may explain the develop- or awake. Compared with wakefulness, sleep caused a ment of apneas during pressure support [67, 68]. These 33% decrease in respiratory rate during pressure support findings indicate that the effect of sleep on breathing pat- and a 15% decrease in rate during assist-control (Fig. 3) tern and gas exchange has important implications for re- [15]. The level of pressure support is commonly titrated search on patient-ventilator interaction. 203 Sleep in the intensive care unit 197
Cardiorespiratory consequences The study has limitations. Sleep was assessed at the bed- side by nursing staff rather than polysomnography. No In ambulatory patients, sleep fragmentation can result in intervention was performed, and a cause and effect rela- elevations of arterial blood pressure, elevations of uri- tionship between sleep deprivation and delirium cannot nary and serum catecholamines, arrhythmias, progres- be inferred. Agitation can cause elevations in plasma cat- sion of cardiac failure, and even death [69, 70]. Sleep- echolamines [21]. Large doses of sedative agents are disordered breathing might cause similar abnormalities often used in agitated and delirious patients; when the in critically ill patients, although direct evidence is lack- agitation resolves, however, the sedative agent may re- ing. Apneas and hypopneas cause hypoxemia [16], main in adipose tissue and interfere with weaning from which, in turn, may produce sympathetic activation and mechanical ventilation. arrhythmias in critically ill patients; evidence on this is- sue, however, is anecdotal [71] and inconclusive [72]. Sleep fragmentation induced by auditory stimuli can Immunological and metabolic consequences increase nocturnal blood pressure in dogs [73]. In pa- tients who have central sleep apnea, the major cause of Sleep deprivation can unfavorably alter immune function oscillations in blood pressure is ventilatory oscillations, [80, 81, 82, 83, 84, 85, 86]. In 42 healthy volunteers, with a significant contribution from arousals [73]. These Irwin and co-workers found that sleep deprivation result- investigations [73, 74] suggest that arousals may elevate ed in almost a 50% decrease in natural killer cell activity nocturnal blood pressure, secondary to increases in sym- and a 50% decrease in lymphokine killer cell activity. pathetic activity, and contribute to cardiovascular com- One night of sleep returned natural killer cell activity to plications [75]. Preliminary data suggests that sleep frag- baseline. mentation in critically ill patients may be associated with Sleep deprivation can promote negative nitrogen bal- elevations in blood pressure [76], but the effect on mor- ance and increase energy expenditure [62, 63, 87]. In six bidity and mortality is unknown. healthy volunteers, 24 h of sleep deprivation produced a The effect of sleep deprivation [77] on the ventilatory 7% increase in nitrogen excretion. Some subjects experi- responses to hypoxia and hypercapnia is controversial enced as much as a 20% increase in nitrogen excretion. [78]. Sleep deprivation has long been believed to depress It is not known whether similar changes occur in critical- chemoreceptor function [78]. Spengler and colleagues ly ill patients. [78], however, recently found that sleep deprivation did not alter the hypercapnic ventilatory response in healthy subjects. The situation in critically ill patients has not Long-term consequences been studied. Blunting of the chemoreceptor response can decrease the ability of the respiratory system to com- Critical illness may have long-term consequences on pensate for respiratory loads during or after the with- sleep [22]. When 329 patients were interviewed drawal of mechanical ventilation [68]. 6 months after discharge from an ICU, 223 (67%) report- At least some postoperative patients experience an in- ed severe alterations in sleep. The lack of a control group crease in REM sleep on the third to fourth postoperative makes it impossible to distinguish the role of critical ill- day secondary to the earlier suppression of REM sleep ness from previous health status, underlying medical by anesthetics and analgesics [12]. Because REM sleep diagnosis, persistent disability, or other factors. is characterized by unstable breathing patterns and sym- pathetic-parasympathetic imbalances, the increase in REM sleep in the early postoperative period may aggra- Strategies to decrease sleep disruption vate the risk of postoperative atelectasis, pneumonia, hypoxemia, and cardiovascular morbidity. Gabor and co-workers studied the effect of reducing noise in six healthy volunteers while they slept in an ICU [8]. The average level of noise was 51 dB in an Neurological consequences open ICU and 43 dB in an isolated single room (the re- spective peak levels were 65 and 54 dB). Total sleep Sleep deprivation may contribute to delirium and agita- time was greater in the isolated room than in the open tion [19, 79]. In a study of 62 critically ill patients, Hel- ICU, 9.5 versus 8.2 h, although the number of arousals ton and colleagues [19] noted that 24% experienced se- and awakenings were virtually identical in the two set- vere sleep deprivation and 16% experienced moderate tings (14 to 15 events per hour) [8]. In six healthy volun- deprivation. One third of the patients with severe sleep teers attempting to sleep in a noisy environment, Wallace disruption suffered from delirium, 10% of patients with and co-workers found that use of earplugs increased moderate sleep disruption suffered from delirium, but REM sleep (20 versus 15%) and decreased REM latency only 3% of patients with adequate sleep had delirium. (107 versus 148 min), although the number of awaken- 204 198 S. Parthasarathy and M.J. Tobin ings was not affected (25 versus 27 per hour). Because Conclusion only 20% of sleep fragmentation in critically ill patients appears to be attributable to noise [8], reducing noise in Research into sleep disorders in ambulatory patients over the ICU may be of limited value. the last 30 years has provided us with a strong set of Shilo and co-workers undertook a double blind, pla- physiological principles. The time is ripe for applying cebo-controlled study of melatonin in eight critically ill these principles to critically ill patients. A major chal- patients with chronic obstructive pulmonary disease lenge, as with most research in critically ill patients, is [27]. The authors conclude that melatonin achieved the difficulty in controlling for confounding influences greater sleep time and less fragmentation, although the in order to achieve high fidelity recordings. conclusions are not well supported by the data.
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flammatory events, and mortality are poorly understood. This lack of information on the biology of Mg contrasts with well established correlations between serum total and ionized calcium (Ca2+) concentrations, manifesta- tions of acute Ca2+ deficiency, and the physiological ef- fects of correcting ionized hypocalcemia [9, 10, 11, 12]. This review summarizes key aspects of Mg metabo- lism in adult intensive care patients, emphasizing the in- terdependence of Mg homeostasis with that of other cat- ions such as Ca2+ and K+. Thereafter we examine the jus- tification for the trend of increasingly frequent measure- ments of serum total Mg in the critically ill, and how this information is related to emerging data concerning circu- lating Mg2+. In this context, the limitations of current treatment recommendations for hypomagnesemia in the ICU are analyzed as well as research developments like- ly to alter our diagnostic and therapeutic algorithms in the near future. The use of therapeutic doses of Mg inde- pendent of hypomagnesemia or titration to serum total Introduction Mg levels to treat conditions such as preeclampsia and asthma are covered since this is beyond the scope of this Magnesium is the second most abundant intracellular review. cation and the fourth most common cation in the body [1]. Its importance as an essential nutrient has been rec- ognized since 1932, when Kruse et al. [2] reported the Compartmental distribution and metabolism of Mg effects of acute Mg deficiency in rats. Even recently Mg was considered the “forgotten cation” in clinical practice The body normally contains 21–28 g Mg [13]. Approxi- [3]; however, this is no longer the case [4]. Estimates of mately 53% of total Mg stores are in bone, 27% in mus- Mg deficiency range from 20% to 61% [5, 6, 7], while a cle, 19% in soft tissues, 0.5% in erythrocytes, and 0.3% recent study found that reductions in total serum Mg on in serum [14]. The Mg in muscle, soft tissues, and eryth- admission are associated with increased mortality [8]. rocytes is considered to be intracellular [1], and mostly Nonetheless, the relevance of such data to intensive bound to chelators such as adenosine triphosphate (ATP), care is problematic. Controlled data are lacking on how adenosine diphosphate (ADP), proteins, RNA, DNA, and circulating total Mg concentrations are related to levels citrate [14]. Although only 5–10% of intracellular Mg is of biologically active ionized Mg (Mg2+). Data are like- ionized, this fraction is essential for regulating intracel- wise sparse concerning the interplay between serum total lular Mg homeostasis [15] (Fig. 1). and ionized Mg levels during specific critical illnesses Traditionally, extracellular Mg in serum was consid- and their treatment. In particular, the efficacy of thera- ered to be 33% protein bound, 7% complexed to citrate, 2+ 2– – peutic Mg supplementation on Mg , organ function, in- PO4 , and HCO3 [16], and 55% circulating in the diva-
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 201 DOI: 10.1007/978-3-642-01769-8_36, © Springer-Verlag Berlin Heidelberg 2009 668 202 J.L. Noronha and G.M. Matuschak
ents and solvent drag [20]. Although 30–40% of dietary Mg is absorbed [19, 20], factors controlling intestinal ab- sorption are unclear. An inverse curvilinear relationship was shown in healthy volunteers between Mg intake and its fractional absorption ranging from 65% absorption at low intake to 11% at high intake [21]. Thus, estimating the amount of oral Mg salts to correct hypomagnesemia in ICU patients who commonly have ileus and other forms of gastrointestinal dysfunction is problematic. The effects of vitamin D and parathyroid hormone (PTH) on enteral Mg absorption are minor [22]. Renal function is central to Mg homeostasis. Of the approx. 2.4 g Mg filtered per day (i.e., the 77% of total serum Mg that is not protein bound), 5% (120 mg) is normally excreted in the urine [23]. Glomerular filtration and tubular reabsorption both influence renal Mg han- dling [24]. Specifically, 20–30% of filtered Mg is reab- sorbed in the proximal tubule and 60% in the thick as- cending loop of Henlé [25]. This is where ionic regula- tors, hormones, and medications affect Mg excretion. Mg reabsorption in the thick ascending loop of Henlé is linked with NaCl transport and is therefore influenced by Fig. 1 Mg homeostasis. Extracellular Mg levels are maintained tubular flow [24, 25]. Conservation of Mg by normal via absorption, renal excretion, and bone contribution. Extracellu- kidneys during Mg deprivation may decrease fractional lar Mg comprises protein-bound, complexed, and ionized frac- excretion to less than 0.5% (12 mg/day) [23]. Converse- tions. Ionized extracellular Mg is in exchanging equilibrium with ly, the kidneys increase excretion of Mg to approximate the intracellular ionized Mg fraction. MgA cytosol, MgA ribos, MgA nucleus, MgA SPR, MgA mito refer to Mg bound in the cyto- the filtered load during increased intake or excessive Mg sol, ribosomes, nucleus, sarcoplasmic reticulum, and mitochon- administration [26]. During renal failure the fractional dria, respectively excretion of Mg progressively increases, and normal se- rum total Mg levels are maintained until the later stages when hypermagnesemia supervenes [27]. lent ionized form (Mg2+). However, the newer methods of ion-selective Mg electrodes, atomic absorption spec- troscopy, and ultrafiltration indicate that serum Mg is Mg homeostasis and compensatory mechanisms 67% ionized, 19% protein bound, and 14% complexed [17]. Standard clinical determinations of serum total Mg Mg homeostasis involves interaction between three or- reflect all three forms. Of note, protein-bound and com- gan systems: kidneys, small bowel, and bone (Fig. 1). plexed Mg are unavailable for most biochemical pro- Acute Mg deprivation increases tubular reabsorption and cesses [1]. The important issue of the dynamics of equil- intestinal absorption [28]. The mechanisms for such ibration among the various states of extracellular Mg has compensatory alterations in Mg transport are not fully not been extensively studied. Since serum contains only understood. Several reports indicate a lack of correlation 0.3% of total body Mg stores, serum total Mg measure- of these alterations with serum total Mg concentrations ments poorly reflect total body status. Serum total [29, 30, 31]. In Mg deficient rats a fall in urinary Mg ex- Mg concentrations normally average 1.7–2.3 mg/dl cretion was found to occur without changes in plasma to- (1.4–2.1 mEq/l) [13], depending on the laboratory tal Mg concentrations [28]. This adaptation was rapid and measurement technique. Mg concentrations are (within 5 h) and specific (without changes in Na+ or Ca2+ commonly expressed in units of milligrams, millimoles, reabsorption). If Mg deprivation continues, exchange- or milliequivalents; for conversion one can use the able bone Mg starts contributing to extracellular Mg lev- following formula: 1 g Mg sulfate contains 98 mg= els [32]. Up to 30% of bone Mg is rapidly exchangeable 4.06 mmol=8.12 mEq elemental Mg. [33]. Daily Mg intake in adults normally averages The threshold of negative Mg balance that triggers 6–10 mg/kg [18]. Absorption occurs primarily in the je- compensatory mechanisms is not known. Even so, ion- 2+ junum and ileum [19]. Several lines of evidence suggest ized intracellular Mg [Mg ]i appears to be the ultimate 2+ that absorption involves a transcellular, saturable process regulatory signal [28]. [Mg ]i and intracellular bound involving facilitated diffusion and a passive intercellular Mg are exchangeable and are in equilibrium with extra- mechanism mediated by cationic electrochemical gradi- cellular Mg2+ [34]. Thus, ionized and bound intracellular 669 Magnesium in critical illness 203
Mg represent buffers whose chief function appears to be to skeletal muscle resistance to PTH is controversial maintaining constancy of the intracellular concentration [48]. 2+ 2+ + + + of free [Mg ]i. In human erythrocytes and other cells an Mg regulates K transport via the Na -K -ATPase 2+ + + increase in [Mg ]i by Mg loading is associated with Mg system as a cofactor. This action influences Na and K 2+ 2+ 2+ efflux via the Na /Mg antiport until [Mg ]i is normal- extracellular fluxes, which determine the electrical po- 2+ 2+ ized. Furthermore, reductions in [Mg ]i stimulate cat- tential across cell membranes [49]. [Mg ]i blocks out- ionic diffusion down a concentration gradient from high- ward movement of K+ through K+ channels in cardiac 2+ 2+ er levels of extracellular Mg [35, 36]. Consequently, cells. Decreases in [Mg ]i cause excessive outward 2+ + + Mg homeostasis is regulated chiefly by [Mg ]i which is movement of K even as intracellular K falls, thereby in equilibrium with both intracellular bound Mg and ex- inducing depolarization [50]. This critical role of Mg2+ tracellular Mg2+. Neither the magnitude nor the efficien- to maintain intracellular K+ concentrations is termed “in- cy of these compensatory mechanisms is known for criti- ward rectification” [51]. Mg2+ deficiency also impairs cally ill patients, in whom counterregulatory hormone re- K+-Na+-Cl– cotransport [52]. lease, insulin administration, and de novo renal and gas- In the nervous system Mg has a depressant effect at trointestinal dysfunction are common. the synapses; this is related to competition with calcium in the stimulus-secretion coupling processes in transmit- ter release. The best described of these is presynaptic in- Biochemical, biological, and physiological effects hibition of acetylcholine release at the neuromuscular of Mg junction [53]. The action of Mg as an anticonvulsant is related to noncompetitive blockade of N-methyl-D-aspar- Mg is important in physiological processes involving en- tate receptors. These are a group of glutamate receptors, ergy storage, transfer, and utilization [13, 37]. Mg com- stimulation of which leads to excitatory postsynaptic po- plexed to ATP is a substrate for signal-transducing en- tentials causing seizures [54]. zymes including phosphatases and phosphokinases on Overall, Mg2+ deficiency has the potential to impair the plasma membrane and within intracellular compart- oxidative phosphorylation, protein metabolism, and ments. Enzymatic reactions involving ATP require Mg2+, transmembrane electrolyte flux in cardiac and neural tis- which neutralizes the negative charge on ATP to facili- sues. tate binding to enzymes and assists hydrolysis of the ter- 2– 2+ minal PO4 bond [38]. Intracellular Mg regulates in- termediary metabolism by activating rate-limiting glyco- Assessment of Mg status lytic and tricarboxylic acid cycle enzymes [39]. Mg2+- 2+ + + 2+ – ATPases include Mg -(Na -K ) ATPase, Mg -(HCO3 ) Assessing Mg status in the critically ill beyond serum to- ATPase, and Ca2+-Mg2+ ATPase, which are involved in tal Mg levels is difficult. No single laboratory test tracks Na+, proton, and Ca2+ transport, respectively [40]. Mg total body Mg stores. In all, three groups of tests are indirectly affects protein synthesis by four mechanisms: available: (a) estimates of tissue Mg using concentra- (a) facilitation of nucleic acid polymerization, (b) en- tions in serum, red blood cells, blood mononuclear cells, hanced binding of ribosomes to mRNA, (c) acceleration or muscle; (b) metabolic assessments of Mg balance en- of the synthesis and degradation of DNA, and (d) regula- compassing isotopic analyses and evaluation of renal Mg tion of protein:DNA interactions and thus transcriptional excretion and retention, and (c) determination of Mg2+ activity [41, 42]. Adenylate cyclase also requires Mg to levels which utilize fluorescent probes, nuclear magnetic generate the intracellular second messenger cAMP [40]. resonance spectroscopy, or ion-selective electrodes Intracellular Mg2+ significantly affects Ca2+ and K+ (ISE). metabolism. As a divalent cation Mg2+ competes with Measuring total Mg concentrations in serum rather Ca2+ for membrane-binding sites and modulates Ca2+ than plasma has been preferred because additives such as binding and release from the sarcoplasmic reticulum anticoagulants may be contaminated with Mg or other- [43]. Complementary effects include maintenance of low wise affect the assay. For example, citrate binds Ca2+ as resting levels of intracellular Ca2+, thereby modulating well as Mg2+ to affect fluorometric (8-hydroxyquinoline) muscle contraction by noncompetitive inhibition of ino- and colorimetric procedures for Mg estimation [55]. As sitol 1,4,5-triphosphate gated Ca2+ channels [44]. Calci- indicated above, serum total Mg levels reflect Mg2+, the um metabolism is controlled chiefly through PTH; sub- protein-bound Mg fraction, and Mg complexed to an- stantial evidence indicates that Mg modulates Ca balance ions, and each component of the total value may change by its actions on PTH itself [45]. For example, impaired independently and in a nonlinear manner with respect to PTH secretion associated with hypomagnesemia results the other Mg fractions. in hypocalcemia. This is attributed to reduced Mg- Most clinical laboratories report serum total Mg con- dependent activation of adenylate cyclase in parathyroid centrations using colorimetric methods with calmagite or tissue [46, 47]. Whether Mg deficiency also contributes methylthymol blue as the chromophore [56]. As men- 670 204 J.L. Noronha and G.M. Matuschak tioned above, the chief limitation is that serum concen- tions weighted by their respective dissociation constants. trations represent only 0.3% of total body Mg content For Mg2+, these probes work well within the cell. Other [14]. Moreover, with the exception of bone, serum total fluorescent probes for Mg2+ have been described [65]. Mg concentrations are not correlated with other tissue Nuclear magnetic resonance spectroscopy estimates pools of Mg [57]. As for Ca, normal total Mg levels may Mg2+ noninvasively. Although several isotopes (19F–, coexist with ionized hypomagnesemia and vice versa 25Mg2+, and 31P–2) have been used to estimate Mg2+, the [58]. Red blood cell Mg determinations have no advan- α- and β-phosphate moieties of ATP have been used tage over serum levels and also are not correlated with most frequently [66]. other tissue fractions [57]. In normal subjects there is no Three ISEs for Mg2+ determination are currently correlation among Mg levels in mononuclear cells com- available: (a) the NOVA 8 analyzer (NOVA, Waltham, pared with serum or erythrocytes [59]. In a prospective Mass., USA); (b) the Microlyte 6 analyzer (Kone, Espoo, controlled study measuring skeletal muscle Mg concen- Finland); and (c) the AVL 988/4 analyzer (AVL, trations in 32 ICU patients with respiratory failure no Schaffhausen, Switzerland). In May 1993 the United correlation was found between serum total and muscle States Food and Drug Administration approved the Mg concentrations [60]. Lower muscle Mg levels were NOVA 8 electrode for clinical use, and most studies of associated with reduced intracellular K+ levels, a higher Mg2+ have used the NOVA 8 instrument. These ISEs em- incidence of ventricular extrasystoles, and a longer ICU ploy ionophores and neutral carrier-based membranes stay. designed to function in the presence of Ca2+ and other Physiological assessments of Mg balance require cations. Mg2+-specific ISEs yield rapid results on whole steady-state conditions for accurate results, conditions blood, plasma, and serum using samples between that are infrequent in the critically ill. A 24-h urine col- 100–200 µl. Ionized Mg concentrations in healthy sub- lection for renal Mg excretion takes into account the cir- jects using the NOVA 8 average 0.54–0.67 mmol/l [58, cadian rhythm of cationic urinary losses [61]. However, 67]. Serum reference intervals for the Kone and AVL an- existence of this rhythm during critical illness is un- alyzers are 0.47–0.57 mmol/l and 0.55–0.63 mmol/l, re- known. Even so, a 24-h Mg excretion rate of less than spectively [68]. No gender-related differences in Mg2+ 12 mg/day is acceptable evidence of Mg deficiency in have been described [67]. To date ISEs have been found the presence of serum total hypomagnesemia and normal to be selective for Mg2+; physiological concentrations of 2+ + + + + renal function [23]. The Mg tolerance test has been used Ca , Na , K , H and NH4 have negligible effects. for many years as a fairly reliable means of assessing to- Therefore the precision of these analyzers is suitable for tal body Mg status in patients at risk of hypomagnesemia determining Mg2+ in intensive care [67]. [62]. Subjects with normal Mg balance and renal func- The NOVA 8 and AVL analyzers correct signals from tion excrete most of a parenterally administered Mg load the Mg2+ electrode for concurrent Ca2+. Calculations of within 24 h [28, 62]. A generally accepted protocol in- Mg2+ and Ca2+ are normalized to a pH of 7.4 in the cludes: (a) a baseline 24-h urine collection for Mg, fol- NOVA 8 instrument, which also estimates Na+, K+, Ca2+, lowed immediately by (b) an infusion of 2.4 mg Mg per hematocrit, and pH [69]. The binding capacity and affin- kilogram of lean body weight in 50 ml 5% dextrose over ity of albumin for Mg2+ and Ca2+ varies with pH [70]; 4 h, and (c) a second 24-h urine collection. Differences hence the Mg2+ and Ca2+ levels are pH dependent. Be- in Mg content between the two urine collections repres- cause of pH changes during specimen storage, measured ent the retained Mg fraction. Retention of more than Mg2+ can be reported as the Mg2+ at the pH of the blood 20% of administered Mg is suggestive of Mg deficiency, sample (preferably) or as Mg2+ normalized to a pH of whereas retention of more than 50% is confirmatory 7.4. [40]. This test is contraindicated when serum creatinine exceeds 200 µmol/l. Furthermore, drugs or conditions producing renal Mg wasting invalidate the results. Using Mg deficiency in intensive care the Mg loading test, serum ionized Mg levels were found to be insensitive markers of Mg deficiency in 44 ICU pa- Ideally, Welt and Gitelman’s [71] definition of hypomag- tients without renal insufficiency [63]. However, con- nesemia as “a reduction in total body magnesium con- founding variables, such as the use of diuretics, prevent tent” defines true Mg deficiency. Unfortunately, this def- any firm conclusions to be drawn. inition of Mg deficiency is not in keeping with common- A major advance in evaluating Mg deficiency is the ly available laboratory technology. In spite of its imper- ability to measure Mg2+. In 1989 Raju et al. [64] modi- fections serum total Mg is still used as the standard for fied the calcium fluoroprobe fura-2 to improve selectivi- defining hypomagnesemia in intensive care patients. ty for Mg2+. The resulting compound furaptra (mag fura- 2) exhibits a shift in the peak excitation wavelength for fluorescence when bound to Mg2+ or Ca2+. The change in fluorescence corresponds to Mg2+ and Ca2+ concentra- 671 Magnesium in critical illness 205
Clinical manifestations of hypomagnesemia latory weaning attributable to hypomagnesemia have re- sulted in the widespread practice of frequent measure- Most hypomagnesemia in intensive care is asymptomatic. ments and vigorous normalization of serum total Mg lev- In theory, symptoms and signs occur when the serum to- els in ventilated patients. However, no controlled data tal Mg concentrations fall below 1.2 mg/dl (0.5 mmol/l) support this practice, and its putative physiological bene- [72], as summarized below: fit to respiratory muscle function remains obscure. In- deed, neuromuscular manifestations of serum total hypo- ● Neuromuscular manifestations magnesmia may be due more to concomitant hypocalce- – Positive Chvostek’s sign mia, even though tetany attributable solely to hypomag- – Positive Trousseau’s sign nesemia can occur independently of reduced serum total – Carpopedal spasm (tetany) Ca levels [75]. Overall, neuromuscular irritability and – Muscle cramps weakness appear to be related to the combined actions of – Muscle fasciculations and tremor ionized hypomagnesemia and ionized hypocalcemia on – Muscle weakness the neuromuscular apparatus. Hypocalcemia does not usually develop until serum total Mg is below 1.2 mg/dl; ● Neurological manifestations serum total hypocalcemia occurs in one-third of hypo- magnesemic medical ICU patients [76]. Hypocalcemia is – Convulsions usually refractory to Ca repletion unless Mg is first ad- – Nystagmus ministered [76, 77]. – Athetoid movements – Apathy – Delirium Neurological manifestations of hypomagnesemia – Coma Reported neurological manifestations of hypomagnese- ● Cardiac manifestations mia include convulsions, athetoid movements, nystag- – Supraventricular arrhythmias mus, apathy, delirium, and coma [40]. As mentioned – Ventricular arrhythmias above, the anticonvulsant effect of Mg appears to be via – Torsades de pointes a voltage-gated antagonist action at the N-methyl-D-as- – Enhanced sensitivity to digitalis intoxication partate receptor [54].
● Electrolyte disturbances – Hypokalemia Cardiac electrophysiology, hypomagnesemia, – Hypocalcemia and hypokalemia
However, manifestations of hypomagnesemia may de- The frequency and pathogenesis of cardiac arrhythmias pend more on the rate of development of the deficiency, during hypomagnesemia [78] are hard to establish be- on serum ionized rather than total hypomagnesemia, or cause coexisting hypokalemia is common. Whang et al. on tissue Mg deficits rather than on circulating levels [79] reported hypokalemia in 42% of hypomagnesemic [73]. Consequently symptoms and signs ascribed to Mg patients. Such hypokalemia is also refractory to treat- deficiency may be absent even with severe hypomagne- ment unless Mg is first repleted [74]. Although Mg per semia (serum total Mg levels <0.8 mg/dl) [72]. Such dis- se does not participate in the production of the cardiac sociations between serum total Mg levels and clinical action potential [80], Watanabe and Dreifus [81] showed findings make it difficult to infer total body Mg deficien- that Mg’s effects on cardiac transmembrane potentials cy, the need for correction of hypomagnesemia, and the varied in perfused rat hearts according to extracellular physiological benefit of such correction in individual pa- K+ levels. Increases or decreases in Mg levels with nor- tients. mal extracellular K+ concentrations causes minor elec- trophysiological changes. Alterations in serum total Mg concentrations are unlikely to destabilize sinus rhythm Neuromuscular manifestations of hypomagnesemia: unless accompanied by changes in other cations [80]. relationship to hypocalcemia Serum total Mg levels below 0.7 mmol/l are associat- ed with electrocardiographic changes indistinguishable Serum total hypomagnesemia is usually corrected be- from hypokalemia-related effects, including ST segment cause of concerns over neuromuscular irritability (e.g., depression, flattened T waves, and prolongation of PR positive Chvostek’s and Trousseau’s signs, tremors, fas- and QT/QTc intervals [38]. Arrhythmias associated with ciculations, and tetany) or weakness [74]. In particular, serum total hypomagnesemia include premature atrial the possibility of weakness and resultant delays in venti- contractions, atrial fibrillation, multifocal atrial tachycar- 672 206 J.L. Noronha and G.M. Matuschak dia, premature ventricular contractions, ventricular ● Drug-induced renal Mg wasting tachycardia, and ventricular fibrillation [82, 83]. Hypo- – Loop and thiazide diuretics magnesemia promotes digitalis-induced arrhythmias – Cisplatin [84]. The mechanisms are unclear but include: (a) in- – Cyclosporine A creased myocardial uptake of digoxin, (b) augmented in- – Aminoglycosides + + hibitory action of digoxin on Na -K -ATPase causing a – Amphotericin B + reduction in intracellular K [82], and (c) loss of the – Pentamidine and foscarnet 2+ membrane-stabilizing effect Mg on the myocardial cell – Colony-stimulating factor therapy membranes [84]. Mg therapy is recommended for tor- sades de pointes [85]. Despite these associations of low ● Hypophosphatemia serum total Mg levels with cardiac electrophysiological ● Hypercalcemia/hypercalciuria changes, purported links between low Mg and arrhyth- mias do not confirm a cause and effect relationship. Lack Endocrine causes include: of a standard by which to define a Mg-deficient state, co- existence of other electrolyte abnormalities, varying ● Hyperaldosteronism methods of arrhythmia monitoring, and inability to dis- ● Hyperparathyroidism tinguish between spontaneous and drug-induced arrhyth- ● Hyperthyroidism mia termination are all factors [80]. Moreover, a pro- ● Syndrome of inappropriate antidiuretic hormone spective uncontrolled study of 23 heart failure patients ● Diabetic ketoacidosis found no correlation between serum total Mg and myo- ● Alcoholic ketoacidosis cardial Mg concentrations [86]. Causes related to the redistribution of Mg include:
Causes of Mg deficiency in intensive care ● Acute pancreatitis ● Administration of epinephrine Singly or combined, Mg deficiency in intensive care has ● “Hungry bone” syndrome three main causes – (a) reduced intestinal absorption, (b) ● Massive blood transfusion increased renal losses, and (c) compartmental redistribu- ● Acute respiratory alkalosis tion, as detailed below. Other causes include: Gastrointestinal causes include: ● Cardiopulmonary bypass ● Nutritional disturbances ● Severe burns – Inadequate intake ● Excessive sweating – Mg-free fluids and total parenteral nutrition ● Chronic alcoholism and alcoholic withdrawal – Refeeding syndrome Nearly all data concerning hypomagnesemia during criti- ● Reduced absorption cal illness comes from measurements of circulating total – Malabsorption syndromes Mg. These do not shed light on the causes of Mg defi- – Short bowel syndrome ciency and likely underestimate ionized hypomagnese- – Chronic diarrhea mia and total body Mg depletion.
● Increased intestinal losses Gastrointestinal causes – Intestinal and biliary fistulae – Prolonged nasogastric suction Prolonged administration of Mg-free parenteral nutrition formulae and other intravenous fluids can precipitate Mg ● Pancreatitis deficiency, especially in patients with preexisting mar- ginal stores of Mg [87]. Vomiting and nasogastric suc- Causes related to renal Mg wasting include: tioning further contribute to Mg depletion [48], since the Mg content of upper intestinal fluids is about 1 mEq/l. ● Intrinsic tubular defect Diarrheal fluids and fistula drainage contain up to – Interstitial nephropathy 15 mEq/l total Mg ions [88]. Hemorrhagic pancreatitis is – Postobstructive diuresis an additional cause of acute hypomagnesemia with hy- – Diuretic phase of ATN pocalcemia due to formation of Mg and Ca fatty acid – Postrenal transplantation soaps in sites of tissue necrosis [89]. 673 Magnesium in critical illness 207
Renal causes controversial. Other hormonal conditions associated with hypomagnesemia are the syndrome of inappropriate anti- Renal Mg wasting is traditionally diagnosed when the diuretic hormone secretion [101] and hyperthyroidism 24 h urinary Mg excretion exceeds 24 mg in the presence [102]. of hypomagnesemia as assessed by serum total Mg lev- els [23]. Random or “spot” urinary tests for Mg are inter- esting albeit unvalidated diagnostic tests. Renal Mg Redistribution of Mg wasting has been reported with tubulointerstitial renal diseases, postobstructive diuresis, the diuretic phase of “Hungry bone syndrome” after parathyroidectomy [103] acute tubular necrosis, and following renal transplanta- or diffuse osteoblastic metastasis [104] can result in hy- tion [90]. Since Mg absorption in the thick ascending pomagnesemic, hypocalcemic tetany from osseous depo- loop of Henlé depends on the positive transmembrane sition of Mg and Ca. Epinephrine and other β-agonists potential created by NaCl absorption, alterations in NaCl (e.g., salbutamol) cause transient hypomagnesemia in transport by loop diuretics, 0.9% NaCl infusion, or os- healthy subjects [105]. This is thought to occur from up- motic diuresis promote Mg excretion. Loop diuretics (fu- take of Mg into adipose tissue as fatty acids are released. rosemide, bumetamide, and ethacrynic acid) are potent Release of fatty acids into the blood may also lead to the inhibitors of Mg reabsorption and are a common cause formation of insoluble fatty acid–Mg2+ and fatty ac- of hypomagnesemia in the ICU. Thiazide diuretics act on id–Ca2+ complexes [40]. Massive blood transfusion the distal tubule, where less than 5% of Mg is absorbed. (>10 U/24 h) may cause hypomagnesemia from the che- Short-term administration of thiazides does not produce lating effects of citrate [106]. Hypomagnesemia occurs significant renal Mg wasting, whereas long-term admin- during and after cardiopulmonary bypass surgery [84, istration may produce substantial Mg deficiency [40]. 107]. Potential mechanisms include hemodilution from Several drugs cause excessive renal losses of Mg. large-volume infusion of Mg-free fluids, removal of Mg Cisplatin causes hypomagnesemia in more than 50% of by the bypass pump, and catecholamine-induced intra- treated patients [91]; the incidence increases with the cu- cellular Mg shifts, and binding to free fatty acids [107]. mulative dose. Likewise, aminoglycosides induce mag- A retrospective study of 30 patients undergoing elective nesuria; 4.5% of 200 patients treated with 400 courses of cardiopulmonary bypass surgery demonstrated ionized aminoglycosides developed hypomagnesemia [92]. The hypomagnesemia in 73% [108]. Of note, the relationship total dose of aminoglycoside treatment in these studies between Mg2+ and Ca2+ during CPB was variable, and varied from 1.3–40 g and recovery from hypomagnese- Ca2+ levels did not predict Mg2+ levels [108]. Significant mia varied from 2–8 weeks. A recent prospective study hypomagnesemia (i.e., serum total Mg level showed ionized hypomagnesemia secondary to renal Mg <1.40±0.15 mEq/l) occurs in up to 30% of alcoholics. wasting in cystic fibrosis patients treated with a 2-week Multiple mechanisms are likely, including decreased Mg course of 33 mg/kg amikacin daily and 250 mg/kg cef- intake accompanying poor nutritional status, vomiting, tazidime daily [93], although no clinical correlation with chronic pancreatitis-induced steatorrhea, and Mg malab- ionized hypomagnesemia was performed. Amphotericin sorption [109]. B causes mild and reversible hypomagnesemia [94]. Bar- Collectively, the above data indicate that hypomagne- ton et al [94]. reported that reversal of amphotericin B- semia (serum total Mg level <1.5 mEq/l) may have mul- induced renal Mg wasting could take as long as 1 year tiple causes in the ICU patient. Even so, three critical following treatment. As with amphotericin B, cyclospo- questions remain: (a) to what extent does ionized hypo- rine A causes Mg deficiency secondary to defects in re- magnesemia parallel reductions in serum total Mg levels nal tubular function [95]. Parenteral pentamidine has and in total body Mg stores? (b) Does Mg replacement to also been implicated in hypomagnesemia secondary to correct levels of serum total Mg also correct ionized hy- renal Mg wasting [96]. pomagnesemia? (c) Is correction of serum total or ion- Hypophosphatemia is common during intensive care, ized hypomagnesemia associated with definable clinical particularly in insulin-dependent diabetics and during changes in biochemistry, electrophysiology, inflammato- Gram-negative bacterial sepsis [97]. Although hypo- ry responses or organ function? Until the answers to phosphatemia promotes magnesuria, the mechanism is these questions are forthcoming, we may be spending unclear [79]. Serum total Mg levels are inversely corre- considerable effort and expense merely to make serum lated with the fasting blood sugar level in diabetics in total Mg levels “look better.” whom glycosuria, ketoaciduria, and hypophosphatemia contribute to renal Mg wasting [98]. Primary [99] and secondary [100] hyperaldosteronism are associated with Mg, sepsis, and shock renal Mg wasting secondary to volume expansion, caus- ing increased tubular flow rates and decreased NaCl re- Novel immunoregulatory effects of Mg deficiency and absorption [99]. The exact mechanism, however, remains supplementation are increasingly reported [110, 111, 674 208 J.L. Noronha and G.M. Matuschak
112]. Such data suggest that reductions in circulating and carrying ability of hemoglobin and myoglobin due to in- intracellular Mg have important, albeit clinically occult teraction with heme proteins, and inhibition of enzymes immunomodulatory consequences during severe sepsis containing heme and nonheme iron-sulfur centers all and shock states. By enhancing generation of reactive O2 contribute to toxicity [122]. Overall, emerging data species [111] and cytokine biosynthesis, hypomagnese- showing interrelated links among biochemical, physio- mia can promote inflammatory tissue injury [112]. logical, and immunoregulatory effects of Mg deficiency Altura et al. [113] proposed that circulating free Mg2+ during sepsis and shock suggest the corollary thesis that ions are “natural” Ca2+ antagonists that modulate lethal titrated Mg supplementation can alter outcomes. Further cellular Ca2+ entry during shock. Lower Mg2+ concentra- experimental and clinical data are needed to confirm tions have been found to be correlated with efflux of this notion. Ca2+ from the sarcoplasmic reticulum of frog myocytes over a 0.3- to 3-mmol concentration range of Mg2+ 2+ [114]. A direct effect of low [Mg ]i to increase the volt- Ionized Mg and intensive care age-gated calcium current (ICa) was implicated. Based on this and other reports [115], Mg2+ deficiency may pro- Serum total Mg levels are not correlated with serum mote abnormal cellular Ca2+ entry during sepsis; this Mg2+ in the critically ill because of accompanying varia- may in turn increase free cytosolic and mitochondrial tions in plasma protein concentrations, acid-base bal- Ca2+ to cause cell death. In support of this, intracellular ance, metabolic derangements, and drugs that affect Mg Ca2+ has been reported to increase as tissue Mg2+ levels balance [58, 123]. Külpmann et al. [123] showed that re- decline in a rat endotoxic shock model [116]. Concomi- duced serum total Mg concentrations maymight reflect tant depression of mitochondrial respiration was restored “pseudohypomagnesemia” from hypoalbuminemia when after Mg2+ supplementation. concomitant Mg2+ concentrations are normal. Such find- Since considerable intracellular Mg2+ is complexed to ings have led to the suggestion that the terms hypo-, nor- ATP, sepsis, or ischemia/reperfusion-induced ATP hy- mo-, and hypermagnesemia should be restricted to Mg2+ 2+ drolysis or falls in ATP production release intracellular levels. Of note, [Mg ]i levels are correlated well with 2+ 2+ 2+ 31 Mg ions. Subsequently [Mg ]i concentrations rise, and serum Mg by P-nuclear magnetic resonance spectros- 2+ 2+ Mg effluxes from cells [115, 117]. Three negative con- copy [124]. In aortic endothelium [Mg ]i levels change sequences may result: (a) impaired Na+-K+ ATPase within 5 min of increasing extracellular Mg2+, suggest- pump activity, (b) reduced inwardly rectifying K+ ion ing that extracellular Mg2+ dynamically equilibrates with 2+ channels, and (c) dysfunctional cell membrane and sar- [Mg ]i [125]. Additional studies are needed to confirm colemmal Ca2+ ion channels [61]. These changes may whether extracellular Mg2+ accurately tracks total body partly account for the increased lethality of endotoxemia Mg balance. In spite of in vitro studies demonstrating the seen in rats during hypomagnesemia as well as the pro- superiority of ionized Mg measurements over total Mg tective effects of Mg replacement from endotoxin chal- estimations; few studies have attempted to demonstrate lenge [118]. the importance of measuring ionized Mg levels in the Mg2+ ions modulate key immunological functions, critical care setting and to examine the correlation of including macrophage activation, leukocyte adherence, ionized hypomagnesemia with clinical manifestations and bactericidal activity [119], granulocyte oxidative and outcomes. burst, lymphocyte proliferation, and endotoxin binding Salem et al. [126] measured Mg2+ and serum total Mg to monocytes [118]. In Mg-deficiency models time-de- concentrations in 180 critically ill patients. Serum total pendent increases are seen in circulating interleukin-1, Mg values were sensitive (75%) but not specific (38%) tumor necrosis factor-α, interferon-γ, substance P, and in predicting ionized hypomagnesemia. Increased supra- calcitonin gene related peptide [110, 112, 120]. Such ef- ventricular and ventricular dysrhythmias, seizures, hypo- fects may result from altered DNA binding of transcrip- tension, and death were associated with ionized hypo- tion factors notable for their suppression of inflammato- magnesemia (normal range 0.52–0.60 mmol/l). Recently, ry cytokine gene activation, including the cyclic AMP Huijgen and colleagues [127] evaluated the relationships response element binding protein [42]. Likewise, Mak between serum Mg2+, total body Mg estimated by Mg et al. [121] reported overproduction of nitric oxide in an content in blood mononuclear cells and erythrocytes, se- Mg-deficient rat model. In that report increased nitric rum albumin, and 30-day mortality in 115 critically ill oxide production was considered secondary to Mg defi- patients. A normal serum Mg2+ was found in 71% of pa- ciency-related stimulation of inducible nitric oxide syn- tients with total serum hypomagnesemic values. More- thase and activation of Ca-sensitive nitric oxide syn- over, neither total nor ionized Mg measurement was cor- thase from increased intracellular Ca2+. Cytotoxic ef- related with cellular Mg levels or with outcome. With re- fects of NO include those resulting from its combination spect to the cardiovascular effects of hypomagnesemia, with superoxide to form peroxynitrite [121]. Inhibition Kasaoka et al. [128] found that supraventricular and ven- of mitochondrial respiration, interference with the O2 tricular extrasystoles decreased by 50% and ventricular 675 Magnesium in critical illness 209 tachycardia was abolished by a 0.15 mmol/kg intrave- tion when indicated may be of value in reducing morbid- nous bolus of Mg sulfate (MgSO4) over 10 min, which ity after head injury or cerebral infarction. The positive increased serum Mg2+ from 0.35±0.06 mmol/l to data correlating neuromotor outcomes after head injury 0.54±0.09 mmol/l. MgSO4 had no effect in patients with and correcting ionized hypomagnesemia are currently a normal serum Mg2+. The ratio of Mg2+ to Ca2+ as a limited to animal studies only; more investigation needs modulator of vascular tone also increased after intrave- to be carry out to determine whether the same holds true nous MgSO4 and was thought to contribute to the antiar- in human head-injured patients in prospective random- rhythmic effect. Bertschat et al. [129] determined serum ized controlled trials. Mg2+ levels on days 1, 2, 3, 5, and 7 after myocardial in- farction in 42 patients, in addition to concomitant serum total Mg, free fatty acids, Ca2+, and total Ca. Compared Treatment of hypomagnesemia with serum total Mg concentrations, Mg2+ levels fell on the 1st day of myocardial infarction and were inversely Treatment recommendations for hypomagnesemia in in- correlated with serum free fatty acids. The ionized hypo- tensive care are confounded by the lack of controlled magnesemia was attributed to β-adrenergic induced li- clinical data regarding the directional changes in time- polysis and binding of Mg2+ by fatty acids. Since the matched serum total and ionized Mg levels, particularly benefit of intravenous MgSO during acute myocardial 2+ + 4 in relation to concomitant ionized Ca , K , and PO4 infarction is not established, the authors suggest that se- concentrations. In addition, renal insufficiency, adminis- rum Mg2+ rather than total Mg be measured in coronary tration of drugs which promote renal Mg wasting, and care patients, and that those with ionized hypomagnese- varying recommendations for Mg repletion are problem- mia be treated [129]. atic [140, 141]. An ideal ICU study to clarify these is- Frankel et al. [130] noted a poor correlation between sues would therefore have to first attempt to define the serum total and Mg2+ values in 113 trauma patients, al- measure of true Mg deficiency (total body, extracellular though injury severity or blood ethanol levels did not ionized, etc.) that is correlated with clinical manifesta- predict ionized hypomagnesemia. It has been hypothe- tions. The study would further need to control for distur- sized that decreased serum Mg2+ levels after trauma re- bances in other cations and drugs that interfere with Mg sult from increases in circulating catecholamines and balance and renal function and determine the clinical, corticosteroids, and to Mg redistribution within injured biochemical, and hemodynamic effects of correcting Mg tissues [131]. Ionized hypomagnesemia occurs after ex- deficiency with the ultimate goal of determining patient perimental head trauma [132] and in brain-injured pa- outcomes. tients [133]. In vivo animal studies have shown that pre- Nonetheless, several generalizations are appropriate or posttreatment with MgCl2 15 min after cerebral injury regarding the treatment of Mg deficiency: restores brain Mg2+ levels, improves motor function [134], attenuates cognitive deficits [135], and reduces ● Emergency (intravenous route): cerebral edema [136]. In a traumatic brain injury rat – 8–12 mmol Mg over 1–2 min model Bareyre et al. [137] studied serum Mg2+ levels – 40 mmol Mg over next 5 h 24 h postinjury and neuromotor outcome after 1 and 2 weeks. Supplemental Mg treatment given to rats with ● Severely ill (intravenous or intramuscular route) ionized hypomagnesemia reduced posttraumatic impair- ments. No such correlation was found using blood total – 40 mmol Mg on day 1 Mg levels, which did not change postinjury. In other in – 16–24 mmol Mg on days 2–5 vivo animal studies Mg treatment has been shown to re- duce posttraumatic edema and cortical damage, in asso- ● Oral maintenance ciation with concomitant changes in gene expression for – 12–24 mmol per day c-fos, heat shock protein-70, neurotrophins, and cyclo- oxygenase-2 [136, 138]. In addition to Mg’s multiple ef- Kidney function must be assessed prior to the initiation fects on intermediary metabolism, oxidative phosphory- of Mg therapy. Since the major route of Mg excretion is lation, protein synthesis, regulation of membrane perme- via the kidney, significant hypermagnesemia can occur ability to Ca2+ and K+ ions, and potential anti-inflamma- in the setting of compromised renal function. In general, tory effects, it has also been recently shown in murine when rapid Mg administration is needed, as for cardiac cortical cell cultures to be a potent antioxidant to iron- arrhythmias, the intravenous route is safe. It should, dependent oxidative injury [139]. By increasing the however, be performed with hemodynamic and electro- physiologically active ionized Mg fraction, MgCl2 possi- cardiographic monitoring as there may be significant bly restores the ability of cells to maintain homeostasis prolongation of intra-atrial and atrioventricular nodal [137]. Available data therefore suggest that early mea- conduction times [142] as well as hypotension. Davies et surement of blood ionized Mg levels and supplementa- al. [143] noted hypotension in three patients during 676 210 J.L. Noronha and G.M. Matuschak
Gram-negative bacteremic sepsis when Mg sulfate on total vs. ionized Mg levels, and clearcut physiologi- (MgSO4) was given using a rapid regimen (8 mmol in- cal endpoints have been performed. In general, 2 g travenously over 5 min). The authors did not mention the MgSO4 constituting 8 mmol intravenously over 1–2 degree of hypotension that occurred, nor the baseline min, followed by an additional 40 mmol over the next blood pressure and the use of vasopressors (if any) prior 5 h is considered safe and probably effective [141]. to Mg administration. No hypotension occurred when As discussed above, an antiarrhythmic dose of 48 mmol MgSO4 was infused over 24 h. Such hypoten- 0.15 mmol/kg MgSO4 given as an intravenous bolus sive responses may reflect the combined effects of sep- over 10 min was used by Kasaoka et al. [128] to correct sis-induced myocardial dysfunction together with Mg in- ionized hypomagnesemia (<0.40 mmol/l). Simultaneous fusion-induced reductions in systemic vascular resis- administration of K+ and Ca may be necessary because tance. In the critical care setting treatment recommenda- concomitant losses of these cations are common in Mg tions must therefore be tempered with the urgency of re- deficiency. Emerging data underscore the lack of a pre- placing Mg deficits. Slower infusions (mentioned below) dictable relationship between serum total and ionized are appropriate unless cardiac arrhythmias or seizures Mg levels, either before or after intravenous Mg supple- are present. Slow replacement can be achieved by giving mentation. Barrera et al. [144] were unable to predict 2+ 8–12 g MgSO4 intravenously over 24 h, followed by serum Mg levels from serum total Mg values in 33 4–6 g daily for another 3–4 days [40]. Since up to 50% ICU patients, in whom intravenous treatment with of administered Mg may be lost in the urine, continuous 4.1 mmol (1 g) had no effect on ionized Ca2+ or K+ con- infusions of Mg or repeated doses may be preferable. centrations, although both serum ionized and total Mg However, there are no controlled data with regard to the levels were increased. efficacy of this approach in critically ill patients. Oral Mg salts can be used as maintenance therapy in condi- tions associated with chronic Mg loss, for example, short Summary or long-term use of diuretics. An initial daily dose of 300–600 mg elemental Mg may be used. The Mg is giv- Mg metabolism and the important physiological roles of en in divided doses to decrease its cathartic effect. Sig- Mg as they relate to the critically ill have been reviewed. nificant hypermagnesemia can complicate Mg replace- However, fundamental aspects of Mg metabolism, as- ment when the glomerular filtration rate is less than sessment of Mg deficiency, and efficacy of treatment of 30 ml/min [13]. Elevation in serum total Mg to levels hypomagnesemia, whether total or ionized, remain poor- higher than 2 mmol/l are usually accompanied by symp- ly understood. Although serum total Mg continues to be toms. The effects of increasing rise in serum total Mg the most frequently used tool for diagnosing and treating levels include hypotension (1.5–2.5 mmol/l), electrocar- hypomagnesemia, randomized clinical studies are need- diographic changes (2.5–5 mmol/l), areflexia (5 mmol/l), ed to determine whether newer methods of Mg assess- respiratory paralysis (7.5 mmol/l), and cardiac arrest ment, including the measurement of Mg2+, are superior. (>12.5 mmol/l) [38]. Physiological antagonism of hyper- Newer insights into the immunomodulatory roles of Mg magnesemia with intravenous calcium gluconate can be in vivo, improvements in estimating whole-body and used until dialysis can be initiated. compartmental Mg concentrations, and clearer documen- With respect to cardiac arrhythmias and ventricular tation of the biochemical and physiological effects of arrhythmias in particular, recommended protocols for correcting hypomagnesemia will undoubtedly assist the Mg treatment are unclear as no large-scale controlled intensivist in determining the the rationale and the mode studies comparing replacement regimens, their effects for correcting a low Mg value.
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J Crit Care 15:36–40 lism. Arch Surg 100:343–348 S. E. Orfanos Pulmonary endothelium in acute lung injury: I. Mavrommati I. Korovesi from basic science to the critically ill C. Roussos
Abstract Background: Pulmonary with circulating blood cells, and lead endothelium is an active organ pos- to increased vascular permeability sessing numerous physiological, im- and pulmonary edema formation. munological, and metabolic func- Objective: We highlight pathogenic tions. These functions may be altered mechanisms of pulmonary endothe- early in acute lung injury (ALI) and lial injury and their clinical implica- further contribute to the development tions in ALI/ARDS patients. of acute respiratory distress syndrome (ARDS). Pulmonary endothelium is Keywords Endothelium · Lungs · strategically located to filter the en- Acute lung injury · Acute respiratory tire blood before it enters the sys- distress syndrome temic circulation; consequently its integrity is essential for the mainte- nance of adequate homeostasis in both the pulmonary and systemic circulations. Noxious agents that af- fect pulmonary endothelium induce alterations in hemodynamics and hemofluidity, promote interactions
Introduction the entire circulating blood volume before it enters the systemic circulation. Thus pulmonary endothelial func- The intimal lining of all blood vessels is composed of a tional and structural integrity are essential for adequate single continuous layer of simple squamous epithelial pulmonary and systemic cardiovascular homeostasis. cells of mesenchymal origin which are called endothelial Pulmonary endothelium is a major component of the cells (ECs). In the human lung ECs occupy a surface area alveolar-capillary unit; it is therefore vulnerable to injury of approximately 130 m2 [1]. Vascular endothelium was from noxious agents (mechanical, chemical, or cellular) considered for many years to be nothing more than a that are either inhaled or delivered to the lung through the nucleated layer, functioning as a semipermeable barrier pulmonary circulation and may cause acute lung injury that separates blood from the surrounding tissues and, in (ALI) in animals and humans (Table 2). the lungs, blood from air. However, extensive research ALI represents a pathological continuum characterized over the past 25 years has confirmed that vascular en- by acute respiratory distress and severe oxygenation im- dothelium is a highly specialized metabolically active pairment, occurring as a consequence of the host response organ possessing numerous physiological, immunologi- after exposure to noxious external or endogenous agents. cal, and synthetic functions (Table1). The strategic loca- The most severe extreme of ALI is the acute respiratory tion of the lungs and the tremendous surface area of the distress syndrome (ARDS), an overt noncardiogenic pul- pulmonary capillary endothelium allow the latter to filter monary edema that carries high morbidity and mortality
M.R. Pinsky et al. (eds.), Applied Physiology in Intensive Care Medicine, 215 DOI: 10.1007/978-3-642-01769-8_37, © Springer-Verlag Berlin Heidelberg 2009 1703 216 S.E. Orfanos et al.
Table 1 Major pulmonary endothelial functions in vivo animal studies, and EC culture techniques. It is Synthesis and release of several vasoactive compounds such as well recognized now that the pulmonary endothelium pos- angiotensin II, prostacyclin, thromboxane A2, nitric oxide (NO), sesses numerous enzymes, receptors, and transduction and endothelins; regulation of vascular tone molecules, and that it interacts with other vessel wall Expression of enzymes such as angiotensin converting enzyme, constituents and circulating blood cells. Major physio- endothelin converting enzyme, nucleotidases, NO synthase and lipoprotein lipase logical properties of the pulmonary endothelium include: Expression of receptors and signal transduction molecules (a) the promotion of antiaggregation and hemofluidity, (b) Cell surface redox activity (transplasma membrane electron trans- an enforced barrier function, and (c) the synthesis, me- port systems) tabolism, or uptake of vasoactive compounds that mod- Removal and biotransformation of drugs ulate the systemic (endocrinelike action) and/or pulmo- Regulation of coagulation and thrombolysis; promotion of hemofluidity nary vascular tone (paracrinelike action) [4, 5]. The latter Participation in immune reactions appears to contribute in the induction of hypoxic pul- Binding of immune complexes monary vasoconstriction (HPV), a unique physiological Interaction with bacteria (phagocytosis) and blood components feature of the pulmonary circulation that maintains proper such as leukocytes and platelets Expression of adhesion molecules ventilation/perfusion match and optimizes systemic oxy- Production of growth factors genation. Although the exact role of EC in HPV is still Production of cytokines and chemokines under investigation, EC-derived vasoactive compounds Production of reactive oxygen species such as nitric oxide, endothelin (ET) 1, and a yet un- Barrier function identified agent that may cause Ca2+ sensitization in the smooth muscle have been implicated [6]. Consequently, pulmonary endothelial injury is expected to compromise Table 2 Major agents that cause pulmonary endothelial injury adequate HPV and contribute to the ventilation/perfusion Endotoxin abnormalities seen in ALI/ARDS. Cytokines, chemokines The most important endothelial functions are presented Activated leukocytes in Table 1. Most of these functions are constitutive while Proteolytic enzymes others are induced upon endothelial activation after ex- Partially reduced O2 species Immune complexes posure to proinflammatory stimuli such as endotoxin and/ Microbes (e.g., rickettsial infection) or cytokines. In this respect the activated pulmonary en- Hyperoxia dothelium (a) expresses leukocyte adhesion molecules, Radiation (b) produces cytokines, (c) induces changes in vascular Drugs integrity and tone, (d) becomes procoagulant, and (e) Ischemia/reperfusion Hyperlipidemia upregulates HLA molecules [7]. ALI is associated with an Fibrin split products intense pulmonary inflammatory response with accumu- Actin and actin complexes lation of both pro- and anti-inflammatory mediators [8]. If Toxins the proinflammatory process dominates, endothelial ac- Mechanical stretch tivation is followed by functional and, at a second stage, structural endothelial injury, leading to alterations in all the above critical metabolic functions that contribute to [2]. ALI/ARDS is caused by an autodestructive inflam- ARDS pathogenesis. ARDS-related structural endothelial matory process characterized by the activation of intra- injury has been identified in humans: Postmortem studies pulmonary and circulating cells and by a tremendous in- of patients who died of sepsis-related ARDS revealed flux of neutrophils (although ARDS occurs in neutropenia) patchy EC swelling and injury [9], while a recent study and cytokine production, resulting in a breakdown of the found circulating ECs to be increased (i.e., increased EC lung barrier and gas exchange functions. ALI pathogenesis shedding) in sepsis and septic shock, suggesting a wide- is still only partly understood; however, pulmonary en- spread endothelial damage that should also include the dothelium plays a major role by: (a) altering its metabolic pulmonary endothelium [10]. activity, thus affecting pulmonary and systemic homeo- stasis; (b) mediating cell-cell adhesions, especially with neutrophils; and (c) changing its barrier permeability, thus Cytokines and pulmonary endothelium promoting pulmonary edema formation [3]. Cytokines are soluble polypeptides serving as chemical messengers between cells; they are involved in processes Pulmonary endothelial functions such as cell growth and differentiation, tissue repair and remodeling, and regulation of the immune response [11]. The various pulmonary endothelial metabolic properties ECs are both targets and cytokine producers. Among the were identified using isolated perfused lung preparations, more than 250 known cytokines, tumor necrosis factor 1704 Pulmonary endothelium in acute lung injury 217
Fig. 1 Schematic illustration demonstrating major endothelial func- prostacyclin; TxA2 thromboxane A2; PAF platelet-activating factor; tional properties in the normal lung (upper endothelial cell layer), t-PA tissue plasminogen activator; ROS reactive oxygen species; and mechanisms of pulmonary endothelial injury induced by in- PSGL-1 P-selectin glycoprotein-1; ICAM-1 intercellular adhesion fection, encompassing many of the major inflammatory interactions molecule-1; PECAM-1 platelet-endothelial cell adhesion molecule- among cytokines, macrophages, neutrophils, and pulmonary en- 1. Underlined Adhesion molecules; red arrows action; black ar- dothelium. LPS Lipopolysaccharide; TNF-a tumor necrosis factor- rows synthesis (and uptake for ET-1); dotted arrows location a; IL-1 interleukin-1; NO nitric oxide; ET-1 endothelin-1; PGI2
(TNF) a and interleukin (IL) 1 are produced mostly by member of the gp130 cytokine family that carries anti- mononuclear phagocytes, and natural killer cells. In the inflammatory properties, appears to attenuate the endo- lung they are mainly produced by activated interstitial and toxin-induced impairment of endothelium-dependent pul- alveolar cells (primarily macrophages), as well as ECs, monary vasorelaxation in an ALI ex vivo rat model [15]. and have a major role in the early ALI stage. TNF-a and Partial liquid ventilation with perflubron decreases serum IL-1 share a number of biological properties and marked- TNF-a concentrations in a rat acid aspiration model, thus ly amplify each other’s biological actions. They act on EC reducing the systemic sequelae of ALI [16]. The above mainly by inducing a functional program that promotes anti-inflammatory phenomenon might be related in part to thrombosis and inflammation [12]. Among other things attenuated leukocyte activation, which would consequent- they induce (a) a prothrombotic EC phenotype, (b) the ly attenuate leukocyte–EC interaction. Interestingly, it has production of several cytokines including chemokines, recently been shown that TNF-a installation into the al- colony-stimulating factors, IL-6 which has both pro- and veolar space sends inflammatory signals to the adjoining anti-inflammatory properties, and IL-1 itself, (c) the capillary endothelium, which in minutes upregulates the production of several autacoids such as prostanoids in- expression of the adhesion molecule P-selectin enhancing cluding prostacyclin (PGI2) and thromboxane A2, plate- leukocyte–EC interaction [17]. let-activating factor (PAF) and nitric oxide (NO), and (d) The cytokine-EC interaction in ALI pathogenesis has the upregulation of adhesion molecules (Fig. 1). All these also been shown in humans or human tissues. Pulmonary functions, with the latter being the most important, con- microvascular EC (PMEC) from ARDS patients present tribute to ALI/ARDS development [11, 12]. an upregulation of TNF-R2 receptors and a higher con- Several animal studies have revealed the pro- or anti- stitutive production of IL-6 and IL-8 than control PMEC, inflammatory contribution of cytokine–EC interaction in suggesting either a stronger EC activation occurring dur- the pathogenesis of ALI occurring from different insults. ing the ALI/ARDS process or that PMEC are constitu- In this respect acid aspiration induced lung injury in tively more reactive in subjects who subsequently develop rabbits is mediated mainly by neutrophils recruited in the ARDS [18]. Additionally, TNF-a induces IL-8 production lung by IL-8 and the subsequent endothelial injury [13], by pulmonary EC via the p38 mitogen-activated protein while IL-8 also mediates injury from smoke inhalation to kinase pathway; the underlying mechanism is regulated both pulmonary endothelium and epithelium in the same by the EC redox status, suggesting that anti-oxidant ther- animal model [14]. In contrast to this, cardiotrophin-1, a apy might be of value in the ALI treatment [19]. 1705 218 S.E. Orfanos et al.