INTERCOMPARISON PROCEDURES DOSMETRE TH N I F YO HIGH-ENERGY X-RAY AND ELECTRON BEAMS

REPOR ADVISORN A F TO Y GROUP MEETING ORGANIZED BY THE INTERNATIONAL ATOMIC ENERGY AGENCY AND HELD IN VIENNA 2-6 APRIL 1979

A TECHNICAL DOCUMENT ISSUEE TH Y DB INTERNATIONAL ATOMIC ENERGY AGENCY, VIENNA, 1981 The IAEA does not maintain stocks of reports in this series. However, microfiche copies of these reports can be obtained from

IN IS Microfiche Clearinghouse International Atomic Energy Agency Wagramerstrasse5 0 10 P.Ox Bo . A-1400 Vienna, Austria on prepayment of Austrian Schillings 25.50 or against one IAEA microfiche service coupon to the value of US S2.00. CONTENTS

REPORT AND RECOMMENDATIONS OF THE ADVISORY GROUP

Repor recommendationd an t Advisore th f so y Group...... 7 . APPENDI . I XIAEA/WH O postal dose intercomparison (TLD) for high energy X-ray . Instruction sheet...... 7 1 . APPENDI . XII IAEA/WH O postal dose intercomparison (TLD) for high energy X-ray therapy. Data sheet...... 21

EXPERIENCE WITH AND THE NEED FOR DOSE INTERCOMPARISONS

The IAEA/WHO thermoluminescent intercomparison used for the improvemen clinicaf o t l dosimetry ...... 7 2 . N.T. Racoveanu A surve f clinicallo y y applied dosimetry (Summary e reporth n o t IAEA/WHO postal dose intercomparison of cobalt-60 telecurie units with TLD) ...... 3 3 . Seelenta. W g Dose intercomparison programm Regionae th f o e l Reference Centre of Argentina ...... 45 R. Gonzalez, M.S. de Fernandez Gianotti Experience in intercomparison at an SSDL for orthovoltage and high energy beams ...... 51 G. Subrahmanian, I.S. Sundara Rao Bureau of Radiological Health Activities in Dose Delivery Surveys.. 57 R. Morton Status of in Nigeria and problems of accurate dosimetry ...... 59 A.O. Fregene

DOSIMETRY WITH FERROUS SULPHATE SOLUTIONS, TLD AND IONIZATION CHAMBERS e ferrouth f o s e sulphatUs e dosimete s transfea r r instrument for calibrating clinical dosimeters ...... 5 6 . J.P. Simoen Chartier. ,M Page. ,L s Measurement assurance studie high-energf o s y electro d photoan n n dosimetr radiation-therapn i y y applications...... 5 7 . Ehrlich. M , G.G. Soares

resultA e revieth f wo s obtaine NPL/PTe th y b dB Fricke dosemeter calibration servic German i e n radiological centres ...... 9 8 . . FeisH t FeSOf o somn e i ,us e e practicaTh l aspect high-energf o s y photon and electron dosimetry ...... 95 Wambersie. A Prignot. ,M Dutrei. ,A x Postal dose intercomparison for high-energy X-rays and electrons witD ...... TL h l Il . B.E. Bjärngard, B.—I. Rüden, P.J. Biggs, A.L. Boyer, K.A. Johansson, K.R. Kase Absorbed dose determination with ionization chambers in photon and electron beams ...... 9 12 . K.A. Johansson, L.O. Mattsson High energy radiation dosimetry and cavity theory - a re- examination ...... 7 13 . A.O. Fregene

ANNEX

Procedure Externaln si " Radiation Therapy Dosimetry with 5 Electro14 d nan Photon Beams with Maximum V EnergieMe 0 5 sd betweean V Me 1 n Recommendations by the Nordic Association of Clinical Physicists Reproduced witkine th hd permissio Actf o n a Radiologica

L/is't of participants 169 REPORT AND RECOMMENDATIONS OF THE ADVISORY GROUP

1. Introduction

radiotherapf o m Theai achievo t s besye i eth t tumour control with a minimum of radiation-induced complications in critical normal tissues. The implementatio thif no s object depends upon various factorse Th . present report, however, concerns itself specifically with the improve- ment of dosimetry and its uniformity.

All present biological and clinical evidence indicates that at a critical absorbed dose level ,differenca absorben ei d dos lesf eo s thaproduc$ 10 n e difference biologican si tumouls a effectr rfa s sa contro normad lan l tissue reaction concernee . sar 2] , d[l

A possible procedure for achieving the goal of improving dosimetry is to send an expert to the various radiotherapy centres and have an on-the- spot dose determination. Anotheachievinf o y rwa g this woulo t e db « greatly enlarge educational programme trainine th r medicasfo f g o l physicists and other persons responsibl radiatior efo n dosimetr thein yi centresn row . A third procedure is to make use of a mailed dose meter for the determination of absorbed dose.

A postal dose intercomparison programme of absorbed dose for Co y-rays was initiate IAEe continueds 1966n th ha Ai y d b large,a an n ,o r scale, since 1970 with WHO collaboration. Thermoluminescence dosimetry was used for this study. In 19?6, an Advisory Group to the IAEA recommended to extend the same technique for dose intercomparison to the field of orthovoltage X-rays.

présene Th t report deals witextensioe hth postae th f lno absorbed dose intercomparison programm high-energo et y photo electrod nan n beams.

The need for accurate dosimetry in this field is well recognized and results from the proliferation of these machines. The increased use of high-energy photo electrod nan n beams means thae earltth y indication oincorrecn fa t absorbed dos acutn shows a ea y enb skin reactios ni eliminated. Moreover reducee ,th d skin reaction allow higher sfo r tumour doses. In this situation the accuracy of the dosimetry is revealed only in late radiation effects with a latent period of at least several •- months. Therefor absorbee eth d dose give high-energy nb y photod nan electron beams mus wele tb l established. 2. Objectives

The objective plannee th f so d postal dose intercoraparison programme are simila thoso rt e formulate formea n di r IAEA report (TR 182). SNo . creato T ) greateea (a r awarenes neee correcr th dfo f so t dosimetry in radiation therapy. (b) To compare and improve the accuracy of the clinical delivery of the radiation dose. (c) To improve dosimetric consistency within and among radiation therapy centres. o identifT ) (d ysourcee th som deliver e f erroeo f se th o th n ri f yo target absorbed dose as well as methods by which these may be corrected.

3. Spécifia aims

presene th f o t m programmai e exteno t Th postae s ei dth l dose inter- comparison programme initiated by the IAEA and the WHO to high-energy radiation emitted by betatrons, linear accelerators, and other similar equipment, i.e.:

- X-ray maximuf so m energV Me 20tf yo 0 5 o - Electrons with nominal energy of 2 to 50 MeV

The dosimeters which nowo t ,p ,u hav e been propose used sucr dan dfo h postal intercomparisons are the PeSO, chemical dosimeter and the thermo- luminescence dosimeter. Their respective advantage disadvantaged san e sar discussed here, taking into account tneir general merits as well as practical considerations.

r thiFo s intercompariso dosimetrie choice th nth f o e c metno wels da l technicae th f o s la procedures shoul provido t suce db s ha determinatioea n of absorbed dose witr uncertaintn .a lesf yo s. tha5$ n+

As for the other energy ranges already investigated, the planned inter- comparison programme snould help in the assessment of the reasons for signi- ficant discrepancies sucf ,i h discrepancies occur.

4. Methods

4.1. General

methodo Tw s that coul usee db specifie meeo t dth t c aimthermoe sar - luminescence and ferrous sulphate dosimetry. 4»2. Thermoluminescence Dosimeters

4«2.1. Lithium Fluoride Powder

The ongoing IAEA/WHO postal dose intercomparison programme is based powderP ocharacteristics Li nsyste e it Th .d man s have been described elsewhere [3»4]> The reproducibility of the dosimeters irradiated in beamo C particularn ,i a bees $ ,ha n95 evaluatee 1,5+ th s i $t a d dan confidence level. This figure has been obtained by dividing the LiP powder eacn ,i h dosimeter int equao5 l part takind san averag e gth f eo these readings.

Preliminary experiments indicat energy-dependence eth systee th f meo for photons with a maximum energy of 4 to 25 MeV is less than 2$ [5].

Data frosame mth e experimental study indicate thaenerge tth y dependence of the system for high-energy electrons is greater than that for high-energy X-rays (i.e. 10$ in the range from 4 to 20 MeV).

4.2.2. Pressed Lithium Fluoride Thermoluminescence Dosimeters (TLD "chips")

Pressed LiP TLD chips have been used without build-up in surveys of dose delivery during clinical radiographie procedures sealen [6,7i d ]dan glass extensivn bulba r sfo e one-time teletherap o surveC f yo y dosimetry [8,9,10]. pressee th n advantage i d th LiD fors PTL mha powdeD eTL ovefasteP f ro rLi r reproducible readou equipmenn ti t lending itself readil partiao yt l automation of dosimeter handling. A disadvantage is the need for either individual dosi- meter calibration between successive mailings or for selection and calibration of dosimeter comparablf so e respons identicao et l irradiation.

The relative standard deviation from the mean response of individual cnips varies somewhat from dosimeter to dosimeter. On the average, at the 95$ confidence interval for the mean response of an individual bare dosi- meter chip irradiated 9 times at one given level and read in a hot-nitrogen reader it was about +1,0 percent; that for an individual sealed bulb in whicf, the two enclosed chips are permanently in contact with an electrically

r.eatable metal strip was about +_ Of6 percent. When the quantity of dosimeters thousandse handleth n i s becomedi t ,i s cumbersom keeo e t wit p pu h dosimeter identity. In tnis case, a batch calibration is preferable. If one selects a batch of dosimeters of which, on the average, the individual dosimeter readings var abouy yb percent3 _ t+ obtaine ,on measa n response fro9 m identically irradiated dosimeter percen5 9 e whicr th ts fo t hconfidenca e interva standare lth d deviatio percent5 abous ni 1, t+ . 4-3- Ferrous Sulphate Dosimeter (Fricke Dosimeter)

Tte ferrous sulphate dosimeter is extensively used by National Standardizing Laboratorie calibratior sfo intercomparisonr fo d nan , both by postal service 14], 13 ,, s Sinc12 [ll, eIAEe 1965th A , als carries oha d out postal intercomparisons based on this method [15]-

The following advantages of the ferrous sulphate technique are parti- cularly applicable here:

) 1 High precisio $ confidencn95 (withie th t a e0,5n+ $level accuracd )an y (within £ 2% for Co, better than within + 5$ f°r "the radiation qualities under consideration). 2) Change in the energy response of less than 1% for the radiation quali- ties under consideration. ) 3 Approximate water equivalence. ) 4 Dose rate independent response ovedose rth e rate rang clinican i e e lus 14], .[1213 ,

However, acceptable precision can only be obtained if particular care is taken in the preparation, handling and evaluation of this dosi- metric technique. Thus, from a practical point of view, certain dis- advantages must be taken into account : 1) The method is relatively laborious and expensive. 2) Since the ferrous sulphate solution is acid and poisonous, postal regulation mann si y countries prohibi conveyancs it t ordinary eb y mail. 3) The reliability of the solution might decrease when the time between preparatio evaluatiod nan n exceed monthsw fe sa . 4) Higher absorbed doses than those used in clinical application have to be delivered. energn A y) 5 dependent perturbation facto introduces i r glase th sy db container.

4.4« Recommended Procedure

It is recommended that the established Co postal dose intercomparison P powdeLi y extendee rb b higr.-energo dt y wate n X-raysi m rc 0 deptA .1 f ho capsulee th r recommendes fo si thesr dfo e irradiations. Correctionr sfo measured light versus absorbed dose givequalite wateth o nt r yrfo under consideratio nominae basee th b nn y do musl ma mad e energytd b ean .

It is recommended that the absorbed dose intercomparison for high- energy electrons also is by LiP powder. To meet the accuracy required , correction for the energy dependence has to be made. This correction can be made on the basis of nominal energy, supplemented by information derived from depth dose curves provide participante th y db .

10 For electron beams of energy lower than 8 MeV, experimental diffi- cultie determininn si dose gth e accurately witdosimeterF Li h s wil- lin disturbancee th creaso t fluence e th e du f so e dosimetecausee th y db r holders anit d additionn I . accurate ,th e positionin dosimetee th f go r become characteristice sth cruciao t e deptle du th hf so dos e curves energiesw alo t thesr Fo . e reasons unlikels i t ,i y thauncertainte th t y of the dose evaluation of + 5% can be achieved for energies <8 MeV. However, since electron beam thesf so e energie usee sar d clinicalld yan since their dosimetry is difficult, an intercomparison would be valuable even wit uncertaintn ha e rangth _f +n eo i y1C$ .

plannee th r dFo IAEA/WHO postal dose intercomparison depte ,th f ho irradiatio electror nfo n beanswil establishee lb d afte completioe rth f no experimentae th l study mentione action di - 5 n

4«5- Actions in Case of Intercomparison Discrepancies

All participants will be informed of their results and in particular of the deviation between the quoted absorbed dose and the dose determined by the IAEA. It is generally recognized that a deviation of up to jh 5$ in dose is within the presently accepted requirements for effective radio- therapy.

r largeFo r deviations importans i participane t th ,i r tfo investigato t e causee attempo t th d o improvt san s dosimetrhi e y procedure.

deviationr Fo s above recommendes i 10J& t i , d t..at IAEA/WHO take eth following measures: 1. Inform the participant immediately. . 2 Advis participane eth participato t nexe th t n planneei d inter- comparison. . 3 Attemp determino t probable th e e observee reasonth r sfo d dis- crepancy froanalysie datmth e th a f so shee providd an t e this informatio participante th o nt , together witguidee th copha f -yo lines compile thir dfo s purpose (see Appendi- x5)

For deviations greater than 15%, it is recommended that the following additional measures be taken by IAEA/WHO: 1. Send a letter immediately to the radiotherapist in charge and/or the phycisist who carried out the intercomparison, urging him to repeat the dosimetry and check all computations of absorbed dose. Tr.e contents of this letter should be considered strictly confidential, inasmuch as it may involve the treatment of patients.

2. If the preceding step confirms the previous results, recommend to to the participant to have his dosimeter calibrated immediately.

11 5- General Recommendations

While thernecessita s ei dosimetnr yfo c Intel-comparisol al r fo n energie modalitied san s use radiation di n therapy especian thera s i e l urgency to perfor n intercompansoa m dosimetrf no high-energr fo y y X-ra d electroyan n equipment. This necessit brougr.s yi t rapi e abouth dy tb proliferatio f o n this type of equipment and the possibility of serious dosimetry errors due to the complexity of the medical accelerators and trie dosimetric procedures. high-energr Fo y X-ray rise accidenf sth ko overdoseo t e du t increases si d reducee th y b d early skin reactions. Thu radiotherapise sth inadvertentln tca y deliver high doses without producing visible severe reactions.

Therefore, this Advisory Group recommends ï

1) Users of high-energy X-ray and electron machines should be encouraged to conduct radiation therapy only witparticipatioe htn qualia f no - fied medical physicist; internationan A ) 2 l postal absorbed dose intercompanson programmf eo high-energy photon d electronsan s shoul initiatee db IAEA/WHy db O earliese th t a t possible followee datb o et similay db r SSDL programmes. The following studies should be included: a) A pilot study should be conducted for high-energy X-rays. A sufficieit number of institutions in various countries and witn different macnines shoul includede db . b) For hign-energy electrons, the experimental study of precision d energan y dependencF systeLi e m th shoulf eo continuee db y db IAEA. Measurements with FeSO. should be included. It is recommended well-establishee th f o thae on t d centers already carryint gou FeSO. dosimetry provide this service. importance th n vie I IAEA/WHe f o w) th c f o e O intercomparison service, it is recommended that tne IAEA take measures to make this service availabl widea o et r international community, maintainine gth present high-leve performancef lo .

12 APPENDIX

IHTERCOHPARISON OF ORTHOVOLTAGE THERAPY DOSIKETRY

repore th reconunendationf n to I Advisorn a f so y Group Meeting, organized "by the International Atomic Energy Agency and held in Vienna, 6-10 December 1976, a pilot study of the X-ray postal dose inter- comparison technique for orthovoltage therapy was requested. The pilot study was conducted in the summer of 1977 sna. the results were reported [16].

The conclusion piloe th tf s o study were summaryn ,i : a) The external filter technique for determining HVL is practical ovequalite th r y rang interesf eo necessars i e d th tan r yfo purpose of correcting the TLD signal for the energy dependence of LiP. techniquD TL P Li ee provideTh ) b s sufficient precisiod nan reliability and meets the requirements of the Advisory Group (1976) that "the accurac dose th e f determinatioyo n should be better than £ 10$ and preferably £ 5$..

197e Th 9 Advisory Group confirms these conclusion recommendd san s that the IAEA/WHO and the SSDL's conduct intercomparisons in the ortho- voltage energy range using this technique, adhering to the conclusions piloe ofth trecommendatione studth d yan 197e th 6f so Advisor y Group.

13 REFERENCES

[I] Lanzl. L.H..; Why is a high accuracy needed in Dosimetry? Inter- comparison Procedures in the Dosimetry of photon radiation (Techn. Rep. Ser. 182), IAEA, Vienna (1970), 8l.

] Turesson[2 Notterd an Ski; . . ,I ,G n reactio biologicaa s na l para- mete contror fo r differenf o l t dose schedule correctionp ga d san . Acta Radiol. Ther. Phys. Biol (1976)5 .1 , 162, [3j Eisenlohr, H.H., Haider, J.G. and Rüden, B.—I«; International Postal Dose Intercomparison, Fifth Int. Gonf. on Lum. Dosimetry, Sao Paulo (1977), 350. [4] Bjarngard, B.E., Rüden, B.-I., Bisenlohr, H.H., Girzikowsky, R. d Raideran Evaluatio; . ,J e 197th 7f o n IAEA Pilot Studf yo Postal Dose Intercomparison (TLD Orthovoltagr )fo e X-ray Therapy. Nationa d Internationalan l Standardizatio Radiatiof o n n Dosimetry Vol Vienna, 1 . j IAEA, 319. ] Bjarngard[5 , B.E Rüdend .an , B.-I.; IAEA's Postal Dose Intercomparison (TLD) System for High Energy X-rays and Electrons, this publication, p.111 ] Crabtree[6 , C.L. Jamesond ,an Denta; 5. , l Exposure Normalization Technique "DENT" Instruction Kanual, HEW Publication (PDA) 76-8042 published by US Department of Health, Education, and Welfare,'Pood and Drug Administration, Bureau of Radiological Health, Rockville, Maryland. ] Jans[7 , R.G.;A Federal/State quality assurance progra mammographyn mi , In Breast Carcinoma, the Radiologist's Expanded View, Edited by Wende Logan, p.121. New York, N.Y. John Wiley and Sons, Inc., 1977. [8] Ehrlich, K...,. Welter, G.L.; Nationwide Survey of Co-60 Teletherapy Dosimetry, J. Res., National Bureau of Standards—A. Phys. and Chem., 80A, 663 (1976). [9] Soares, G.G., Ehrlich, L:.; Nationwide Survey of Co-60 Teletherapy Dosimetry, NBS Technical Note 978, US Department of Commerce (1978). [10] Thompson, D.L., Kearly, F.B., Uyckoff, E.O., Gitlin, J.N.; Nationwide Surve Co-6f yo 0 Teletherapy: Final Report, Techn. Rep., Sept. 1979, publishe DepartmenS U y db Healthf o t , Education Welfared ,an , Food d Drug-Administrationan , Burea Radiologicaf uo l Health, Rockville, Maryland. [II] Ehrlich, H. and Scares, G.G.; Measurement assurance studies of high- energy electron and photon dosimetry in radiation therapy applications, this publication. 75 . p ,

[12] Peist, H.; A review of the results obtained by the NPL/PTB Fricke dosimeter calibration service in German radiological centers, this publication, p. 89.

14 [13] Ellis, S.G.; The dissemination of absorbed dose standards by chemical dosimetr yFrickf o mechanis e eus dosimeterd man , Ionizing Radiation Metrology, ed. by E. Casnati (1977). [14] Simoen, J.-P,. ferroue th , f Chartiero s e sulPagesd Us an ; -. ,L. M phate dosimete transfes ra r instrumen calibratinr tfo g clinical dosimeters, this publication. 65 . ,p [15] Sanielevicid Naglan . ,J Dosisvergleichsmessunge; ,A. hochr fü n - energetische Elektrone Eisensulfat-Dosimetert nni , Strahlentherapie, 133 (1967), 36 x [l6] B.lärngard,, B.E. and Rüden, B..-I..; Report of Consultants' meeting to evaluat 197e eth 7 pilot stud postaf yo l dose intereomparison (Till) for orthovoltage-X-ray therapy, Techn. Rep. Ser. 182, IAEA, Vienna (1978), p.155«

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15 APPENDII X

IAEA/MHO POSTAL DOSS IMTE3COMPASISOÎT (TLP) FOR HICK ENERGY" X-RAY THERAPY

INSTRUCTION SHEET

ATTENTION; to obtain appropriate results IT IS ESSENTIAL TO EXPOS RETURD EAN N THESE DOSIMETER CASO N 3N I SLATE R THAN

to the address given in the covering letter. Exceeding the time limit entails uncertainties in the results. Such dosimeter evey n ma s e disregarded havb o t e .

If you are unable to carry out the irradiation before e datth e indicated above, t beforRETURse e e th eth N deadline, markin t gi tf£JH5XPQSS3" .

WARNING.: Capsules rar.ist never be exposed to heat (e.--;. sunshine), nor stored in a place where accidental exposure to ionizing radiation cannot be excluded.

TBOH-TTCAL INSTRUCTIONS :

Please read all the following instructions carefully before you start irradiating the cspcules. Aloo' complex e DATth e A SHEET carefully; onlyn a the s i n evaluatio e resultth appropriatf d no san e advice possible.

A. Preparatio e holdeth v;ate d f o nan r r phantom

1. The parts of the holder are shown in Piß. \. There is a long lucite tube with a hole in it across its long axis, attached to a (red) disc at one end. The disc has three holes. Also in! e showar I Fign . three (red) sticks e fittesticke b Th n . dca s holdee t^ dise intd s holee thei rth oan th n f i s read r usefo y . (Look s showa s n Fir;i n , ii.).

17 (Caution: the parts of ihe holder are to be handled carefully s otherwisa e deformation will resurlt).

. 2 Piec waterprooea f containe ry irateria madan f o e l available and. having a minimum length, width and height of 30 cm each, in a vertical X-ra^ beam. Alig containee centee th th n f o r r witcentrae th h beamle axith .f so

. 3 Plac holdee eth r intcontainee th o y thaplactie n sucwa i r th t a h c tube is aligned with the central axis of the b.eam. 4. Fill the container with water exactly to the level of the top end holdere th f o . Check that the plastic tube is completely filled with water-and, in the case the TLD capsule is tu be inserted while the holder watere th n ,i checs i k also thaalignmens cha.n/^edt it no s ha t .

. B ExposincapsuleF Li e gth s

e insertioTh D capsule TL performee b f o ny sma d befor holdee eth r is placed intcontainee th o r afte fule th rl alignmen holdee th f ro t wit X-rae th h y beam decisioe .Th usere th lefs i n.o t fielm c yout 0 a d1 rx norma0 1 a le sourcUs surfaco . t e1 e distance (BSD r sourc)(o centre-of-capsulo et e distancf ei normallu yo isocentrin a e yus c set-up).

2. Insert one of the three LiP capsules to be exposed by you into the hole at the upper part of the tube of the holder. Insert first the capsule th s showf botto o avoi o (a e Pigt n d ni ) en dm. iv openin g by accident. Place the capsule so that it shows extends equally on deptm botc 0 h hcapsul1 e tube sidet th th a e w f s so (Pigei No . .v) in water and ready for exposure (Pig. iii). Recheok alignment, water level and distance.

3» Calculat irradiatioe eth n time accordin methoe th o dgt u useyo y db in your daily practice ("Guideline calculatinr sfo g absorbed dose ...", ). Under these conditions irradiate one of the three LiP capsules to give an absorbed dose of 2 Gy (200 rad).

. 4 Remov capsule th e e froholdee th m pushiny rb g agains bottoe tth d en m of the capsule (Pig. vi).

5. Repeat procedure from 2 to 4 at the same machine with the same arrangemen othee capsuleso th r eac tw rtfo f ho exposee b o ,r t fo d the same time.

18 6. The capsule with white stopper is for the purpose of checking environmental influence capsulee th n so s during transpord tan storag irradiatede b d mus t ean tno t should;i , however e store,b d together wit otherse hth .

7. Throughout all procedures, handle the capsules very carefully to prevent opening and loss of powder.

C. Completion of the Data Sheet

Completio. 1 date th a f no shee essentias i tevaluatioe th r fo l f no dosimeter readings; dosimeters withou witr to h incomplete data sheet evaluatede sb wil t lno . Give more informatio additionan a n no l wisho s sheetu .yo f ,i

Indicat. 2 e irrelevant question y "NAapplicablest b No " = .

3. In the data sheet use has been made of the new SI units. The old unit givee sar parenthesn i n participantf .I s already employ thee th m givee b dat thesn y i n ama e units.

THANK YOU FOR HAVING BEAD AND FOLLOWED THESE INSTRUCTIONS

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19 APPENDII I X

IAFA/HHO POSTAL DOSE INT5RCOMPARISON (TLD) FOR HIGH-ENERGY X-RAY THERAPY

DATA SHEET

''Please use BLOCK LETTERS or typewriter, particularl r n=une yfo addressesd an s )

>'=•"» of institution ... Addres f institutioo s n

Form completed by ...... (name) (position) (date)

Signature ......

Previous participation in the IAEA/WHO Cobalt-eO TLD intercomparison 1 [ date...... s Ye ] N[ o . e IAEA/WHth n i r Oo orthovoltage X-raintercomparisoD yTL n No [] Yes [] date...... or in the IAEA/WHO high-energy X-ray TLD intercomparison ] [ date...... s Ye ] N[ o .

It is of great importance for the evaluation that all information requeste date th a n sheei d filles i t . in d The data sheet cannot cove possibll ral e measurement proceduresa f .I participant uses a procedure not covered "by the data sheet, he is rerjested to give full details of his method on pasre 4.

A. Specificatio acceleratoe th f no r

1. Type and model of accelerator Dat. 2 installatiof eo n Nomina. 3 l energ irradiatioe yth use r dfo n of the IAEA dosemeters

21 Detail Beaf so m dosimetry

Specification of dosemeter Typ) a doBemetef eo r (ionization chamber) Seria) b l dosemetenumbee th n ro r Dat) c calibratiof eo n Calibratin) d g laboratory Calibratio) e n facto Co-6r rfo 0 f) At which temperature and pressure calibratioe ith s n factor valid .mmHg g) Check source reference reading at tim calibratiof eo n h) in check source

Actual condition time f th eo t sa the calibration of the beam. a) Type of monitor chamber in the accelerator pressure Ar ) temperatud b ean r corrections applied to the monitor reading Chec) c k source reading d) Check source reading corrected for decay e) Dosemeter reading Temperatur) f phanton i e m during calibratio) C ( n g) Air pressure in the phantom during- calibration (mmHg) h) Correction factor for temperature and air pressure i) Or correction factor derived from check source reading Correctio) j n facto recombinatior rfo e th n i n dosemeter. Pactor(s) k ) useconvertinr fo d g dosemeter reading to absorbed dose to water Accelerato) l r dose monitor setting m) Medium for measurement

22 3. Beam dosimetry

1. Date for calibration of the beam . 2 Sourc detectoo et r distance (cm) 3. Source to surface of the medium distance (cm) a. Field size at the surface of the medium detectoe th t a rr ) o positioCT x m (c n 5. Beam calibration factor for the accelerator; a) absorbed dose per (Gy/mon^ depte th phanton i ht a (cmf mo ) b )

C. LiF-oapsule irradiation

Give values for only those factors th=t are used by you for calculation below. Write NA against whichever is not applicable. In your computation of absorbed dose to perturbatioe watercorrect th no r o ,d tfo n introduced by the LiF-capsule. 1. Date of irradiation . 2 Sourc wateo et r surface distance (SSD)(cm) 3. Field size at the water- surface or at the ) positio cm capsulF x Li m f no (c e . A Dose monitor setting 5. Absorbed dose delivered to water at the irradiation of LiF capsules (Gy) casn I e your calibration t identicadeptno s i h l wite hth depth at which the LiP capsule is irradiated '10 cm) please /riv followine th e g additional information. 6. Depth of calibration (cm) 7. Percentage deoth dose at calibration denth 8« Percentage depth dose at a death of 10 cm

23 . D Please giv arrive u figure detain yo ei th w t eldho a given in B.5 n cas.(i eclearlt thino s si y enough describee th y db data requested).

E. Pull details of measurement procedures if not covered by this data sheet (see pag. el)

P. If you have suggestions to improve this intercoraparison, please give details.

24 -r, i rt<- | TLI>

0

na 55 0 SAO Ti-a T- i l \ •fifi. P ' l t / r. \ I ôcm lOc-m W

Vl m

'} OSi-( i -no, f

25 Next page(s) left blank THE IAEA/WHO THERMO LUMINESCENT DOSIMETRY INTERCOMPARISON USED FOR THE IMPROVEMENT OF CLINICAL DOSIMETRY

N.T. RACOVEANU Radiation Medicine, World Health Organization, Geneva

Introduction

A number of papers have already presented .-UK! analysed t-lie IAEA/WHO TLD postal dose intorcompariso r Co-6fo n 1etlierapy e 0t . Mos f theso t e have been lie-votee methodologth o e resultt d th r o ys obtained without considerine us e th g of these result o improvt s e clinical dosimetr n centrei y s where this beeha s n shown necessary from the TLD results.

The present paper is based on the experience of the author in one of the Regional Office O wherWH n attempf a e o tins us -o TI/t t J result o improvt s e clinical dosimetry was made during the last five years.

Pa-suits of the TLD intcrcomparison in the Eastern Mediterranean Region of WHO

The results discussed here wore obtained from 23 radiotherapy departments located in universities or spocia1izcd hospitals in 12 countries of the Tastern Mediterranean Region. All the given data represent dose and not dose ratd weran e e obtained during 1971-1978 (TLD batches II-XXII) e resultTh . s are presented in Table I by country and radiotherapy department.

Of the 104 measurements undertaken in the 23 departments 53.9% did not exceed ^_5.0Z deviation froe giveth m n dose-1, whic s considerei h n acceptabla d e limit for clinical dosimetry. The remaining 46.1™ of i»oasurenients exceeded j|;5.1% and therefore fall into the category of unacceptable precision for clinical dosimetry. Of this latter group 25.9% exceeded ^10.IZ and of this 2.97. exceeded +20.1% deviation, as can be seen from the last line in Table I.

n observatioA s alswa n o made concernin e ratith gf positivo o o negativt e e deviations; positive deviations meaning doses given which exceeded the given vjlu d negativan e e deviations those administere f leso d s thae giveth n n value. All deviations in the range of -"-5.0 - ^10.07, are equally distributed in the positiv d negativan e e areas e ratith , f positivo o negativt a e being justa little ovee unity th rf O deviation. s greater than _+10.0 a %large r numbee ar r found to be negative, the negative/positive ratio beinr 1.7.

JLD results trends

Data from 1(> radiotherapy departments have been set out to show their chronologi cal evolution so that it r.iny be seen whether the 1 LI) interconiparison h.-id an influence on the precision of the clinical dosi:r.otry. The departments have been split into three categories according to their TLD results: !) radiotherapy departments with good results (graph 1); 2) radiotherapy departments with acceptable result s) radiotherap 3 (grjp. ; 2) i y departments with poor results (graph 3). The first and second graphs ci early show a tendency towards an improvement of the clinical dosimetry over the period covered and D e attributeintercompnrisob TL thi n e ca sth o t d n helpin e medicath g l physicists to check more carefull e parameterth l al y s involve e measuremeneh n e i d th f o t output of their Co-60 machines. Graph No. 3, on the contrary, shows that the D intcrcompariso'I. I o significann d ha n t influenc e procedureth n o e r measurinfo s g the Co-60 machine outpu n thesi t e seven radiotherapy departments. Onle on y department (Am s subsequentl)ha y produced deviations whic e positivar h d an e t diffeno o d r greatly froe measuremenon m o anothert t A secon. d department

Tl (15);) has two erratic values (one of +h.5 and another of -21.0%) and five correct values A thir. valueo d tw departmen s s ha whic c -20.0) ar hOr t % and -15.0% and one which is correct.

e deviationTh s encountere n somi d e other department ) deviatsKa (Al, La ,e fo a certair n minue perioth n si ddirectio n then suddenly after 1976-77 change to the opposite direction, only to alter again later on with the exception of Al, which remains with quite high positive deviations. This inconsistency of values obtained clearly shows inaccurate clinical dosimetry procedured an s shoul e followeh d n enquira e institute th y b do t y s concerne n ordei d o t r detect the sources of errors. IAEA and WHO should concentrate their attention n thoso e radiotherapy departments with results show Grapn i n . 3 h

Discussio e resultth d f counteo nan s r measure

In order to find an explanation for the deviations encountered a mission by a physicist with a calibrated secondary standard dosimeter was organized early in 1978 to the departments shown in Graph 3, with the exception of one. The finding f thio s s investigation were that:

the clinical dosimeters used by three of the departments were not working properly causing inconsistent data to be obtained;

the remainder of the departments had one or more dosimeters in perfect workin e procedurg th orde t r measuremenbu r fo e e machinth f o te outpus wa t inadequat e correctioth r o e n factors (pressure, temperature) were wrongly applieo lac t f reliabl o ke du d e instrument r sucfo sh measurements and/or inadequate trainin e locath lf o gmedica l physicists

As a result of this investigation a decision was taken to purchase three w clinicane l dosimeter r thosfo s e departments where faulty dosimeters were being used and to organize a refresher course on clinical dosimetry for medical physicists from all departments witli inconsistent results.

The experience presented here shows how the 1AI.A/WHO postal TLD inter- compariso usee o identift li d n ca n y places where clinical dosimetrf o s i y a low standard and to determine appropriate counter measures. In order to make further improvements it is suggested that the IAI.A/W110 Network of Secondary Standard Dosimetry Laboratories should be actively involved in the assessment and follow-up of TLD results and in undertaking appropriate action to raise the level of clinical dosimetry.

Another essential factoe considereb o t r s reducini d e ratheth g r lengthy delay betwee D dosimeternTL receipe th f n Vienno ti s d e sendinan th a t ou g resulte variouth o t ss radiotherapy departments throughou e worldth tf thiI . s e achieveb n ca a mord e direct impac n clinicao t l dosimetr e expectedb n ca y .

A final comment concern e sendinth s e d dosimeterreturth an g f o n d an s the need for improvement in this respect. The number of non-returned dosimeters remains high, some being los n mailini t g either r posprioo o tt r irradiatio^ d other.m t beinsno g irradiated becaus f equipmeno e tf ordero bein t ou .g

A gradual improvement in the number of dosimeters being returned has taken plac d bettean e r contact maintained wite variouth h s radiotherapy departments. Letters were sent to all departments to ascertain their willingness to participat a give n i en batc d dosimeteran h s sent onl o thost y e which replied positively. Reminders were sent to all departments which did not return the dosimeters by the fixed deadline and this has caused the number which have not been returned to decrease substantially.

Mailing the dosimeters represents another constraint as postal and custom authorities sometime e x-rayus s o chec t scontene th k f packageo t r o s fear that packages might contain explosives Eastere th n I n. Mediterranean Regio e existencth n f diplomatio e c pouche e participatin th o mos t sf o t g countrie f greao s twa s hel n forwardini p d recoverinan g dosimeterse th g .

28 Table I

TLD Results expressed in Percentage Deviation from the (Uven Dose for 3 Radiotherap2 y Department 2 Easter1 n i s n Mediterranean Countries

f measuremento . TotaNo l No.os ideviatio-wit % a h n Couny tr RT Dept. Measurements +5.o t 0 0+ ' +_5.1 to +J0.( +_10. +20o t 1 . over +20.1 1971-1978

1i N | 5 5 0 0 0

2 Al 6 0 3 2 1 Cu 4 1 (1 3 0 Ccl 6 4 0 2 0 Cm 3 0 1 2 0

3 A 2 2 0 0 0 Is 3 3 0 0 0 Sw 6 4 2 0 0 Tel 5 3 2 0 0 TMH 2 1 0 1 0 1

4 Bg 7 5 1 0 1

5 Ha 4 4 0 0 0

f, Ani 5 0 2 3 0

7 Sll 6 5 1 0 0

8 TU 5 2 1 2 0

9 Ka 7 2 1 3 1 La 6 2 0 4 0 II 4 1 3 0 0 M 2 0 2 0 0 P 4 1 1 2 0

J 10 Ku 4 4 0 0 0

] 1 D 2 2 0 0 0

12 Tu 6 5 1 0 0

TOTAL: 23 104 56 21 24 3

% - 100.0 53.9 20.2 23.0 2.9

29 TLD INTERCOMPARISOIM IN EMRO 1- RADIOTHERAPY DEPT WITH GOOD RESULTS

2 - RADIOTHERAPY DEPT. WITH ACCEPTABLE RESULTS 5

4

3

2

1

0

1

2

3

4

5

6

7

8

9

10

11

12

13 _1_J———l————L ' m a 2 H ' n ZI ' SCQ XE7 wn n xx i xx 3 7 2 7 1971 74 75 76 77 78

30 3- RADIOTHERAPY DEPT WITH POOR RESULTS

n m s vm xi ZED SDK 1971 72 73 74 75 76 77 78

31 Next page(s) left blank SURVEA CLINICALLF YO Y APPLIED DOSIMETRY

W. SEELENTAG* Radiation Medicine Unit, World Health Organization, Geneva

1. Introduction

Biological evidenc s beeha e n.V. obtainee Andersoth t a d n Hospital, Houston,

Texas-, accordin c whict g a differenchn arrlie i « -7 e V ctherapeuti f th o dose n i e c ranee already result n increasei s d tumour recurrenc e cas f th underdosago e n i e n i d an e aggravated side effects and darcap.e in the case of overdosage. Unavoidable uncertainties in tur.our localization and definition of the tumour volume in clinical routine work occupy practicallv fully this therapeuti e accuracc e physicath rane th d f an eo v l aspects of clinical dosiir.etrv should therefore be much better than ^7%. The absolute accuracy of the realization of radiation units in Primarv Standard Laboratories, e.e. NBS, NTL, ?TE, is ouoted in calibration certificates for clinical dosimeters to be about *2 to 3%. Experience in the IAEÂ/KHO Network of Secondary Standard Dosimetrv Laboratories (SSDLs) bv intercomparin e calibratioth g a referenc f o n e instrumen 7 laboratorie1 n i t s has, however, demonstrated that the calibration of secondarv standard dosimeters and the transfe e uni f radiatioth c t f ro a "fiel o t n d instrument" aareworldwida n o e e scalo t e ^uch bette f appropriatelri tha " -2 n y performed.

One maior component of WHO's programme for imrovine, promoting and strengthening radiothera^v as an essential part of cancer control is therefore clinical radiation dcsi^etry. Three approaches are used:

) (a prorotic e traininth f d educatioo n an g f redicao n l physicist d theian s r appointment in radiotheranv institutions as partners - not iust auxiliarie e radiotheraristth f o - s ;

(b) establishing in all W.O Regions '/HO Coilaboratinc Centres for Secondarv Standard Dosin-.etrv (SSDLs n orde)i o facilitatt r e useth f o r r fo e radiation e radiotherapth , y institute, acces o calibratint s g facilities where the clinical dosimeters can be calibrated and regularlv recalibrated.

* Present address: Bundesministeriu Innerns mde Bonn3 ,5 , Postfach, Federal Republic of Germany.

1 Shukovsky, L.J.: Dose, time, volume relationships in squamous cell carcinoma of the supragloltic larynx; Am. J. Roentgenol. 108 (1970): 27-29.

33 This is necessarv as individual dosimeters varv in sensitivity and energy response, etc., and their characteristics mav even change with time. Accurate calibration of a dosimeter is, therefore, the first prereauisite fon accurata r e measuremen f doseo t . Furthermore n SSDa , L should builp u d regional and local expertise in the field of dosimetrv, act as regional or national advisor to the user (radiotherapy institutes, but also radiation protection services and e.g. industrial users of radiation), and undertake educationa d traininan l g activitie n radiatioi s n physic d dosimetrvan s . e targeTh f thio t s programm e availabilitth s i e t leasa e appropf on to v - riately qualified SSD eacn i L h maior f radiatiocountro e us whicn i ve nth h and radionuclide t iusno ts i snegligibl d easan e v accesa n SSDa n o i Lt s neighbouring countrv for the user of radiation in a country without its n nationaow l SSDL o meeT . t that target n closi , e collaboration witd an h e initiativth e Internationan o th f o e l Atomic Energy Agency e join,th t IAEA/WHO Networ f SSDLo k s establisheswa n 197i d d includepan t Septembe(a d r 1978) already 39 regular members, and 11 affiliated members (Rational Primary Standard Institutes, e.g. the National Bureau of Standards, NBS, Washington).

(c) Performing dose intercomoarisons and survevs for radiotherapy institutes which allow the following to be checked:

(i) the validity of calibration of the clinical dosimeters used;

(ii) the accuracy of the irradiation equipment including its shutter mechanis d timinan m g procedure;

e abilite institute'th (iiith f )o y s staf o accuratelt f y set-up patients (checke v measurementb d n simplo s e phantoms);

(iv) the professional capacity of staff to reliably irske the dose calculations necessar r applyinfo v g radiotherap - sucy h surveys furthermore allow:

) (v e individuaadvice giveth b o o t t ne l institut n casi ef pooo e r results on how to improve the quality of work and avoid mistakes;

(vi) decide whether sendin a consultang e institutth o t t o chect e k locall e procedureth y s applie d providan d e local trainins i g necessarv to improve the situation", or,

(vii) conclude that due to the frequency oc events in ?. eeoeraphical region it is desirable to establish local or regional training activities in order to improve generally the level of professional competenc e relevanth n i e t countr r reeiono y .

e long-terth n I n plannin s expectei t i g d that finally each national SSDL, M IfflO Collaborating Centre or ember of the IAEA/WHO Network of SSDLs, performs such intercomparisons and surveys independently of each other in their geographical are f competenceo a . International coordinatiov b n e Networth r s suco a k O h WH wil IAEd lan A the e limiteb n o harmonisint d q the methodology applied by the various SSDLs to »-aV e their results internationally comparabl o chect d k an e'-hethe r svsteratic deviations occur.

Some SSDLs have already starte o implement d t thei n programmeow r r fo s "postal dose intercomparisons e participatinar d an " n internationaa n i g l e IAEAprogramme r th comparin fo ,y b n ru ,g such programes e majoritTh . y of countrie n thii s s world are, however t covereve t y sucno b ,d h national or regional programmes and this is the reason th,at IAEA and WHO still continue the "IAEA/WHO Postal Dose Intercomparison Programme". An evaluatio s resultit e f presenteo nar s n thii d s paper.

2. The IAEA/WHO Postal Dose Intercomparison Programme

Apart from sendin n expera g n dosimetritow wit s hhi c equipmen radiotherapa o t t y institution (RTI) for checking all procedures applied, there is only one possibility for intercomparin d surveyinan g g clinical dosimetrv: thi s sendini s y mai (b r gthrougo l h other channels of communication) a dosimeter to the RTI, with the request that it be irradiated under prescribed conditions wit prescribea h d absorbed dose d measurinan , e th g

34 absorbed dose received by the dosimeter after it has been returned. Unfortunately, the classical dosimetric metho measurinf o d numbee th g f ionizationro s produce y radiatiob d n in a defined volume, is not appropriate for that purpose. Other effects of radiation on matter need to be used. Considering the existing possibilities therefore IAEA in 1969 decided to investigate the use of the "Thermo-luminescent-dosircetry (TLD)" -principle for "postal dose intercomparisons". Detail f thio s s principl describee ar e mann i d y publication d therefor an st repeate no e ar ed here.

n 197I O joine0WH de implementatio th fAE n i A e IAEA/WHprojece th th d f o nan t O Postal Dose Intercomparison Programme started n thiI .s programme IAEs responsiblAwa e r preparin fo D set TL dosimeterf o se th g measurind an s radiatioe th g n dose receivey b d the sets returned, WHO took care of the distribution and recollection of the dosimeters throughou worlde th td acte,an d together wit evaluatiohe th IAE n Ao f resultso n d ,an initiating corrective measures where necessary.

followine th n I resulte IAEA/WHe th gth f so O Postal Dose Intercomparison Programme are described and critically evaluated.

1 Methodolog2. y

Lithiuro-fluoride powde plastin i r c capsule representins- thermoluminescena g t dosimeter (TLD sens i participatino t )- g institutions e instituteTh . e ar s requeste irradiato t d e these capsules under prescribed conditions wit prescribea h d radiation dos d returean n them throug O channelWH h IAEAo t s , wher radiatioe th e n dose receive e capsuleth y b dmeasureds i s e "setOn . f dosimeter"o s consistf o s 6-10 cansule differenf o s t kinds intende evaluato t d dosee th e , doserate, additional dose received r "fading,o " during transport d consistenc,an resultsf o y e Th . institutes also "data fil n i la sheet" whicn ,i h they describ w theeho y calculated and arrived at the dose given to the capsules. The difference between the measured d quotean d dose give n percenquotei e n th f do t indicate e accuracth s f dosiroetro v y e relevanth n i t institute, whereb negativa y e deviation means thadose th te really administered was smaller than intended (quoted) and vice versa. Accordingly, completed "data sheets" frequently enable the source of errors to be located. In other cases comprehensive correspondence, repetitio measuremente th f o n r eve,o n sendin expern a g dosimetryn ti , solve problee th s d improvean m e accuracth s f o y radiotherap e relevanth n i y t institute.

2.2 Results 1969-1978

Documenn I D 40/7tRA evaluatio n 6a resultf no untip u s l 197 s provided6wa . The present evaluation, covering the period from 1969 to 1978 is, however, not just an extension from 1976 to 1978, but a revaluation of all data available by. September threo 1978t 0 set 8 o dosimeterf eo so .Tw t batche 0 4 f o ss were distrib- uted and recollected annually. Details of the batches and their distribution to O regionWH x e showsi ar s A Tabln totae i n th f . 101o 1 le 1 set f dosimetero s s have been distribute f theo d r% ove recollecte85 year0 1 rd an s d evaluatedan d needt I . s to be mentioned that onlv a few of the unreturned, unirradiated or unevaluable dosimeters (all included in the tables as "not returned") were "dropouts" due to condition f controusere o th t ,f ou slo e.g . failur mailinf o e g services, etc. Unfortunatel majorite th y y reflect e carelessnesth s participatine th f o s g institute d lac an f intereso k improvinn i t n workow qualite s . th git Considerinf o y g that material costs and the work of international staff involved amount to approximately US$ 50 per set of dosimeters, the waste of 15% of the dosimeters distributed is a wast f aroun0008 eo $ ,US d leadin o considerationt g whethef o sjustifiabls i t i r e to perform such intercomparisons free of charge for the participating institutions, particularly as they represent direct assistance to countries rather than an investigatio purpose th r f IAEWHOeo nd fo an A . Chargin r participatiofo g e th n i n programme would, however, havadverse th e e effect that manI interesteRT v n i d improving their quality of dosimetrv are prevented from participating for administrative and budgetary reasons.

A similar observation was also made by WHO in distributing free of charge personnel monitoring dosimeters (film badges), which were fullv financed bv extra- budgetary contributions (provision to WHO free of charge bv the Service Central de Protection contre les Rayonnements ionisants under Professor P. Pellerin and the Personnel Monitoring ServicGesellschafe th f eo Strahlenschutzr tfü , Neuherberg, under Professor Wachsmann). Here again reture ,th n rat mucs i e h lower than when participant e chargedar s e misusTh .wastd an ef service o e s provided fre f chargo e e is a serious problem which needs further consideration.

35 In Table 2 data for 1969 to 1978 are split into VHO Regions, Africa has not vet participated e programmth n i e (aoart froir pilot studie whicn i s n 196i h 9 South Africa and Southern Rhodesia were involved). RT has developed on this continent durin e lasw yearth gfe t s onlt thibu y s momentum will increas futuree th l n Al i e. othe O regionWH r s particinated nearlv eouallv with aroune th 5 eac f 1/ do h distributed dosimeter sets. Seventy countries, representing more thae n th hal f o f O MembeWH r States participated d altoeethean , I throughouPT 6 41 rworle th t d were checkedf theo n% participate50 . d once onlv 7 mor10 ; e tha 5 timesn e relativelTh . v high rat f 32-33o e f institute%o s participating nore tha Eastere 5 timenth n i sn Mediterranean (EM d South-Eas)an t Asia (SEA) demonstrate specifie th s c interesf o t some RTId Darticularlan s e Regionath f o v O Regional WH Adviser e th ln i Offices o t s e situatiogeth t n under control. Considerable differences exist between regionn i s the percentage of "not returned etc." sets. This rate of "waste" is below 102 for e South-Easth r fo % e Europeat 21 th Asi d Westerd an aan n8 1 s higRegion a s a hd an n Pacific Regions respectively.

n e Tabl"noI th t3 e returned etc." set f dosimetero s e listear s n relatioi d o t n the frequenc e programmeth f participatioo n s vinterestini i t I I RT . n a o t gf o n note that 38% of all institutes which participated once or several times did not retur e dosimeterth n t leasa s t l instituteoncd 7.5al an t e retur f no %o d ndi s them two or more tines. It is unfortunately obvious that such failures are not normally e mailin e faulth th f o tg svste ? countr n i md failur an v o returt e dosimetea n r should thereford unreliablan d ha e judge eb a es a resultd .

e followingth n I , however, onlv result f returneo s d measurablan d e setf o s dosimeters are analvsed. Table 4 provides the summary of data split according to WHO "eeions and into periods of time, I including batches I to XI, and II including batcheo XXIIt I I XI srespectively e periodTh . s coveyeare th r« 1969-197 d 19743an - 1978 resuectivelv r botfo h m periodsu e s alsTh i s. o nuote worle th wels a dds a l total. Finallv, the results in a number of sinele countries are given wherebv the relevant O RegioVP s mentione i ne country' th t bu d s name codified. "Results e interth f -o " comparison are expressed as % deviation of the dose measured from the TLfi by IAEA (M..) and the dose auoted bv the relevant RTI as havine been administered (0) to

the M cansules according to the formula.

M M -O Deviatio ——-—0 = ' 10 n x —

e evaluatioth r Fo 7 classen f deviationo s e definedar s :

% = +10. 20 D o t 1 +5.= % 10 C 1o t = % +2.5 = +27.B A o 1t

E = +2O.1 to 50% F = +50.1 to 100% and G = above +100%

In Table cumulativth 4 e e percentag numbee th f resultf relevane o ro e th n i s t clas e auotedar s . e tota100th %ls i numbe f dosimeteo r r sets returne d evaluatean d d for the relevant line. The third column therefore gives the percentage of results within +2%, the fifth column those within +107- (= the sum of class A + E + C) . The sixth column includes the sur of D and all higher classes; in other words, all result e qualitTh s abov f result. e variouo y on th e o n s +10i s s d classe%an e b n ca s defined as: A = excellent and a deviation of this size is not significant as it is within the maximum achievable accuracv of the TLD nethod under the given conditions. B = good and some values in this class near to 2% rav even result from exceptionally greater rando D methodmTL e error f neareth 7 thei ;5 f o syo t rshould , however, lead to a check being made of the irradiation and calculation procedures and the deletion f smalo l errors, when detected .t eoono Clas d= althougo C serious to d t an sno h should lead to a careful checV being made of all procedures applied, including perhap a srecalibratio e dosimeteth f o n f thii r s e samresulth e n i directiot n (either olus or rinus) is repeatedly obtained. The error in class D is totally unacceptable for effective radiotherapy and immediate steps need to be taken to locate and correct the error and improve the quality and accuracv of work. Class E and higher mean a total disaster if patients are treated vitb that accuracv. Serious conseouences will result and immediate expert advice from outside the RTI, perhaps fro nearba m y SSDL, shoul e requesteb d o locallt d y chec proceduree th k s applie d givan de on-the-spot training.

36 In the last columns the nutr.beT of countries included in the relevant line, the numbe f participatino r nun-bee gth PTlf dosineted o r an s r sets distributed e givenar , . The final colunn gives the dosimeter sets vhich have not been returned, not irradiated r cannoo e evaluateb t r varioufo d e numbeth s f f setreasono o r % s n distributedi s .

Although the table is self-exnlanptory a few noints mieht, however, be extracted: the results vary considerablv between the various regions. Africa (AF) should not be considered in this context as only a few selected RTI participated in the first pilot batches, in order to check the suitabilitv of the intercomparison method. Good results withi T deviatio+5 n n ovewhole th r e period 1969-1978 were observe a littl r fo de ove% 5^ r neasurerente oth f Latin i s n America (Latin-AM), Eastern Mediterranean (EMd )an South-East Asia (SEA), whereas Europe (EV Westerd )an n Pacific (VT) regions show more than 60 to 703 good results, compared with 59% for the world total. 28 and 29% of the results were not acceptable at all (more than +10% deviation) in Latin-AM and EM e worlrespectively e resultth th dr f fo o totals . % 27 20 . ,d comparean D E r dfo wit% 10 h for Latin-AM were out bv more than +50% during the first period and 0.5% for the world total in both periods.

A review of the data split according to single batches was made to check whether the situatio d irproveha n d vear0 durin 1 programme e th s th e s beeeha n runningt . no Thi s swa demonstrate e proportioth s a d f eaco n h batc e differenh th sen o t t regions varied considerabl programme th d an y e increasingly concentrate n regiono d d countriean s s mosn i t need of advice. Comparing the two periods 1969-1973 and 197^-1978, however clearly demonstrate n improvemena s n Latin-AMi t , wher numbee th e f totallo r v unacceptable results was reduced from 42 to 21% and the good results increased from 36 to 59%. Sir.ilarlv, the situation has improved in SEA. In EM the results in the second period worsened because the programme concentrate n thoso d e countrie d PTIan ss mos neen i tf improvement o d . This region also demonstrates the need for locally given expert advice.

e valueTh variour fo s s countries demonstrat e eveth en ereater differences between countries figuree th ; swhole refeth eo t rperio d 1969-1978. r examplCountrfo ) e(g v show H goo 88 swer% d 12 rese resulte f th o "dropouts"(>10t d an s % deviation),(total no.of sets distribute however, is d , verv small). Another countrsame th e s nearl f resioo vha ) y(h n one-half dropout d onlan sy one-quarter good results e highlOn . y industrialised country 5 goo/ 4 d s result ha % dropouts U o15 t stilE f bu s ha l .

An evaluation is given in the last three lines of Table 4 of the results of inter- comparisons obtained with the repeated participation of institutes which once or several tires did not return the TLD (N average). In line "N before V" the results of the participation precedinn.r= s availableN a " . r e etc.fa th g s ")(a were evaluatede Th . distribution of values within the various classes belongs to the lower qualitv distribu- tion, those "after H" are a bit better, those "before N" a bit worse. Final conclusions cannot, however, be drawn from these observations.

These examples demonstrate that o regiothern s d practicalli ean n o countre n v th n i v world which does not need to make continuous efforts to get accurate clinical dosimetry appliel radiotherapal n i d y institutions e maioritth ,n i evef institution o f y i n e th s standar s highi d .

e occasionallOn y hear e argumenth s t tha a deviatiot n dosi n e froie internationath r l standard does not matter as lone as it is consistent within the institute; in other words e samth e deviatio n ii th directio fe samd th an es i n n (plu r minuso s ) ovee vearsth r , thee institutth n e woul dn empiricall ow appl s it y y found therapeutic dose. This argument is not considered valid in the opinion of most experts. Nevertheless, it was thought to be of interest to check the consistency of results of institutes participating more than once in the intercomnarisons. The data are presented in Table 5. 205 RTIs or 49% of the total 416 participated more than once; of these, 66 twice, 45 three times and 94 four and more times. The table shows the percentage of the institutes in the relevant column belongin fivo t g e classe f consistencso y rangin gmoro t fro e% 5 mtha n 40%e Th . relevant class means thahighese th t t measured deviation differs froe lowesth m t measured by the percentage indicated by the class. Class A, for example includes differences from 0% (e.g. +A +A for the "highest" and "lowest" deviations, or +B +B, or -C -C etc.) up to 5% (e.g. +A -A, or +B +0, or -C -B etc). Class B includes e.g. +A -B, or +B -B, or +C +0 etc. and so on. The values quoted in brackets (...) indicate the percentage of institute e relevanth n i s t colum whicr difference nfo th h highesf o e d lowesan t t devia- tion does not include the +5% class of deviation from IAEA measurement and all deviations are either in the plus or minus direction. In column "twice" for example 35% of the 66 institutes in class A, which could e.g. be +A -A or -B -C etc. (18)% outside the +5% class therefore are +C +B or -B -C pairs, 35-18 « 17% are +A -A, or +B +0 and similar.

37 Considerin 5 institute20 l al g s togethe remarkabls i t i r e tha f theto e onlar m% 19 y consistent in their dosimetry within 5% and only 13% of them (19-6) are also in agree- ment wite internationath h l standard f theo % m) demonstratE 55 (clas .o t C s e differences in their applied dose of more than 10%. The statistics of consistency are much better for those which participated twice or three times onlv. This is easiIv explainable for two e increasereasonsTh ) (1 :d number participatiof o s n increas e chancth e f detectino e g errors occurring randomly rather than systematically ) Institute(2 . s wit d resulthba s were usuallv requeste participato t d e nexe agaith t n i nbatch n iudginI . e resultth g s one should not forget in addition that the higher classes C to E also include those institutes which first showe d resultba d d thean s n improved. This evaluation anyhow demonstrate e invaliditth s e argumenth f o v t that consistenc f dosimetro y n indiva n i y - idual institut mors i e e important than accurac n relatioi y o standardt n . Institutes which were consistent (clas , perhapA s s als wer) B o e usually also goo n relatioi d o t n the standard; those deviating from the standard were almosr all also bad as regards consistency.

. 3 Conclusions

3.1 The situation regarding the accuracy of clinical dosimetry still requires considerable effort practicalln i s O "egionn almosi WH l l countried al al tyan s o t s ensure that the existing radiotherapy services, particularly in developing countries, but also in industrialised ones, deliver accurate tumour therapy which is essential e effectiveb o t s e IAEA/WHi Th t .ii f O Networ f Secondaro k y Standard Dosimetry Laboratories (SSDLs) should obtain increased suppor d strengtheninan t y nationab g l and international authorities in order to enable it to become fully operational and effective in the shortest possible time, and particularly to fulfil its advisory and educational function worldwida n o s e basis.

3.2 It is considered desirable that it be included in codes of practice or even made compulsor y nationab y l authoritie y radiotherapan r fo s y institute involven i d cancer therapv with high energy radiation to regularly - say once a year if the result e goodar s ; more freauentl t acceptablno f i v e deviation e observear s - d participat postaa n i e l dose intercomparison simila o that r t oreanize y IAEA/WHOb d . e SSDLTh s shoul e stimulateb d d supportean d n organizini d g such nationa r regionao l l intercomparisons e timth e r beinFo . g alse IAEA/WHth o O Service e user b fo n d ca s that purpose. Services offere y SSDLb d s should n additionaa s a , l safety measuree ,b regularly intercompared on the international level, and this could perhaps be organized by the Network.

3.3 Services of short-term consultants should be made available at relatively short notice to RT institutions which cannot manage to solve their problems by themselves. Experts from WHO Collaborating Centres and SSCLs should increasingly be appointed for such missions.

3.4 The training of radiotherapy staff, including physicists, radiotherapists and medical radiological technicians n clinicalli , y applied dosimetrv shoul e strengthb d - ened and short, practically oriented training courses organized on a national or regional basis, whereve n increasea r d frequenc d resultba f o s yobservei s a n i d country or region.

3.5 The above recommendations do not conflict with, but rather complement, WHO's prioritie e fiel th f Primar o dn i s y Health woult i Care e ethicalls b da , y unacceptabl o establist e h Primary Health vhos f o Care e e e?rl ,on th aim s yi s detectio f cancero n , without establishin r bringino g g existing hrslth servicer fo s cancer treatment to a stage of development and competence where thev can effectively treat cancer patients. Reference is made in this context to the report of a WHO Meeting of Investigators on the Optimization of Radiotherapy particularly in developing countries held in Cambridge, UK from 11-15 September 1978. It is expected that this report wil e publisheb l d during 1979.

38 Table 1 - Distribution of TLD 1969-1978

Nunber of Sets to Pegion Batch No. Date AF AM EM EU SEA KP TOT. n.r . etc

Julv 1969 ) Partiallv (Not all results available II" October 1969 ) included as trial donv b e IAEA III0 December 1969) in I-III alone) . I April 1970 5 2 6 36 5 6 60 18% II August 1970 15 9 18 22 4 68 10% III December 1970 3 38 1 12 12 8 74 12% IV April 1971 3 12 21 6 - 42 12% V July 1971 6 2 9 8 14 39 8% VI November 1971 1 - 1 1 37 40 40% VII March 1972 - 2 35 - - 37 8% VIII July 1972 5 20 9 7 - 41 27% IX January 1973 - 3 17 - 22 42 14% X May 1973 - - 14 10 10 34 6% XI October 1973 11 8 7 7 5 38 21% XII January 1974 20 2 - 1 18 41 20% XIII May 1974 11 - - 1 11 23 0% XIV October 1974 16 12 3 5 - 36 39% XV April 1975 19 - 8 - 12 39 10% XVI August 1975 15 - 1 - 21 37 16% XVII March 1976 S 18 - - 18 44 11% XVIII August 1976 1 15 8 24 - 48 31% XIX December 1976 10 - 1 21 - 32 9% XX May 1977 17 16 - 34 10 77 9% XXI November 1977 9 15 - 35 ]0 69 6% XXII July 1978 - 15 4 28 3 50 6% XXIII September 1978 (Not vet available, November 1978)

TOTAL 8 207 156 204 227 209 1011 15%

* = not returned, or not irradiated, or not évaluable due to pistakes in handling e Instituteth y b D thTL .e

39 Table 2 - Other Data split by Regions

Ar AM TOTAL

Sets distributed 0.8%20.5? 15.4% 20.2% 22.5% 20.7% 100% Sets n.r. etc. 0? 137. 1C?. 9Ü % 15 182 % 21 f Countrieo . No 2 s part. 20 13 17 7 11 70 No. of Institutes part. 7 121 38 115 60 75 416 Inst. part. 1 tine 86% 667 24% 57" 4fi"277 50% 2 tir-es 1Ü? 137 13Z 22;; 122 237 17% 3 tines 9% 8% 15% ? 12 T7. % 23 4 tirpes 7 2 r 8i ' n i 157. 77 5 times 27, 13" 2r 32 87. 47 + Line 5 s 27, 32Z 1% 33" j% 107.

Table 3 - Kot returnen ( d .r. etc.) Sets Snlit according to frequency f participatioo n

Participation (times) 1 234 * 5 TOTAL We. of Inst. n.r. once 30 20 11 5 21 87 = 14% - 14% =7.5%% =21 4- % % 23 = No. of Inst. n.r. twice - 4 5 9 7 25 % 7 = % 3 •=- 3' =2% =6% No. of Inst. n.r. three - 0 0 8 S and store times = 247 = 2%

40 Tnblc It - Results of TLD Interconn.iri sons

WHO CLASS A A + B A+B+CG o t D E to G F + G No. of No. of No. of Of these PERIOD REGION -2% ±5% ±10% •> ±10% "> ±20% > *50% Countries Inst. sets distr. n.r. etc

AF* I 25% 63% 100% - - 2 7 8 0%

I AT I N I 14% 36% 587 42% 13% 2% 56 81 21% AM IT 31% 59% 79% 21% 8% 1% 91 126 9% 1 + II 25% 51% 727, 28% 9% 1% 20 121 207 14%

EM I 24% 60% 76% 24% 2% 29 63 21% II 27% 48% 67% 33% 4% 30 95 13% 1 + II 26% 53% 71% 29% 3% 13 38 158 167,

EU I 31% 73% 90% 10% 3% 112 179 8% 11 25% 50% 85% 15% - 15 24 17% I I + I 30% 70% 89% 10% 3% 5 11 17 203 9%

SEA I 30% 52% 70% 30% 7% 36 78 22% II 24% 58% 87% 13% 4% 0.8% 49 148 16% I + 11 26% 56% 82% 18% 5% 0.5%7 60 226 18%

VP I 34% 55% 82% 18% 12% ]% 64 103 25% II 35% 72% 86% 14% 7% 57 110 16% I + II 34% 64% 84% 16% 9% 0.6%11 75 213 21%

WORLD I 28% 59% 79% 21% 6% 0.5% 304 512 17% TOTAL II 29% 59% 81% 19% 5% 0.5% 242 503 14% I I + I 28% 59% 80% 20% 6% 0.5%70 416 1015 15% Tabl Continue- 4 e d

WHO CLASS A B + A A4B+CG o G t + 0 F G o t E No. of No. of No. of Of these PERIOD REGION ±2% ±5% ±10% :>±20% >±50% Countries Inst. sets distr. n.r. etc COUNTRY LATIN (a) 31% 6% 1 29 37 14% AM 19% 50% 69% (b) 33% 65% 79% 21% 9% 1 28 47 9% (c) 30% 50% 77% 23% 10% 3% 1 27 36 17% W) 30% 50% 60% 40% 10% 1 7 12 17% (e) 13% 38% 75% 25% - 1 8 10 20%

EM (f) 32% 68% 86% 14% 7% 1 11 35 20% (g) 38% 88% 88% 12% - 1 5 10 20% (h) 14% 24% 55% 45% 3% 1 5 31 6%

EU (i) 25% 58% 88% 13% 8% 1 10 25 4% (k) 31% 71% 94% 6% 3% 1 24 39 10% (1) 31% 77% 85% 15% - 1 26 28 7% (m) 20% 53% 80% 20% 7% 1 8 19 21% (n)" 56% 89% 100% - - 1 9 9 - (o)* 50% 67% 100% - - 1 6 6 -

SEA (P) 22% 53% 80% 20% 5% 1 44 144 17% (q) 36% 64% 82% 18% - 1 5 15 27% (0 (r) 34% 72% 86% 14% 7% 3% 1 5 32 9%

WP (s) 46% 82% 100% - _ 1 11 32 13% (t) 37% 60% 79% 21% 10% 1% 1 36 99 31% (u) 29% 57% 95% 5% 5% 1 7 25 16% (v) 27% 58% 69% 31% 15% 1 11 30 13%

N average 25% 51% 73% 27% 7% 1% 416 38% N before N 19% 45% 69% 31% 7% 58 N after N 26% 52% 76% 24% 5% 58

Nota: Period I = 196o 197t I 9X 3 o Batct inclusiv I h e Period II o XXIIt Patc I = I197 XI ho 197 t 4 8 inclusive

N average Resultl setal s f distributeo s o institutet d s which have onc r moro e e time t returneno s a setd , H before N Result f seto s s obtaine t returnedno s d wa befort . se a e N after N Results of sets obtained after a set was not returned. *• Only selected institute r thafo s t countrv(ies) participate e firs lotth i (n n t)i d batche n ordei s o chect r k the suitability of the intercomparison method. Tabl Result- 5 e f Repeateo s d Measurements

4 and Total ir>ore Participation: 2 times 3 tines more tipes than once No. of Institutes 66 = 100% 45 = 100% 94 = 100% 205 = 100%

Class t returnese o N d 6% - - 2%

A 0-5 Z 35(18)% 27 (2)% 4 (2)% 19 (6)% B 6-10% 29 (9)% 36 (4)% 17 (3)% 25 (S)% C 11-2"% 24 (9)7 20(11)7- 26(10)% 24(10)% D 21-40% 2 (2)% 7 (4)2 28 (9)7. 15 (5)% E >40% 5 (3)% 11 (7)% 26(13)% 16 (8)% All i(% Total) 32% 22% 462 100%

Values in (..) = % of values outside - 5% in absolute terns (i.e. all values of the institute either oositiv r negativo e e deviations).

43 Next page(s) left blank DOSE INTERCOMPARISON PROGRAMME OF THE REGIONAL REFERENCE CENTR ARGENTINF EO A

R. GONZALEZ SARAV. M , FERNÂNDEE ÏD Z GIANOTTI Direction de Raclioisötopos y Radiacioncs, Comisiôn Nacional de Energfa Atômica, Buenos Aires, Argentina

AbGtract

DOSE INTERCOM?A.R RAMMC RO TÎIF E0 P E N IREGIONASO L REFERENCE CITCTE ARGENTINAF O R .

This report include briesa f activitiee surveth f yo s developed in the Regional Heference Center and a description of the TLD teletherapy interconpar-ison programme baaed on the original IAEA/WHO studies. Results oabsorben fa d dose intercompariso 8 therap1 f o n y unit e presentedsar .

1. TNTKOX'CTIOM

The Regional Reference Cente Argentinf o r s establisheawa y b d agreement betwee Worle th n d Health Organizatio Conisioe th d nan n Nacional e Sncr/jld a Atörnic f Argentino a cooperation i a n v:itInternationae th h l Atomic lancriry Agency, in 1968. This Regional Reference Center is a Secondary Standard Dosimctry Laboratory that belongIAEA/WHe th o st O network similas A . r laboratories existing in other countries, it was established due to the necessity of improving the treatment planning in radiotherapy services and increasing the participation of the physicists experienced -_n this speciality and was the natural step in the developing programmes in radiotherapy physics establishe t thada t tim Argentinan i e . The; principal aims or these laaoratorLejo arc: to calibrate radi'ition measurement instruments used for radiotherapy ana radiation protection; to -?ivc advice on radie Lion doaimctry in oLinical work; and to develop a training progranoe in radiotherapy physics. >7 n agreemenia 19 n I t with '„he TA.EA viaa si-p-.e n ordei u o develot r p a oonlal dose Lntercomparison programme. It will be explained in detail below.

. " SîJJTPK-WT, INSTRUMENTS AîJD PHINCIPAL TAoKO PERWRMED e availablTh e irradiation source t thisa s laboratory are: v.%'O X-ray .^ennratorc (a 10 - 100 kV Seif art, with a Philips tube and a 80 - 300 kV Siemens Stabilipan), a tcleooba.lt unit (picker and s.mlJcr Co-00 and Cs-137 sources for hor.lth physics calibration. The principal, instruments employed are a secondary standard dosimeter Xustncr-PychlpM o PT^-tw ,J type IXJO a free-ai, r w chambeenergielo r fo rs (n.ado in Argentina), and all the accessories needed to perform the cali- bration of dosimeters used in radiotherapy and radiation protection.

For thermoluminescent dosimctry TLJ-70F Li , 0 powde uses i rs da detector .TeledynA e Isotopes model 3730C reade uses ri evaluato t d e the detectors. The ri'Lu absorbed-dose values are derived from PTW ionisation chambers.

45 This Center has also a laboratory for chemical dosimetry. The most important tasks developearew no :o t p du (a) Dosimeter calibration. Since 1971» 430 calibrations of radiotherapy instrument 0 calibration14 d san radiatiof so n protection instruments were performed. (b) Training programme. Since 1964» 19 Dosimetry in Radiotherapy courses have been given physician2 .25 physicist8 1 d san s advisers attended these courses d som ,an thef o e m tooka special trainin radiotherapn gi y physics. (c) Radiation dosimetry advisory work has been performed in several radiotherapy services. Cooperatio) (d ninterconiparisoe wit PAHth e n th hOi n quality- control studie r filsfo m badge dosimetry services, madn ei 1975 and 1977. (e) TLD intercomparison programme. This will be explained in nexe detaith t n sectioni l . Developmen) (f ferroue th f o ts sulphate syste higr fo mh dose measurements. This laboratory has participated in the two IAEA high dose intercomparisons mad 197n ei d 1978 7an .

3. THE TLD INTERCOMPARISON PROGRAMME 1 Cooperatio3. n witIAEA/WHe th h O Co-60 therapy units intercomparison programme. Since 197 Argentine'e 4th s SSDcontributes Lha IAEA/Me th o t d O Co-60 Teletherapy Dosimetry Servic sendiny eb dosimeterF gLi therape th o st y center r countrou f so y arid giving them technieàl assistance th n ei experimental procedure for the intercomparison. 197o t participante 5p th U s receive o set capsulef tw dso s containing exposee b specifiea o t o t dLis Fwa powdert d se dos e e.On (200 rad). The other set was to be exposed for a specified time (2 min). The results capsulee th f o s irradiate fixea r dfo d time were considered less reliable than those of fixed dose irradiation (Ref. l). Thus, since 1976 the fixed-dose procedur adopteds ewa . Participants complete data d a sheet and provided information on the basic beam output calibration measurements, the geometry of irradiation and the values of various physical factors that they use estimato dt dose deptm eth ec watern 5 rathi t ea . Table 1 shows the results obtained by the IAEA/WHO for 21 radio- therapy center Argentinf so e durin yeare gth s 197 1977o 4t ' Fro1 2 m intercomparisons (code 619 and 940 are the same center), about 50^ have good dosimetry with a deviation less than HH 5$. Only three centers have a deviation between £ 10$+ _d e onlyf.oan Th y center wit deviatioha n greater tha niOfo+ (code 619 s improve)ha dosimetrs deviatioe it d th t ybu s i n still greater than + 5$« In 1977 °ur SSDL started with a thermoluminescent dosimetry programme, in order to develop an intercomparison programme for Co—60 therapy units regioe ith n n wit same th he procedur employes i s ea IAEA/WHOy b d .

3.2 Activities at our SSDL

Detail firse th tf so measurement r SSDou L t swera e reporteo t d the IAE Januarn i A y 1978 (Ref. .2) 197n I cooperatioe 7th thref no e radiotherapy center Buenof so s Aire obtaines swa orden i d undertako t r epiloa t intercomparison. These center adequatd sha e instrument d highlsan y trained hospital physicists. They were selected to assure a good irradiation procedure. Each center receive capsule6 d s wit powdeP hLi r frosame th me batch irradiatee b thef o otherse o t :m3 th d ,dan without previous irradiation, were kept as control. The centers made the irradiation on the same day, and in order to avoid any fading correction the capsules for calibration were also irradiated in our SSDL on the same day. Once the material was returned to our laboratory all the measurements were performed on the same day. The absorbed-dose values assigned by our SSDL to each capsule and the values quoted by each eenter are compared in Table 2.

46 TABL . E1 Rl-SULT F 'ISO I 113 lAHA/MÜ INTl-RCOMPARISON R ARCLNTINIIO - RADIOTHERAPY ü'NTl-RS SINCE 1974

Yc>,;r- Batch Code MEAN Dosn Deviation DOSE RATE Deviation number calculated quoted1 by (%) moas'.irud quotey b d (%) y b fAF.A participant by IAÏ:A participant (rcid) (rad) ) in r i, (« (r (rad/min)

1974 12 578 487,9 500,0 -2,4 89,4 91,0 -1,8 019 179,5 200,0 -10,2 27,9 29,9 -6,5 620 204,0 200,0 *2,0 65,7 64,0 +2,6 1974 13 621 196,0 200,0 -2,0 58,5 58,6 -0,3 622 200,4 200,0 +0,2 84,8 85,7 -1,0 (>23 200,9 2CO,0 +0,5 83,3 82,3 -1,1 652 184,5 * A 57,2 * * 053 192,6 200,0 -3,7 125,1 130,1 -3,8 1975 14 654 P P P P P P 655 P P P P P P _i 703 165,8* N A 22,5 N * 1975 15 704 204,9 200,0 +2,4 27,6 26,1 +5,5 706 212,0 200,0 +6,0 20,2 19,5 +3,7 1976 17 818 194,8 200,0 -2,6 199,6 +4,7 I977 19 908 209,0 909 204,6 199,5 +2,6 9-10 185,0 200,0 -7,5 941 197,2 200,0 -1,4 042 * P P 1977 20 <>13 191,9 200,0 -4,1 944 P P P 945 182,0 200,0 -9,0 NotedatO N o:* avail.iblc N Data shee t roluvno'A no tAL I o t l P Other reasons

TABLE 2. RESULTS OF SSDL PILOT INTLKCOM'ARI SON

Center Measured, Diff. Mean A Deviation Kean * (V, Craci ) Crad) C%)

I 100,13 (Co -60) 100 ,.13 0,40 199,55 199,57 -0,01 99,73 I 99,16 CCs-137) 100,83 1,67 203,43 200,05 + 1,70 100,00 II 99,94 (Co-60) 100,38 0,70 197,08 200,15 -1,53 ' 99,68 III 101,12 (Co-60) 98,65 2,47 133,48 142,83 -6,55 100,22

Note: Measured,, .....,, , , , —————\ : individual dose values measured for e-icr. capsule expressed ?.eare th .f o dos % e s l threa valu_ al f eo e capsules (rea- ding r sSSDL) ou mad y .b e Diff. %: differenc e between r.;ax fro«ann mi dn three capsules readings s expressea previoun i d s three columns. Mean: mean dose in rad assigned by cur SSDL. quotes a d eac y b d: ra Ados hn i eparticipatin g center. Deviatiocenr pe t deviatio: n% measuref o n d near cosf ,o e (MM) from the quote regarn di dos ) quoteo t d(A e d dose: Dev.% = 100 . (MM - A) A 47 The percentage deviation of three teletherapy units is less than centee deviatioa On s . rha 2% £ n greater tha n'j%.- Nevertheless this center irradiated with a dose lower than the 200 rad required, and beyon calibratior limite ou dth f o s n straight-line. Thus randoe ,th m uncertainty of the absorbed-dose value assigned by our SSDL is greater thauncertainte th n y expecte y thib d spercentage methoth d dan e devi- ation obtained has less reliability. The first national intercomparison was undertaken in 1978 with 12 participating institutions. 14 therapy heads were checked. Each center received four capsules wite sampowdeP th hLi e f batcho r , thre f theo e m to be irradiated and the other without previous irradiation was kept as control. s requesteItwa dosd deliveree ra "b ecap de 0 -th tha 20 o t da sules at 3 cm depth in a water phantom. The centers received a very sim- ple questionnaire in order to obtain information about the basic beam output calibration measurement. The Co-60 units utilized by the participating institutions were of differen tseee b Tabln origin i nn Mos. ca e3 thef s o t,a m were cali- brated by the Comision Nacional de Energïa Atömica of Argentine at the tim sourcf o e e change CNEe .Th A use thesr sfo e purpose sdosimetea r with appropriate chambers calibrate r SSDLou .t da The intercomparison results are summarized in Table 4- Of 14 intercompared units, 9 have a satisfactory dosimetry with a deviation lower tha ')%.n+ Four centers hav deviatioea 10,«- n.d betweean ° 5/ n- Only one center delivered a dose lower than that required.(beyond — 10?o).

TABL . E3 IRRADIATO R TYPES

Code Irradiator type Dat lasf o e t number Bourse's change

110 Theratron 780 April 1975 112 Picker November 1973 120 Picker - 121 Picker (Cs-137) - 122 Theratron C September 1975 124 Theratron Junior July 1974 130 Theratron Junior January 1978 140 Siemens GainmatroI I n September 1975 142 Siemens GammatroI nII March 1977 150 Siemens Gammatron II March 1967 152 Picker - 160 Theratron Junior March 1971 180 Theratron August 1977 190 Whestinghouse February 1977

NOTE: Except code numbeirradiatore th l rCo-60f o al 121 e , .sar

48 «IP O r-- vO "3- c vD o t~~ 0 CM 0 -3- CM CM CM O I-. m to vO en CM CD to s 1 i + 1 1 + l i + to +

. r > > M 4-> Ul .Q !U r-- SOi O O o O 0 vO o c 0 O o 0 m O co 0) U O O o O o m o c o o CD o r-. 0 Z -H -H O CD o O o CM o CD o o CD o "3- CD en 4-O > < CM CM CM CM CM CM CM CM CM CM CV1 CM cj £&i3 ex (n •H

10 Q CO M l/l CO O oc 1^. CM M in T— 00 O r^ en «3- en r~.

8£ VO r» vo LT) in in VS CO VO o CD T 0 en en Ol O en CM CO co C co co O o CD <5= 4-•> Cù O i: -o o "Oo o ,j o m va t— \O VO r^- co •^T ro O co r- >* VO o ÎO L/î co ce r-. un es. ce oc 'S- cc to O IÛ

a O oo l/l I-O vO 0 0 L.O O en (NI P^ o , CO XI O CM VO •3- CO en «— 0 rrj- o L.O 0 •o (NI u~. O T3 T-* CM CO en CM to f. r^ co en en CNi

O c; Q, rs- r-. co •F*- LO \o O c: L/"> CD CD CO co o W *rt fT3 cn en en O en CM ce oo ô oo « CD c s g° 4J O •rH « CD •a < -O r-l r- co LO if. CTi LO r~- O (N! to O r~- co CM r~- M co en en r~- co to t^ ^* ^r m CvJ

10 Q< r- r~- LO o ir, ro i/i vO r~. r~ *£• CX! 'S- 10 cn en en o en CM ce CO o co co o o CD

oo ^"- LO LP. ^r i~- c-- cr. 0 'M -•ï- co en co CM vO VO t^. c-. 00 c; to 00 vO m 10 o •a- in o r- ce r^ o en to in i-3 CN) to rj «3~ CM to co C3 in en CO •K r^ in un in Lf> in in ro •sr LO in 'S- •«3- CM m ti M o U \D CM O •zr t~~ l.T •«• O ce CO ^r in o .a C in CO CM in ro en vC co CD CM CD co I-> T CD [-^ •a ij (3 10 CM to CM ro c-. o en CO •K r-- m CO LÖ LO u-, 3 in to *t in in «* "T CM m CJ « •a o fO u •o

CO LO VO ^r" o r- c CM en vO 0 vO 'S- vO CO CM r-» LO «c- vD o [^ 1O CM en 'S- VO c. & iH f- en (NI ^ T ^™ .-^ C5 rq VO o ^3- vC o 1-5 Ü II CM CM CJ in (SI fO er. C3 in CD co •«• t~. ^r in in LT. m L/l ro •»T LO m m T in CM L.O « * f-l IU Cl O .•M 0 (M ^? c c CM CD C^J 0 O 0 r- "Si CM (M CM CM to •«c -c- i/> in 0 co cr. O CJ 3 G 3.3 Discussion

The first national Intel-comparison gave a mean value of 196, 12 rad absorbee th r depthm fo dc 5 dos ,t ea wit relativha e standard deviation of +_ 4»3/£. With regard to the prescribed dose of 200 rad, the mean value deviated by — 1,9%« e intercomparisoTh n mad IAEA/WHy eb O from 197 197o 4t 7 gav meaea n absorbee th r depthm fo valudc d 5 dos197[f ra e,o t ea 2wit ha standar d deviation of + 4j4%. The mean value deviates from the prescribed dose of 200 rad by""- l,4/o.

3.4 Conclusions

The TLD intercomparison programme is a very important complement to other means employed to improve the accuracy of radiotherapy clinical treatments. ProArgentine th m e experienc D intercomparisoTL n ei n studies, this programm usefus ei onlt identiflo no y t y error d inaccuracsan y in the clinical delivery of radiation but to create a greater aaareness of the need for correct dosimetry in radiation therapy and to improve contacr ou t with radiotherapy center countryr ou n si . Many physiciank sas for advisor d calibratioyan n services interese th d gettinn ,an i t g better accurac dosirnetrn yi s increasedha y .

. 4 FUTURE INTERCOMPARISON PROGRAMME

In the future this laboratory will continue with the TLD intercomparison programme for telegammatherapy equipment in the y indicatewa d above. recentle Th y initiated similar feasibility stud orthovolr yfo - tage X-ray units wil followee lb orden i d staro t rintercome tth - parisons as soon as possible. indicates A d above ferroue ,th s sulphate syste higr fo mh doses has been developed and we intend to apply this system to the radio- therapy dose rang carro et intercomparisot you n studies. The first linear accelerator for radiotherapy has begun to work this year in Argentina, and several others will begin in the near future. For this reason this laboratory wants to study an intercomparison programm r sucfo eh equipmen chemicae th t d usinan l D g TL bote th h syst ems.

REFERENCES

(1) H. H. Eisenlohr, S. Jayaranian: "IAEA/WHO Co-60 Teletherapy Dosimetry Service using maile dosimeterF Li d - A surve sre - f yo sults obtained during 1970 - 75" (1976). (2) H. Mugliaroli, R. Gonzalez, M. Saravf de F. Gianotti: "Activities with TLD in the Regional Reference Center (CNEA) - Argentina , 1791/RBo N C 1977R/ ,.

50 EXPERIENC INTERCOMPARISOEN I SSDA T NLA FOR ORTHOVOLTAGE AND HIGH ENERGY BEAMS

G. SUBRAHMANIAN, I.S. SUNDARA RAO Radiological Standards Laboratory, Division of Radiological Protection, Bhabha Atomic Research Centre, Bombay, India

INTRODUCTION

With the increasing use of high energy machines such as teletherapy units and high energy accelerators in the various radiotherapy centres in our country, the Secondary Standards Dosimetry Laboratory of the Bhabha Atomic Research Centr playins ei n importanga t rol attendinn ei e th o gt dosimetrie needth f so c requirement thesf so e centres. SSDL (Bombay) main- tains all the national primary standards for various radiation qualities. These primary standards have been intercompared with similar devices at the International Bureau of Weights and Measures (BIPM), the National Bureau of Standards (USA) Nationae ,th l Physical Laboratory (UK) Bureae ,th f uo National Metrology (France) and the Regional Calibration Laboratory (New York) during this decade intercomparisone Th . s have been carrie usint ou d g trans- fer standard Shonka chamber resulte th d san showed congruence better than centr SSDe pe Th L.1 provide- addition i s followine th n g services: (1) calibration of Secondary Standard Dosimeters belonging to various centres in India; (2) output calibration of radiation beams for field conditions; sitn i u ) compariso(3 l Instituteal f no sSecondar* y Standard Dosimeters against SSDL reference standard etc.; (4) organizing postal dose intercom- parison programme using TL dosimeters for different types of radiations in collaboration with IAEA/WHO in this geographical region. The procedures adopted by the SSDL for such postal dose intercomparison programmes for tele- therapy beams and our plans for the international intercomparison for high energy photon and electron beams and also our experience gained in this field are outlined in this paper.

Since 197 SSDe 6th L Bomba beed yha n conductin absorben ga d dose inter- comparison service for Co teletherapy units in India, Burma and Sri Lanka. Abou dos0 7 t e intercomparisons have bee radiotherap0 5 n t conductea r fa o ys d centres resulte Th . seee summarizee b sar n y ma fro e t I Tablmth n d i . e1 Table that in 69 per cent of the cases, the deviations were within - 5%.

Radiological Standards Laboratory, Division of Radiological Protection, Bhabha Atomic Research Centre, Bombay - India.

51 The intercomparisons were repeated whenever deviations exceede 15%- d n .I most cases a significant improvement in dosimetry was observed on repeat intercomparisons. These intercomparisons had also brought to light some instances of serious errors in the dosimetry practices in some of the hsopitals. Wheneve serioua r s erro s detectedrwa , immediate follow-up action s initiatedwa d this continue,an swa d unti mistake lth s identifieewa d an d rectified e postaTh . l dose intercompariso d thunha s really averted several potential accidents in radiotherapy. Frequent intercomparisons are very importan assuro t hospitale eth continuef so d adequac n theii y r dosimetry and in some cases to detect if any later mistake had developed. Thus the dose intercomparison service is valuable both from the point of detecting serious errors and ensuring uniformity and good quality of radiotherapy dosimetry.

An important extension of radiotherapy dosimetry service is the provision of accurate beam output calibratio teletherape th l nal datr yfo a units because the accurac n dosi y e calculations mainly dependaccurace th n o sbeaf o y m out- put value. This programm s initiateewa d conductean d d concurrently wite th h dose intercomparison service by deputing a senior physicist of the SSDL to various radiotherapy centre e countryr countryth ou n n i sI .o far ,s , there io officiasn l cod practicf o e e specifyin beae th m w outpugho t measurements should be performed. Most of the hospitals measure the beam output in air at SSD + 5 mm. Some hospitals measure the dose directly in a water phantom at 5 cm depth. However, almost every hospital relies heavily on published data percentagr fo ) (1 e depth dose, back-scatter factor etc., require absorber fo d d dose calculations e SSD s consciouTh .Lwa e facth t f o sthadepte th t h dose value e influencesar somo t d e exten machiny b t e parameters suc s sourca h e size, secondary collimator design, penumbra trimmer d radiatiosan n field size speci- fications vis-a-vis optical field etc. Bearin l thesal g e thing minn e i s th d visiting SSDL physicist performed beam output measurementn i d an r s ai bot n i h phanto eventuar fo m l compariso absorbef no d dos watern i ee resultTh . o s far obtaine 0 teletherap5 r fo d y unit ss foun werwa t dei thaanalysed an t ) (2 d the absorbed dose value calculate methodo tw y usin db e sth g differes a y db much as 4% in the case of eight units. Again for these eight units percentage depth dose was measured by exposing TL dosimeters at both 0.5 and 5 cm respectively e deptTh . h dose values differed from those publishee th n i d British Journal of Radiology (Supplement 11) by as much as 2.8 per cent (3). The percentage depth dose is an important parameter for clinical dosimetry and should be determined experimentally. The published data may be used for totar fo guidanc lt relianceno t ebu . This experiencanotheo t s u rd le e extension of the dosimetry programme namely the central axis depth dose data servic mailey eb d dosimeters n irradiatioA . n stand designe o thaD s d TL t capsules could be inserted at eight different central axis locations was maile eaco t d h participant along wit n adequata h e numbeD capsuleTL f ro s depending on the demand by the radiotherapy centre. The irradiated capsules were measured at our SSDL and the results communicated to the user. The depth dose measurement service is entirely independent of the dose intercom- parison programme s interestini t I . noto t g e that when error n deptsi h dose

52 values use n intercomparisoi d n were correcte measuree basie th th f so n do d depth dose value, the results in some cases have shown significant improvement.

2. Orthovoltage X-ray dose intercomparison

e situatioTh othey an Indirn n ni i developins a g countr thas e i y th t annual growth rate in the number of teletherapy installations is quite rapid while mor mord ean e conventional X-ray therapy unit e lyin sar disusn i g r fo e obvious reasons. Henc neee X-rar eth fo d y intercompariso keenlo s t yno s ni 60 teletherapyo C case th f eo n i fel s .a t However SSDLe ,th , Tromba worked yha d methodo outw t qualitr fo s y determinatio ratiL T y namelon- b ) centra(1 y l axis depth dos ) externae (2 rati d oan l filtration. Botmethode th h s have been proved to be independent of X-ray spectrum for a given first HVT. They have been successfully use preliminarn i d y dose intercomparison experiments con- ducted for superficial and deep X-ray therapy at a local hospital.

mose Th t important factor that mus consideree tb n thii d s contexe th s i t large fluctuation in X-ray beam intensity due to main voltage variation in citiese th man f yo . Froexperiencr mou have ew e noticet no d s i tha t ti uncommon in routine output measurements that a set of 5 successive output measurements each of 2-3 minutes duration showed variations as much as - 10%. Is impossiblti statemena relo et n yo deliveref to d dose unles X-rae sth y unit had incorporated a monitor chamber system. This point is very important in X-ray therapy dosimetry, particularly when a recommendation has to be made to a hospital on the factors that caused larger deviations. To the best of our knowledge none of the X-ray therapy units in India had built-in dose monitors vien I this.f wo programme ,th initiato et e regular dose inter- comparison service to hospitals was deferred in favour of developing a reliabl d simplean e monitor syste eventuar mfo l large scale supplo t y hospitals. The SSDL has succeeded in developing a small ionization chamber that can be positioned near the space provided for filters.

importann a s i T tHV paramete X-ran i r y dosimetry measuree Th . d value of HVT depends on the conditions of geometry, purity of filters, energy dependenc detectorf eo s etc. Excep purposer fo t usinf so g published depth dose data, the HVT value is not required in dosimetry. Instead of HVT in aluminium or copper, half value depth in water would be a better specification of beam quality. We think that the most appropriate dosimetry service for orthovoltage X-rays centrar shoulfo e db l axis depth dose values using mailed TL dosimeters. The HVT as well as the absorbed dose at a specified depth (5 cm) can be obtained simultaneously besides the central axis depth dose data.

3. Dose intercomparison for Megavoltage X-rays

largA e numbe medicaf ro l accelerator worle s th use dn i de belon th o t g less photo V thaM 0 n1 n energy category (4)encourago T . e participatiof no many hospitals, the dose intercomparison service may be restricted to 6 MV only for the time being. Another advantage of choosing 6 MV is that the existin dosimetro C g y servicextendee b n eca d easily powdeF Li . r encapsulated in nylon is adequate at this energy. A check on the beam energy is very

53 important to avoid errors in dosimetry and this can be done by depth dose ratio check. Since the accepted calibration depth up to 10 MV is 5 cm, two dosi- depthm c d irradiate0 1 an s d an m meterlocatee c b d 5 y simultaneously t sma a d . e dosTh e intercomparison servicextendee b y ema higheo t d r energief si necessary in a progressive manner. The depths at which dosimeters should be locate calibratioe th dsame s th musa e e tb n depths recommende y ICRdb 3 2 U beyondm c 0 1 .d an V M 5 2 o t p u m i.ec 7 .

4. Dose intercompariso higr nfo h energy electrons

IAEA and many other standard laboratories have been conducting electron beam dosimetry service by mailed Ferrous Sulphate dosimeters and valuable experience has already been gained on the reliability of this service. There IAEe discontinuo th t A neeo i r n s fo d e this servic d finean d another substi- tute for FRICKE. The FRICKE system is recognized as a secondary standard and proved to be stable and reliable for mailed dosimetry. From the point of convenience the intercomparison service should be restricted to one electron energy, say 20 MeV, and the depth of measurement should be in the region of dose maximum (1.5 cm).

n energA y check measuremen dose t th parmusa e f e intercomparisono tb . This check can be done by irradiating another dosimeter at 3.5 cm depth simultaneously.

In conclusion, it must be said that absorbed dose intercomparisons have proved extremely valuabl n improvini e qualite th g radiotherapf o y y wito C h and orthovoltage beams. It is only appropriate to extend the programme to include high energy photon and electron therapy. For the sake of completeness, 137Cs teletherapy must also be included in the dose-intercomparison.

Table 1

Result Postaf so l Dose Intercomparison

Batch Total Institutes who returned % 15 ±5 %% 10 5% capsules

1 5 3 2 - -

2 8 5 31-

3 10 5 521

4 9 7 2 - -

5 15 8 733

6 22 15 753

Total 69 43 26 11 7

% 38 15.5 % 62 % %10 100%

54 References

(1) Central axis depth dose data for use in radiotherapy Brit.J. Radiol., Suppl. 11 (1972) (2) S.B. Naik, I.S. Sundara Rao and G. Subrahmanian, Beam output calibration of teletherapy units. AMPI Medical Physics Bulletin 4, 1(1979) 23-25 (3) T. Malini and PNMR Vijayam (1978) (Unpublished). (4) Directory of High Energy Radiotherapy Centres (1976) IAEA.

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55 BUREAU OF RADIOLOGICAL HEALTH ACTIVITIES IN DOSE DELIVERY SURVEYS

. MORTOR N Radiation Therapy Branch, Bureau of Radiological Health, Rockville, Maryland United State f Americso a

1. The Bureau of Hadiolorical Health (3:Gi) is part of -the Food and Drug- Administration of the Unite! States of America and is responsible for the safe and effective use of radiation from electronic products and radioactive material. Licensing the radioactivf o e us e by-product material remain respone sth - sibility of the Nusiear Regulatory Commission.

. 2 Between 197contracteH d 197ER 4an e 7th d witNationae th h l Bureau of Standards (NES) of the United States to conduct a dose delivery cobalt-6e surveth f yo 0 teleiha-spy units . Thi s similaUS IAEe swa e th ith A no t rposta l dosimetry service, but on a one time basis. Abou) abouf a unito 0 t 11 t sou 100 0 units were surveyed. b) 83 °j» yielded dose interpretations within 5 °j, of the prescribed dose. c) 13 fi yielded difference between 3 "jo and 10 $. d) /, •£ of the dose interpretations were creator than 10 ,' for the dose requested. e) N3S Technical Note 978 is a publication reporting the d othersan result e surveK th BR . e f st o y BR!) f conductin!s i n analysiga e survo th wil d f san yo l publis conclusions it h y latsb e summer 19"'9. g) An "Interim Report of the National Bureau of Standards/ Bureau of Radiological Health Co Telcthorapy Survey" by Thompon, Wyckoff and Soares appeared in Int. Journal of Radiation Oncology, Biology and Physics, (Vol 4 pp-106^- 1068 Nov 1978)c -De - plannins i H BR 3mailega . d dose delivery surve medicaf yo l linear accelerators with photon energie^ î 0 1 s o frot ) / m

a) N13S will evaluate and calibrate a lucite phantom con- taining LiF - TLD chips.

57 b) BfiH will conduct the survey probably using LiP - TLD chips because of considerable experience in handling large number of these chips in surveys of dental and mammographie X-ray units. c) An advisory •jroup from the Radiation Therapy Committee of the American Association in î-iedicine is assisting in the desig d selectioan n dcsimetr e th f o n y syste d wilan m l hel plao e t psurve th n y questionnaire. deliveree b dose o th e survet e r Th fo ) s expectedd i y k as o t d ) lucitcm 0 e(2 r phantoa fo n i d n an me t0 depta o1 f o h the calculation arid constants used in arriving at that dose. This will provide rr.ore data than a simple dose interconparison in that it will also check the ability to deliver a prescribed dose under patient-like conditions. e) Site visit follow-up is planned in cases where serious dose delivery difference is found. 1) Tne serious difference "level"has not been defined. methoe Th follow-uf ) o d2 beet ne n s decidedpha . Possibilities include: Hirin) a g private consultants. b) Forming an agreement with the six Centers for Radiological Physics whic e sponsorehar e th y db National Cancer Institute and coordinated by the American Association of Physicists in Medicine.

planr-Scs i t I offeo t ) Lavailabl e f rth D doseTL e delivery assessmen continuina s ta g programme that could become part o ffacilitiea s comprehensive quality assurance program.

y reasonM attendinr . sfo 4 g this meetin thae questione gar th t s the IAEA needs to answer for an intercomparison of medical linear accelerator members s needK it BR a o solvf st e o sr ,th fo e similar Unitee surveth f dyo States. Further botf ,i h agencies choos same compatablr eth eo e survey methods, we both will have an expanded data base.

58 STATU RADIATIOF SO N THERAP NIGERIYN I A PROBLEMD AN ACCURATF SO E DOSIMETRY

A.O. FREGENE Dept Radiatiof .o n Biolog Radiotherapyd yan , College of Medicine, Lagos University, Lagos, Nigeria Abstract: The status of radiation therapy in Nigeria, a developing nation, and high-light f canceo s r incidenc Nigeriann i e e presentedar s . The need to develop radiotherapy, and its place in relation to other moralities of cancer management in developing nations are examined. Finally, the numerous problems of radiation dosimetry typical of some developing nations are stressed. In Lagos we place emphasis on the FeSO, dosimetric system for the most reliable results. In view of the numerous weighty problems in developing nations, there is need for a continious input from the developed nations in order to build-up the most effective radiotherapy centres.

Introduction fl) It is difficult to discuss the Status of Radiotherapy in Nigeria and the Problem f Accurato s e Dosimetry withou w wordfe a ts abou e pattern.th t , of cancer incidence in the country. In additio e establisheth o t n d fact d speculationan s n respeci s f canceto r incidence- racial, sex, age etc., and aetiology in man- genetic, environmental, viral, n importanetca . t finding worth statin thats i ge over-al th , l crude incidence of cancer over the last several decades in Nigeria, is significantly lower than that in Europe, and the U.S. (Doll et al. 1966). Cancer incidence survey Nigeriann i s Edingto( s Haclead an n experienc r ou n d 1965an )Lagon i e s ovee lasth r t decad whicn i er Radiotherap ou h y cente s beeha rn functional, confirm this trend. Virtually, all types of cancer seen in Caucasians have

59 been recorde n Nigeriani d t prevalencbu s f specifio e c types differ e onlTh .y Radiotherap e cit yf th Lagoso e centryregion i th n s ,i i en populatio million3 n . This centre receives cases of cancer referrals from all over Nigeria (population 90 million) and also from neighbouring countries, the Camerouns, Ghana, and Sierra Leone. In discussing the incidence of cancer in Nigeria we cannot but mention a w unusuafe l findings whic y havma h e some implication e generath r lfo s cancer effort. ) (a Primary cancee lund liveth an e glinkef ar o r d respectivelo t y smoking and excessive alcohol consumption amongst other causes. Both practices in Nigeria for economic and other reasons are indulge o considerablt n i d y lesser extents than amongse th t developed nations e incidencTh . f primaro e y lung carcinomn i a Nigeria is unusually low, - only three cases amongst some 1,000 cancer patients seen in Lagos. Liver cancer incidence on the other han s reportei d d higher than amongst Caucasians. ) (b Another occurrenc e unusuallth s i ew incidenclo y f e canceo e th n i r aged in Africans, Davies et al. (1962) - considerably less than in Caucasians - it would appear that those who escaped the multitudinous infections and disease afflictions in childhood and middl e develoag e p enough resistanc o combat e t d canceageol .n i r (c) A common occurrence in both Caucasians and Nigerians is that the incidence of Ca-Breast and Ca-Cervix is high. Indeed about 2 out wome3 f o n treate r r radiotherapcancefo ou d n i r y departmene ar t either afflicte y Ca-Breasb d r Ca-Cervixo t .

) Radiotherap(2 y Centre n Developini s g Nations The problems encountered by developing nations in respect of effective applicatio f radiatioo n n therapi n e manifoldar y ; where facilitiee ar s available e.g. in Lagos, we find problems of (a) lack of supporting technical personnel for effective maintenance and service of teletherapy machines. ) (b mulish ignoranc f administrativo e e staf d consequenan f t inertia in financing progressive programme e areath f traininn o si s d an g acquiring of accessory equipment.

60 (c) with a one man band therapist, possibly one trained a couple f decadeo s back, arid limited clinical interactions with other radiotherapists, chance f optimisatioo s f radiotherapo n y service are not enhanced. (ci) the status of the general radical service whic.n is rerrotely tied e leveth f cenceo o lt p u r consciousnes f the-o s populace coule! effect cure r?tes; for instance, the over-all survival of our cancer patient n Logosi s , woul e inp'-cveb de ratheth f i 1d- high proportion of cases reporting for the "irst time in our clinics did not cone too l~t of a compact Radiation Centre, which incorporate!- a Radiation Biology section, Nuclear Medicine service and a Medical Physics unitr radiotherapOu . l y al divisio y b a siral e s i non l

rri standards s equippei t i , Theratroo d C wit a h unit 0 3 n c'-tliovoltag2 , e X-ray

machines a superficia d an , l X-ra e yaverage th unit n a gooO .n i d , yeef o r

m i UMin ! technical problems, roughly SCpatientw One e treatedar s e otherth , s

unfortunatel turnee ar y d away: thi i !.s - inevitabl numbee th n viei e f f o wo r

countries and the roainiiioUi sized population served by the centre.

(4} T_he Problrii Dosiiv.et.r_ ^of n i Legoy s

The prob le- :".:, of do s i nx-try in Lar.os are considerable, and the need for a

Secondary Standards Dosi^c'Lry labore tory canno oveo b t r estimated especially

in view of r lens 1.o esios'ish new '.r.erapy con ties net only ir. N ice r is hut in

neighbouring countries as well.

Firstly e performancth , ccii'inerciae th f o e l thimble chamber ove a lonr g

period in i.E.rnr is subject to fluct-.JSi.ionb owing to high humidity and temperature

conditions. Kifi Boon arc! colIcïcuss in Singapore a town v.ith high hu:::idity,

and similarl "lyinw lo y g tropical condition s Lagosa s , reporte e interferencth d e

of fungal growths as well (person: conrcvnicctio'i). They have, by proper air 1 pur ificetinn zr.d teiiperctu-e control (net conventional air conditioning)

61 established reasonable storage condition d consequentlan s y improved their ionisation chamber performance. In Lago rele vi sy extensively e FeSOth n .o , dosimetric system whics i h not affected by high humidity and fungal growth. Furthermore, we have for use as standards a pre-calibrated (NPL) 90Sr source, and our 60Co machine of predictable output. These ensure independent r checkionisatioou n o s n chamber measurements d e largeconfidenan ar y e B ,w . t thae prescribeth t d dosen i s contradistinctio e knows e on idea th y - o lan what ne f s one ideai i tar - s- l delivere e tumourth o t d. y pose questionma th ee e introductioOn th s i » f radiotherapo n y departments into developing nations justifiable? Skeptics may argue the importance of other prioritie n healti s h car n thesi e e emerging nations e.g e scourg.th f o e infectious diseases; problems encountere e numerouar d d weightyan s , e.g. lack of trained personnel to successfully execute the specialised damands of this sophisticate f modero m ar nd medicine etc. However, lookin n depthi g , would reveal a pressing need for the benefits of a radiotherapeutic service, even a modes f o te b sizet i .f i

(5) In conclusion may I state the following, (i) Cancer research and treatment in developing nations should be encourage t onlno dy becaus f theio e r benefit o thest s e nationst bu , alse possiblth o e benefits thae over-alth t l cancer effor y derivtma e from this completely different dimension; differences in geographical distribution pattern of cancer, e.g. Burkitt's lymphom n Africai a ; variation n incidencei s e dependenceag d an , , which could a modificatiolea o t d r evolutioo w , conceptne of n f o n s e aetiologith n d treatmenan y f cancero t . (ii) Dosimetry in developing nations, is confounded by numerous factors, d cooperatioan n wite largeth h r centree developeth n s'i d nations can only enhance performance. (iii) Radiotherapy in developing nations is at its infancy and may be nurtured fully only throug e inputh hf boto t h economical, technological and human resources from the better developed nations.

62 (iv) In view of the acknowledged advantages of radiotherapy over other modalities in the treatment of certain types and forms of cancer, and obvious general limitations in developing nations, in these areas as well, e.g. experienced manpower, facilities in the effective administratio d folloan n w throug f chemotherapo h d evean yn surgery, in cancer management, a well developed and properly dispensed less traumatic radiotherapeutic service has a lot to commend it in developing nations.

References:

d Maclea) Edingtoan (1 . M n . 6 C.M.Un . Brit. J. Cancer 19 471-481 (1965) d Knoweldean ; ; Wilso) A. DaviesP. (2 . J . . nB N n . J , Lancet (ii 8 (196232 ) ) (3) In Cancer Incidence in Five Continents; A Technical Report; distribute e Internationath y b d l Union against cancer. Edited by Richard Doll; Peter Payne; and John Waterhouse. Springer - Verlag Berlin - Heidelberg and New York. Boona Ki ; ) "Persona(4 l communication".

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63 USE OF THE FERROUS SULPHATE DOSIMETER TRANSFES A R INSTRUMEN CALIBRATINR TFO G CLINICAL DOSIMETERS

J.P. SIMOEN CHARTIER. ,M . PAGE,L S Laboratoire de métrologie des rayonnements ionisants, CEA, Centre d'études nucléaires tic Saclay, Gif-sur-Yvette, France

1 - INTRODUCTION -

In clinical dosimetry basie ,th c physical paramete reference th s i r e absorbed dose which determines the treatment durations and consequently the doses delivered to the patient. It has been shown, through systematic clinical observations, that discrepancies of only 10 '5 between doses delivered to tumours in identical treatments led to significant clinical differences, thus leading radiotherapists to wish for dose estimations with reproducibilities of . SucJ 1 accuracied h f an constraint 1 % 1 3 referenca f so f o e s us imple e th y dosimete higf ro h qualit correctld yan y calibrated.

Considering that dosimetric primary standards at national laboratories are usually defined with overall uncertainties close to 1 1, and that transfe- rence of knowledge through calibration of an instrument inevitably deteriorates accuracy obvious i t ,i s thaoperatioe tth calibratingf no dosimetryn ,i a s ,i delicatmusd an carriee t b e ewiton t dou h particular care. Note that this si seldom the case in other fields of metrology where the levels of accuracy between primary standard field san d measurements differ ofte y severanb l orders of magnitude. Moreover, the increasing utilization of accelerators in radio- therap enhances yha neee r calibrationth dfo d termn si f absorbeso d doso t e tissue (or tissue-equivalent materials such as water). Such calibrations can be deduced fro calibratioa m termn ni exposurf so applyiny eb g appropriate con- i i version factors (C» s /2 /, C s /" 3 J) ; but recent thorough analysis of " E these factors f 4 J have shown that their values could lead to errors of several percen and, t , besides, even with correct factors, this procedur ablt no e s i e to take into accoun actuae tth l irradiation condition whicn si calibratee th h d dosimeter is to be used. Therefore, the best solution consists of calibrating dosimetee th r directl termn yi absorbef so user'e th n dsi dosbeamd ean , provided that an appropriate transfer instruisent is chosen.

thiIs ti s last procedure whic bees hha n retaine recentld n dan i t ypu Frence placth n hei Calibratio transfee Th n . ChaiJ rB nf dosimete r choses ni the ferrous sulphate dosimete calibratioe th d ran n conditions were agreed upon following thorough discussions with medical physicists e procedurTh . s ei applicable to Y-rays from cesium-137 and cobalt-60 and to X-rays of maximum energies greater tha MeVn2 d -c,an o electrons with initial energies betwee0 1 n and 35 MeV.

65 CHARACTERISTIC- 2 FERROUE TH F SO S SULPHATE DOSIMETER-

e transfeTh r dosimete sealea s i r d glass ampoule containine gth ferrous sulphate solution (see. fig) 1 .

S°lution_containe- 1 - 2 r-

e containeTh pyrex-glasa s ri s ampoul cylindricaf eo l shape, with 1.5 mm walls, an outside diameter of 1.7 cm and a height of 6 cm. In order to avoid spurious oxidation while sealing the container, the solution is frozen by liquid nitrogen during this operation.

2 - 2 - Ferrous_sulphate_solution_-_

As the standard Fricke dosimeter, the solution consists of : 1 1 rn.mol.l~ (Ve

1 0.4 mol.l' H2S04 dissolve air-saturaten di d distilled water.

The distilled wate prepares i r thren di e stage normaa : s l distillation and two slow evaporations in quartz equipment using infra-red heating. Becausgreas it tf eo sensitivit organio yt c impuritie solutioe sth n mus préparere tb handled ,an d with particular care glasl .Al s vessele sar cleaned wit slronha g oxidizing solutio pre-irradiatedwitd nan h dose f severaso l kilograys. The water used for rinsing is the same as that used for preparing the solution.

2 - 3 -

Variatio ferrie th f nco ion, concentratio solutione th o n t ni e ,du irradiation, is determined by means of the absorbance variation of the solution measure y spectrophdb o tome try, accordin Beer-Lambert'o gt s law. Thue sth absorbe dsolutione th graysdosn i n i e obtaines ,i ,classicaD e th y db l SO J- formula : 6 ) (1 Q k x — —— — — — x 9.64= 10 . D9x sol e.Ç>.l,. G. U

where

e / (raol.l ) .cm is the molar extinction coefficient for ferric ions at the wavelength used for the optical density measurement ( \= 303 nm in our case) , minus that for ferrous ions, at the reference temperature (25°C) . _3 densite solutioe p/g.cth reference th s th f i yo t m na e temperature (25°C) 1 /cm is the optical pathlength of the spectropho tome trie cell. ) ± 0.0% m 5c 1 (1= G / (ferric ions). (100 eV)~ is the radiochemical yield of the ferrous sulphate solution.

66 & d is the difference in optical density between irradiated solution and blank, measure actuan n t da l temperatur usuall0 e y slightly different thae nth 25°C= referenc 0 . e eon o

k is the correction factor for temperature : 0

) (2 e- oe )( ) a + i C / i = T k

O O _1 with 0, 0Q in C and a in ( C)

Before utilizatio ferroue th f no s sulphate dosimete r calibrationsfo r , different properties and characteristics of the dosimeter as well as those of 1±e spectrophotometer have been studied. Among them, the values ofc » p r a have been determined :

= 216E 3 (mol.l"1% )" 1 1.cm"0. ± 1

p = 1.024 g.cm" i 0.1 S,

a = 0.66.10"2 ("a"1 r. 1.5 %

Cbncernir. valueG e th g, which depend radiatioe th n so n qualitye ,th following convention has been adopted with users : until the end of the ßxperiments carried out at LMRI and at other foreign laboratories for the determination of G values in high energy photon and electron beams, a constan : adoptes t/ i valu5 G / df eo

G - 15.6 i 0.25 (I'fe"3 ions). (100 eV)"1

This convention, though perhaps leading to false reference doses, enables however comparisons between hospitals throughou countrye th t . Nevertheless, this assumption shouldn't be too bad if one considers the G values indicated in ICRU. J report3 , 2 s/

TRANSFE- 3 R PROCEDUR- E

- 1 - 3

o calibratioTh performes ni user'e th n si d beam conditionn ,i s clossa e n.G oossible to the usual ones (this is of particular importance for accelerator beams dosimetee Th )calibrate. e b transfee o rt th d an dr dosimeter successie sar - vely irradiated under identical conditions ,same i.eth e r inciden.fo t bead man same n.th te positio referenca n ni e water-equivalent phantom. The reference quantity is absorbed dose to water, D /Gy ; the calibration -1 factor, F/Gy . (unit of dosimeter reading) , is given by

dosimetee th whers i eR r reading, correcte r dependencdfo n o e temperature, pressure, humidity, recombination, etc...

67 M and M are the monitor readings, corrected if necessary as above; in the case of a Cobalt-60 or a Cesium-137 beam the monitor is simply a time measuring device.

e referencTh e dos wateo t e , rD is obtained from the dose D , measured W sol e ferrouinth s sulphate solution (relatio applyiny b ) 1 n factoga rk correctin g perturbatiovolume e glasth th e size th f solutiof th r e o o s o fo o t t d e nan du container :

(4) DW = °sol

value G e samconvens i choicth e e e th th r ,k reason f r Fo -eo fo s sa P tionally taken equal to unity until its experimental determination.

3 - 2 - General conditions -

Some of the calibration conditions are standardized, they are presented tabln i . 1 e

- dimensions : 30 x 30 x 10 (cm) - water-equivalent composition : 94 % polystyrene PHANTOM 2- polymerizatio% 5 l noi 1-3 % T.O

- density : 1.03 g.cm

REFERENC, 5 , 4 E, 3 DEPT, 2 : H 6 cm

FIELD SIZE : 10 X 10 (cm)

DOSE TO BE DELIVERED : 50 to 100 Gy

Table 1 : Standardized calibration conditions

The water-equivalent phantom is composed (see fia. 2) of five parts : F, f, A1, B. The main part F contains a cavity into which the other elements e wholTh e 4 constitutet fi homogeneousa s parallelepiped, excep r elementfo t whicf h contain dosimeterse sth givea r n.Fo beam quality reference ,th e depth is obtaine orderiny db . (se B , eelemente figA' g th , A .) 3 , sf

For each calibration, three elements "f" are provided : - two containing each three ferrous sulphate dosimeters (see. fig. 4) : one for irradiation, the other for blank, - one for irradiation of the dosimeter to be calibrated.

68 Particula- 3 - 3 r condition_ s-

The source-to-phantom-surface distance is chosen by the user. The reference depth depends on the beam quality :

- for cobalt-60 and cesium-137 gamma-rays and for 2MV X-rays, the recommended referenc. ecm dept5 s hi - for photons of higher energies and for electrons of energies between recommendee MeV5 th 3 , d 10an d reference dept e deptth hs hi correspondino gt the dose maximum determinee b ,o whict s preliminarhy ha db y measurements.

3 - 4 - Uncertainties_-

uncertainte Th calibratioe th f yo n facto rdependF course f so th n eo uncertainties on the readings of the dosimeter to be calibrated and of the monitor. Concernin reference gth e estimatee dos wateth o et , rD d upper bound to the systematic uncertainty is 1.9 % (linear sum of individual uncertainties) and the random uncertainty is usually of the order of 0.4. %.

RESULT- 4 CONCLUSIOD SAN N-

Thirty-two calibrations have been performed up to now. All dosimeters were of the same type (Nuclear Enterprise, lonex 2500-3, 0.6 cm chamber), and had previously been also calibrate termn di exposurf so cobalt-6r efo 0 gamma- rays. Hence, it is interesting to consider, for each chamber and for the different beam qualities dosquotiente e ,th th e f calibratioo 1 sC n factory sb the exposure calibration factor presentee ar value e ' .Th C tablr n f sdi o fo e2 photons and table 3 for electrons, along with indications on experimental conditions and, for comparison, with the ICRU recommended values of C^ and C f2, 37. For photons., it can be seen that C1 and C^ are identical for cobalt-60 gamma rays and for 5.5 MV X-rays and that important discrepancies appear for higher energies (the mean value of the quotient C'/C\ rises to 1.06). In addition correctioeffece e ,th th f to recombinatior nfo chambee th n ni r (less doesn') tha% 1 n t modif discrepanciese yth .

For electrons the differences between C's and C 's, particularly at high E energies, see depeno mt d correctionmainle th n yo recombinationr sfo , whicn hi these cases ris severao et l percen ove; mea e MeVt3 th 1 rn, valuee th f so thesf e 1.0i quotien0ar e C correction/ tC s have been applie notf 1.0d i .4dan

A conclusionsa , this transfer procedure provides more information than only the calibration factor, because all irradiations and measurements with the dosimete calibratee b o rt performe e n beams i d ar hi use e d n th ,an ri y db the cas acceleratof eo r beams influence ,th monitorinf eo takes gi n into account as well as the quality of the preliminary measurements necessary for

69 photon number dose rate depth in correction C (ICRU) quality of C' values rad .min phantom, cm for rad. R rad. R recombination

60C„o äv 7 0 20 50- 5 no 0.95 0.95 1.00

5.5. MV X 1 230 6 no 0.95 0.945 1.00

X V M 9 1 250 2 no 0.95 0.93 1.02

18 MV X 1 400 4 no 0.97 0.915 1.06

25 MV X 5 0 20 17 0- 5 no 0.98 0.90 1.09

1! 1 1.05 140 5 yes °'945 0.90 U 1 200 3 yes 0.98 0.90 1.09

X V M 7 2 1 40 4 yes 0.96 0.90 1.07

Table 2 - comparison of C' values resulting from calibrations of dosimeters and C, values given by A ——————•— ICRU-Report 14 /" 2 / (for convenience, quantities are expressed in non-Si units). electron beam number dose rate, deptn hi correction C1 C (ICRU) E energy 1 phantom for 1 -1 C'/C of C values rad.min rad.lT rad.R Ii McV cm recombination

10 £ 180/260 2 no 0.90 0.89 1.01

» 1 200 2 yes 0.8.8 0.89 0.99 II 1 245 2.5 no 0.90 0.90 1.00

13 1 50 2 yes 0.87 0.87 1.00

II 2 200/220 3 no 0.93 0.90 1.03

16 2 170/210 3 no 0.895 0.87 1.03 19 1 210 4 no 0.90 0.86 1.05

II 2 200 4 yes 0.865 0.86 1.01

II 1 200 5 yes 0.86 0.88 0.98

30 1 150 2 yes 0.82 0.81 1.01

Tabl - Compariso 3 e value1 C f o ns resulting from calibratio f dosimeterno C value d an s s give y ICRU-Repornb t ^_____ £j J (fo 3 2r£ 1 convenience, quantitie expressee sar non-Sn di i units). the choicreference th f eo e depth informationl .Al s relatiy experimentao et l condition measurementd san officiae th usee gives n i th i sr y lnb document sent back to the Calibration Center. After analysis of this document and reading of the ferrous sulphate dosimeters, the calibration factor is established Calibratioe byth n Center.

Becaus thif eo s distributio taskf no responsabilitiesd san ,gooa d co-ordination is necessary between the user and the Calibration Center. Moreover, this procedure constitute technicasa l assistance service, since throug relatione th h s with hospital physicists, many dosimetric probleme sar dealt with.

REFERENCES

- WAMBERSIE J al.1 t e f ,, Précisio,A. n dosimétrique requis radiothérapin e e Conséquences concernan performances choie le tl t xe détecteurs sde s- J. Belge de Radiologie, 52, 2 (1969)

- ICR J U 2 Repor / Radiatio, 14 t n Dosimetr X-ray: y Gamma-rayd san s with Maximum Photon Energ MeV0 y5 Betweed , ICRan 6 U n0. Publications , Washington D.C. (1969).

- ICR / U, 3 Repor f Radiatio, 21 t n Dosimetr Electron: y s with Initial Energies MeV0 5 Betwee d , an ICR 1 nU Publications, Washington D.C. (1972).

- ALMOND J 4 ,f P.R. SVENSSON lonizatio. ,H n Chamber Dosimetr Photor yfo d nan Electron Beams. Acta Biol. Therapy Physics Biology, 16, 2 (1977).

[ 5 7 - SIMOEN, J.P., et al., Transfert de l'unité de dose absorbée à l'aide du dosimètre au sulfate ferreux. Actes Ville Congrès Int. de la Société Française de Radioprotection, Saclay (1976).

72 e - sealeFig th Vie1 -f o wd glass ampoule containin e ferrouth g s sulphate solution

Fig. 2 - View of the transfer dosimeters and of the different elements of the water-equivalent phantom.

73 , \ f 1f

/\ X

^ -_-._^ L

c /\ F

f BAA Af BA Bf AA A BfA AABf

X/cm 2 3 4 5 6

Fig. 3 - Schematic top view of the phantom and orderings of its constituent r obtaininfo s g various reference depth. x s

- Fig Vie 4 f .elemen o w " containin"F t e threth g e ferrous sulphate dosimeters.

74 MEASUREMENT ASSURANCE STUDIES HIGH-ENERGF O Y ELECTRO PHOTOD NAN N DOSIMETRY IN RADIATION-THERAPY APPLICATIONS

M. EHRLICH, C.G. SOARES National Bureau of Standards, Washington, D.C., United States of America ABSTRACT

This is a brief review of surveys on the dosimetry of radiation-therapy e Nationabeamth y s'b l Burea f Standardo u s (MBS)S .NB e Covereth e ar d ferrous-sulfate (Fricke) dosimetry service, a recently completed survey carrie witt ou dh thermoluminescence dosimeters (TLDe dosimetrth )n o n i y cobalt-60 teletherapy beams a TLld plan ,an r )fo s surve f dosimetro y n i y high-energy bremsstrahlung beams.

1. Introduction e 197th 1t A IAEA Meetin n Nationao g d Internationaan l l Radiation Dose Comparisons, ' one of the authors (M.E.) discussed in some detail S involvemenNB e th whan s becomi t ha t e know s measurement-assuranca n e studies. At the time, our Fricke-dosimetry service, oriented mainly towards the uniformity of high-energy electron dosimetry in medical therapy, was about three years old. The author discussed its conception, rationale mechanicd ,an somn i s e detail d showean , d some test results. e servicTh s stili e l being performed, n face i numbe th t f participanto r s has increased from arouno ove t . Instea5 40 r1 d f repeatino d e th g discussions, which are available in the Proceedings of the 1971 meeting, a brief review is given in Section 2 of this report of some of the technical details of the NBS operation that were not discussed in the earlier report. Also, a progress report on the performance of the participant gives i sd plan an r nimprovement fo s n proceduri s e discussedar e . At the 1971 meeting, a possible future survey of dosimetry of cobalt-60 teletherapy sources, to be done with thermoluminescence dosimeters (TLD) s als,wa o mentioned. Since then e hav,w e complete a one-timd e voluntar ydosimetre studth f o y f oveo y r two-third e U.Sth .f cobalto s - 60 teletherapy sources. At present, we are working on the design and

75 calibration of a TLD system to be used in the near future by the U.S. Bureau f Radiologicao l Healt dosimetre a surveh th r (BRH f fo o y ) f U.So y . high-energy bremsstrahlung beams employe n radiatioi d n therapy. Since some e considerationth f o s going inte desigth o f surveo n y program f thio s s f intereso type ar e t independenD systeTL e f choiceo mth f o t , thee ar y include Section i d , althoug3 n e systemth h e differenar s t from that employed by the IAEA.

2. Fricke Uosimetry for the Survey of High-Energy Electron Beam Dosimetry Dosimeters are provided to users requesting assistance with comparing their absorbed-dose measurement n high-energi s y electron beams with thosf o e their peers e dosimeterTh . s consis f ferrouo t s sulfate (Fricke) solution i n ground-glass stoppered radiation-resistant quartz spectrophotometer cells enclose n polystyreni d e holders s show,a e participantn figurTh i n . 1 e s irradiate all but one of the furnished dosimeters to between 50 and 80 Gy to water (500 800d 0an 0 rad electrot a ) n energie sMeV0 5 betwee ,d an 5 n employin e irradiatioth g n geometry (field size, typd siz an ef phantom eo , position of dosimeter in the phantom) given in the Protocol for Dosimetry of High-Energy Electrons. (2) After irradiation, the dosimeters are r spectrophotometrifo returne S NB o t d c evaluatio e ferric-ioth f o n n concentration in terms of absorbed dose in the phantom, using the value for the radiation-chemical yield given in the Protocol. Inasmuch as the disturbanc e radiatioth f o e ne quart fielth y zb de spectrophotomete wallth f o s r cells is ignored (the same value for the radiation-chemical yield being used ove a widr e rang f electroo e n energies e metho)th d canno e considereb t d o providt e participantth e s wit a highlh y accurate calibratio f theio n r system; it simply provides them with an indication of how their dosimetry compares with tha f otherso t . The Fricke-dosimeter solution used by NBS consists of the following conventional ingredients:

0.001 M Fe(NH4) (S04)2> dissolved in

N H 2a S0O. 4, well aeratedd ,an 0.001 N NaCl.

76 Because of addition of NaCl to desensitize the system against organic impurities e recomme,w e belo us n absorbed-doss wa it d e rat f abouo e t 103 Gy/s (10 5 rad/s), since NaCl causes an increase in the rate de- pendenc e radiation-chemicath f eo l yield. A simplified reaction mechanism (withou e NaClth t s showi ) n below in orde o - reminentert 0 r e w readeth ho ds f into re reactio th o d an n determine e F syield ' . Fe++ + OH -> Fe+++ + OH"

2 H0 * • 2 0 + H

ii _i_ r i " HO + e F > - 2 H0 + Fe + H> - 20 2HOH "+

++ +++ " FeOH H+ + 2 Fe0H > 2O - + A fresh batch of Fricke solution is prepared prior to each shipment and decanted inte individuath o l dosimeter cells. Rather than using glass vials, we find it advantageous to use the stoppered spectrophotometer cells in which the optical density of the solution is eventually measured. e glasTh s vials woul e lesb d s costl d directlan y y scalablee th t bu , solution would have to be decanted into spectrophotometer cells for readout e havW . e shipped Fricke solutio e samth en i nspectrophotomete r cells for the past 12 years, with an attrition of about 20 percent only, during this period e relativ,th e standard deviatio e averagth f o ne reading thesn i s e cell f irradiateo s d Fricke solutio s increaseha n d fron, about 0.8 percent to a still satisfactory 1.2 percent, probably because f smalo l nick r scratcheo s e celth l n i swalls e thereforW . e consider e initiath l larger investmen n spectrophotometei t r cell o havt s e been worthwhile e majoon re Th disadvantag. f usino e n unsealea g d systes i m the necessity of ensuring shipment at low altitudes or in pressurized plane compartments in order to prevent oozing of the liquid and loss of oxygénation. We initially cleaned all spectrophotometer cells with detergent in an ultrasonic cleane d froan r m the n kepo n t them filled with Fricke solution. All other glassware was initially cleaned with hot concentrated sulphuric acid sincan d e thes beeha nn kept filled either with Fricke solution or with pure distilled water. No plastics are ever in contact with the Fricke solution. We now produce our own organic-free distilled

77 water, in a permanganate distillation operation. ' We measure the change in optical density spectrophotometrically at the conventional 304 nm absorption peak of Fe+++ and from it determine absorbed dose to wate publishea vi r de radiation-chemica valueth r fo s le ferrous yielth f o d - ferric oxydation reaction e radiation-chemicaTh . l yield,s i G(F , ) e define e numbee F th . f s ionExpresseo a rdeV s0 forme10 n r i d pe d terms of molar concentration, M (mol/1) and absorbed dose D (Gy), this relationship becomes:

(1) G(Fe+++) = 0.942583 x 107 M/D ,

if the mass density of the Fricke solution is taken to be 1.024 g cm~ . Optical (transmission) densit . Transmissio nm measures i y4 30 t a d n density corrected for losses through scattering in the optics of the spectrophotomete s usualli r y called absorbance , whic,A y Beer'b h w la s is relatee molath o rt d concentrationy b , ,M

(2) A = e M d,

where d is the path length through the solution, in centimeters, M is e molath r concentratio e molath s ri molen i extinctionr e lite pe sd an r n coefficient. If one combines equations (1) and (2) one obtains

(3) D = 0.042583 x 107 ——————— Ae G(Fe+++)d

e changth s absorbancn wheri i e A A e e befor d aftean e r irradiatioe th f o n solution, and Ae ^e(Fe ). We initially chose to do our spectrophotometry at the conventional wavelength of 304 nm but may in the future decide to switch to a readout at 224 nm. ' The advantages of spectrophotometry at 224 nm are (a) an extension of the useful absorbed-dose range (about 5 to 350 Gy) to doses lower by a factor of about 2; and (b) a smaller dependence of the molar extinction coefficient, e(Fe ), on temperature (0.13% per °C). Prior to switchine woulw , dnm o verifreadout 4 g 22 yt a t that t thi,a s wavelengthe th , extinction coefficient of Fe is neglibly small compared to that of d that a consequencean s m ,a n 4 equation i 30 e t A ,a ) s (3 i n t i s a , Fe still can be set equal to e(Fe ).

78 For spectrophotometry to yield sufficiently accurate results, the following parameters e checkedb hav o t e : ) Wave-lengt(a absorbancd an h e scales provideS NB . r thifo ss purpose standard reference filter liquidr so quartn i s z cells ' Sinc. e aqueous potassium nitrate has an absorption peak at ^ 304 nm, it may be used for day-to-day checks on wavelength stability and absorbance-scale linearity.

i ii (b) Molar extinction coefficient, e(Fe ). While values for this quantity are given in textbooks, it is advantageous to determine it experi- mentally for one's own instrument and operating conditions, particularly because of its relatively strong temperature dependence and also because of the possible deficiencies in the optics which, in some instruments, cause its valu o changt e e with absorbance level. This determination involve e carefuth s l preparation of FeJ.J.J . solutions of a number of different known molar concen- trations, starting with electronically FrickeS purifieNB e -th dn I iron ' . dosimetry service, absolute dose determinations of high accuracy are not attempted; therefore absolutn ,a e determinatio molae th rf no extinctio n coefficient actually is not required; yet, it still is necessary for us to determine whethe e extinctiorth n coefficien constans ti t ovee absorbancrth e range of interest. One of the main features of our procedure is that we pre-irradiate all dosimeters, giving about 50 Gy (5000 rad) of cobalt-60 gamma radiation and using only dosimeters whose performance proves satisfactory.(8) Inasmuch as there is absorbance growth with time after preparation even in the dosimeters with satisfactory performance, AA in equation (3) has to be correcte r growtfo d h between preparatio d readoutan n , particularly since, becaus f delayo e dosimeten i s r returns fro e participantsm th som f o e e th , time between initia d fina an lweeksx le ordesi r th readouFo f .ro f o f i t this correction, we use the average growth on all unirradiated controls (shippe d unshippedan d ) whic e finw h d add t leasa s 1 percente tota th lo t uncertaint r procedurou f o y e because growt differens i h r differenfo t t cells. e overalTh l uncertaint r dosou en i ydetermination s currentl s takei y n aboue b o percent4 t , which coul decreasee b d morf o e dus readile th y b y thae dosimeteon n r measuremenpe r mora ty eb poin uniford an t m growtn i h absorbance from cell to cell between the readouts before and after irradiation by the participants, as might be achievable in a controlled

79 sealing procese typth ef o sdiscusse e nexth tn i dparagraph e quoteTh .- un d certainty does not include the systematic uncertainty caused by the assumption of a constant G value over the electron-energy range unaffecteV Me e presenc0 5 quarte th o froth y t b d f 5 mzeo cellsr ,o cause y non-uniformitb d e absorbeth n i y d dose ovee 1-cth rm e deptth f o h dosimeters' sensitive volume. Over the years, we have come to regret that we started with an un- sealed syste s operationa spitn it i m f o e l advantages, sinc a eseale d system may offer better stability. For this reason, we are now investigating the use of seal able spectrophotometer cells with necks graded from quartz o Pyret x glass, filled with Fricke solutio d sealedt weri an n ef I possibl. e o product a batce f suco h h dosimeters tha relativels i t y f stablo d an e uniform sensitivity r manfo yt i e successivcoul ,e on us d e irradiationd an s dose evaluations, particularly in conjunction with an up-to-date stable and sensitive spectrophotometer and readout at a wavelength of 224- nm, which might make it possible to go to lower doses and nevertheless decrease measurement uncertainty. We also have been discouraged by the relatively small improvement in e overalth l performanc e participantsth f o e e conside w e result f th I :l al rs obtained in the years from 1967 to 1975, we find that over 40 percent of the doses assigned by the participants differed from the NBS dose inter- pretation by more than 5 percent. These results are shown in figure 2. The improvement, if any, among regular participants was small, at least up to 1975. However, during the last year or two, considerable overall improvement was observed. In the last survey, the dose assignment of only 16 (or 24 percent) of the 68 dosimeters irradiated differed from the NBS dose interpretation by more than 5 percent. This is an encouraging sign of an increased awarenes e radiation-therapth y b s y communit e importancth f o y e f carefuo l dosimetry e hopW .e contributin ar tha e w t t leasa a g o t t small exten o thit s awareness. 3. TIP Systems for Nationwide Surveys of Cobalt-60 Teletherapy and High-Energy Bremsstrahlung Dosimetry 3.1 Cobalt-60 Teletherapy-Dosimetry Survey The cobalt-60 teletherapy survey was a one-time endeavor supported in part by the U.S. Bureau of Radiological Health (BRH). We mailed TL

80 dosimeter U.Sl al o .t s user f telethorapo s y d expressesourceha o wh s d their willingness to participate. Figure 3 shows the commercially available hermetically sealed dosimeter bulb containin a heateg r stri d smalan p l plaques

of the CaF?:Mri TLD material, which for shipment was enclosed in a suitable plastic container. While this system is initially more expensive than TLU powder or bare plaques ("chips") of the TLD material, it can be handled by a technician wit o previoun h s experienc n thermolurninescenci e e dosimetry. Also, since no large variations in source spectra were expected in the teletherapy survey, it was decided to use the CaF„:Mn phosphor which in th d foune ha paso perforn t de w t . reliabl d whican y h often canno e useb t d because its atomic number is higher than that of water and tissue. The readout system consisted of a commercial unit containing the heater- pholomul tiplier assembly, while general laboratory equipmen s user wa tfo d timingr integratingfo d ,an , digitizin d recordinan g e signalth g . With dose interpretation fro average e readingth mth dosimeters5 f o en o s n ,a overall uncertainty of about ?.5 percent was attained. This includes the uncertainty introduced by the need for correcting for a trend in the readout system, which tende o becomt d e more efficient with consecutive readouts of one dosimeter every 25 or 30 seconds over a period of several hou*".. { I 'no effect probably was due to a rise in the temperature of the rc.-.'j'-r electronic t sentirel no whic s wa h y compensatee phototh y b - r fo d r . i •". ior% cooliriu circuit.) The results of the survey are shown in .;;;>., ,•- onstratin • ." f. g tha r ovefo t0 percen8 r a tota f f o tabouo l 0 90 t ,r ' ..,r;.-yi"J ehe dose interpretation was within 5'percent of the requested >'.(, -, '7 '-, oy (30;! rad) to water.

t£ahJuiT^-p_o_si^eJ^ry_ Su_ry_ey j r,urvc. f high-energo / y bremsstrahlung dosimetry e cannoon , t rule oui LL 1Ü.c .u ; contributio o dosimetet n r respons f low-energo e y photons i:.igril, '.'dry sufficiently from e rrachinhighth f -o o machint ee us o mak t e th e atoniic-nuiiibcr GaF,,:Mn dosimeter undesirable. Gecausc of our experience in the past with spurious readings on LiF both in the form of powder and in the fori f TLD-10o u 0 chip e firsw s L tT investigatef o t ar e e statth th df eo dosiüietry with lithium borate, whic s commercialli h y available e eitheth n i r form of discs in which the crystalline powder is incorporated in a vitreous

81 material(Studsvik e for th f pressed-powde o mn i r )o r chips (Harshaw).e Th * results revealed e presentha th vien i tf o wt stat f developmeneo f lithiumo t - borate TLD materiae th , le recommende b coul t e planneno dth r dfo d survey. (The lithium-borate powder in the vitreous matrix fades more than the pressed lithium-borate chipsn contras i e presse t th ,bu o t d s chipi t i s t hygroscopic.**no e thereforW ) F i L ef o adviseo continu t e us H BR e d th e TLD-100 which they are employing for a number of other surveys, in con- junction wit a hot-nitrogeh n reader preliminara n I . - be ye studth f o y havior of 200 identically irradiated TLD-100 chips handled with suction picku d reproduciblan p C followey° annealehou0 1 40 hou1 y r b dt r ra fo d C befor° 0 a10 et irradiatio d anothe an nC befor ° minute0 0 1 r 10 e t a s readout, spurious readingt occurno d .di s This annealin d readouan g t procedur s repeateewa d nine times oveo weekscourse tw e th r Th f .o e results of the study indicate that there is about a 1.2-percent relative standard deviation from the average of the day-to-day readings on a single chip e relativTh . e standard deviation froe average th mth f o e readings of all the chips in the batch generally will be larger, its value dependin e e readingsprea e th th selecte n th n i o dgf o s d chips after identical exposure. For the present study, a batch of 100 chips was selecte d3 percen _ wit+ a h t sprea n readings i dy give an n nO .day , this batch yielde a d1.8-percen t relative standard deviation froe averagth m e e chips e th reading th l .al f o f o s So far, our investigations have included studies on the choice of phantom material and phantom size for source-to-axis-distance (SAD) irradiations with a 10 cm x 10 cm field size at the various depths of e possibilitinterestth n o d f obtainin,an o y g depth-dose information o n e participantsth ' a singlbea y b m e irradiatio a numbe f o nf dosimeter o r s positioned at different phantom depths, all on the beam axis. The results were: (a) Within the measurement uncertainty, the TLD readings -2 obtained ove ra rang f e depthphantoo e th m n c i s mg fro0 1 mo t abou 5 0. t

*Comtnercial product identification doet implno s a recommendatioy r o n endorsemen y NBStb r doe ,implt no i s y thaS considerNB t e identifieth s d products to be the best available for the purpose. **We subsequently learned that the increase in fading also will be observed e crystallinth n o e powder use y Harshab d wintroduces whei t i n a n i d vitreous matrix.

82 with cobalt-60 gamma radiation are nearly the same in phantom consisting of a polymethyl methacrylate (PMMA) cube with 15-cm sides and one with 20-cm sides. However, there is a trend toward higher reading e largeth n i sr phantom.* (b) Within the measurement uncertainty, the readings obtained ia PMMn A phantoe singlon n i me irradiation with dosimeter t deptha s s _2 e sam th s thosa e e ar e obtaine m c betwee g n separat i 0 d1 d n an aboue 5 0. t measurement t eaca s h depth. However a wate n i , r phanto whicn i me th h dosimeters are held in plastic inserts, there is a significant difference e readingith n f dosimetero s s irradiated separatel d simultaneouslyan y , probably because of displacement of water by the plastic inserts. We further obtained a cobalt-60 gamma-ray calibration of the TLD-100 samples in PMMA in terms of absorbed dose to water as a function of depth e phantomith n e distancTh . e betwee e detectoe sourcth th n d s kepean rwa t constant (1 in) and the beam cross section at this distance was 10 cm x 10 cm. e readingTh s obtained were compared with source-standardization data derived from absorbed-dose calorimetr e sam e th sam eth n i ey bea r fo m field size and distance. Figure 5 shows the results. The readings were arbitrarily fitted to the absorbed-dose curve at a depth of 5 cm, but could be fitted just as well at any other depth. Also, in order to tie in directly with IAEA measurements e sen,w r phanto ou t f 20-co m m side length, loaded in several depths with individually calibrated LiF-TLD-100 samples, o Massachusettt s General Hospital (MGH r irradiatio)fo n theii n r 10-MV bremsstrahlung beam unde e conditionth r s employe e cooperativth n i d e study with the Harvard School of Medicine and the IAEA. A preliminary evaluation of the results after return of the loaded phantom to NBS gave -a value of quotiene absorbee th th lulr f f° lo t d e dos th wateo t ed an r H quoteMG y b d cobalt-60 equivalent dose to water evaluated at NBS with the aid of absorbed- dose calorimetry data. This agrees well within the uncertainties of the measurement and evaluation with the value of 1.014 for this quotient, obtained in the MGH-IAEA experiment of March 1, 1979. (See table II on page 124 of these Proceedings.) For the NBS-MGH study, the relative standard deviation of

*This finding agrees with earlier depth-dose measurements witn chamberio h s in graphite phantoms made by J. Pruitt and S. Domen of our laboratory, who found a difference of 0.7 percent at a 10-cm depth. 83 a single reading froe averagth m f nino e e TLD-100 sample reading eacn i s h of four different phantom depths was about 0.7 percent. Finally, in order to arrive at the number of dosimeters required per measurement (correspondin e numbeth f o readingo t rg s froD powdeTL m r at any one measurement position) for a preselected level of uncertainty, we made a careful assessment of the random and systematic uncertainties entering into each step of the dose interpretation. The steps considered were: ) Cobalt-6(a 0 irradiatio n dosimeter f o n s (applicable also t o powder sufficien readingsn r e selectefo tth n )i d geometry readoutd ,an . ) Relatin(b n reading e average cobalt-6e th gth th o f t so e 0 gamma-ray exposur e pointth t .a e ) Irradiatio(c m f dosimeterseto nf o s varioun i s s calibrated high-energy bremsstrahlung beams of the type to be surveyed. (d) Relating the average of the m readings to absorbed dose e high-energo watet th n i r y bremsstrahlun e deptg th beaf interesto ht a m . ) Determinatio(e e correctioth f o n n e readingfactoth o t r s obtained with cobalt-60 gamma ray e irradiatesb f sample(steo i t ) e a p ar sd with high-energy bremsstrahlung instead (ste. c) p Preliminary resultr analysiou f o s s show that r suitabl,fo y selected batch-calibrated TLD-100 samples, averages from reading 9 sample n o s s n uncertaint a lea 4 percen finae o o t dth t ln 3 i t dosf o y e interpretation. When individually calibrated samples are used, this value is lower by abou e percenton t . t presentA e absorbe,th d dosr high-energfo e y bremsstrahluns i g usually determined froe respons th me bremsstrahlun th n i e gn a bea f o m ionization chamber originally calibrated in terms of exposure with cobalt-60 gamma radiation and multiplied by a suitable correction factor (C,).e Inasmucth e uncertaintf o th e s b a , which C, y n ma hi y percent5 o participantsl t ordeal 4 e sam,r f o th rwilfo e s e b lwa t i , decided to exclude it from the estimate. If, at a later date, calorimetric measurements will be used to obtain the absorbed dose for the high-energy bremsstrahlung irradiations e treatmenth ,e resultinth f o t g uncertainty will be reconsidered.

84 Acknowledgment wore kTh .relate o dosimetrdt n cobalt-6i y 0 teletherapy

beams discusse n thii d s pape supportes wa r e Radioactiv th n pari d y b t e

Materials wore Branchth kd relatean , o dosimetrdt n high-energi y y brems-

strahl ung beams by the Medical Physics Branch of the Bureau of Radiological

Health, FooDrud an dg Administration . DepartmenS . U , f Healtho t , Education

and Welfare.

References

1. M. Ehrlich, National and International Radiation Dose Comparisons, IAEA-PL-479/8 (1973). . 2 Protoco r Dosimetrfo l f High-Energo y y Electrons e Subcommitte,Th n o e Radiation Dosimetry of the Am. Assoc. of Physicists in Medicine, Phys. Med. and Biol. 11_, 505 (1966). 3. See, e.g., H. Fricke and F. J. Hart, Chemical Dosimetry, in Radiation Dosimetry . Attix H . . TochilinRoesc E C . F d . , ,W , an hVol2 . , editors, Academic Press (1966). Chesler. N . Gump. . HertS H S . . al.t ,B H . ze 4 , Trace Hydrocarbon Analysis, p. 49, Appendix A, HBS Technical Note 889, U.S. Government Printing Office, Washington, D.C. (1976). 5. K. Scharf and R. Lee, Rad. Res. 16, 115 (1962). 6. Catalog of NBS Standard Reference Materials, MBS Special Publication 260, , U.S.55 d Governmenan pp 2 . t Printing Office, Washington, D.C. (1975-76). 7. L. A. Machlen, Center for Analytical Chemistry, National Bureau of Standards, private communication. 8. M. Ehrlich and P. J. Lamperti, Phys. Med. Biol. H, 305 (1969). 9. A. C. Lucas, The Harshaw Chemical Company, Solon, Ohio, private communication. 10. B. E. Bjarngard, B. I. Rüden and B. waldeskog, Evaluation of Results a High-Energ r fo y X-Ra d Electron-Dosimetran y y Stud n thi(i ys Proceedings volume).

85 Fig 1 . Fricke Dosimeter Units e spectrophotometeTh . r cell fits snugly inte polystyrenth o e blocke finisheth n i ; d assembly a ,styro - foam plug presses agains e stopperth t d n placekeepi ,an t i s.

ijj'O I

œ ul g 50

PERCENT ERROR

Fig 2 . Electron Dosimetry Performance, 1967 throug hdosee 1975Th s. assigne 8 percen 5 e dosimeter th o t df to s agreeS dNB wite th h dose interpretatio withio t n percent5 n 3 percen;2 e th f to dosimeters showed differences between 5 percent and 10 percent, an9 percen1 d t differe y betweeb d percen 0 1 0 npercent4 d an t . 86 Fig. 3 Schematic Diagram of the CaF2:Mn Bulb Dosimeter (center) and Polystyrene Halveo th f Tw o s e th e Holder (lef right)d an t .

too

eo Ul I z (T 60 ï y

u. o cr ImUJ -Mi-

n „-..-,i <-25" -20 -10 0 10 20 ' >25 PERCENT ERROR

Fig4 .Performanc f Participanteo s Involve Surveye th n i d. Shows i n the difference, in percent, between the dose to be delivered by the participants and the NBS dose interpretation from the averagresponsee th five f th eo e f sirradiateo d dosimeters. 87 F u in 90

80

tr.LU a j ABSOHBED »osr.

LÜ in o f! O LU

I 1/5 6 10 Cti DEPTHm c ,

"icj. 5 ; 'Co CalibraLion of TLD-IOO in a Ib-cin x Ib-an x 15-CM Poly- i-ethyl ."ethdcryldte (PMMA) lhanto:.i. 10-c::i x lO-cm field si/e

aL each depth. Solid lino: j absorbed dose to water; error bars: standard déviation (••- O./ ) for a single dosimeter readimj obtained fronaveratje th : o readin calibrate9 f o g d dosimeters at each depth. The average dosimeter data were M tied to the dhsorbed-dose curve at tic arrow (at a depth of 5.00 cm in P/'-'A, corrosuondincj ;.o :>.'// q cnr in wa'cer, deptc whic Lh n walei h s r i hwhic fo r e percenth h t depth dose ? s approximateli t e !>.0a n sd:;:ti PMMA) th yn s a 0;Ci .

88 REVIERESULTA E TH F WO S OBTAINEY DB NPL/PTE TH B FRICKE DOSEMETER CALIBRATION SERVICE IN GERMAN RADIOLOGICAL CENTRES

H. FEIST Physikalisch-Technische Bundesanstalt, Braunschweig, Federal Republi Germanf co y

In 1972 the Physikalisch-Technische Rundesanstalt (PTB), the national stan- dardizing laboratory in the Federal Republic of Germany, decided to make the Fricke Dosemeter Calibration Service of the British National Physical Labora- tory (NPL) available to German radiological centres. This service has been establishe y Ellib d n 196i s 9 (1) e iraiTh .n feature f thio s s postal reference servics followsa e ar e : Fricke solutio sealen i n d pharmaceutical plass ampoules is made available by the NPL twice per year in May and November. The PTB dis- tributes the dosemeters to the participating institutions, collects them after e irradiationsth r evaluation fo d return an L , NP e s th theA .wate o t m r phantom and data sheet o protocot s l detaile irradiatioth f o s n condition e providear s d by the PTB. Moreover, the PTB offers general advice and assistance in analyz- ing the results. Apparently this activity is very similar to the manner in which inter-comparison IAEAe th e carrie.y b ar sEac t hou d participan dosemetea f to r issue can obtain a set of 10, 12 or 14 ampoules, 4 of which have to be left unirradiated as controls. Of course exceptions are possible and higher numbers of ampoules are conceded when an extensive calibration program is taking place y centerian n e perio.Th f timo d e that elapses between dispatchin e doseth g - e evaluatioth d meter averagen week5 an a s L n i nsso NP froe . th m

The dosemeters are offered for irradiations in the water phantom with cobalt-60, high energy electron MeV)8 > ( megavoltagsd ,an e photons partie .Th - cipant e aske sar o irradiat t d t depthea appld an s y conversion factors given by the corresponding ICRU Reports 14, 21 and 23. In order to secure identical irradiation condition eacn i s h institution phantome th , e suppliee ar s th y b d PTB e user eithereny wateo Th e . rma tth y rbu phantom watee Th . r containers themselve e ordinarar s y polystyrene fish tanks (Fig whic) 1 .e kep ar n hi t stock .A suitabl e lid e chemica ,holdea th r fo rl dosemeter d fitte,an d holders for the ionization chambers, according to specifications given by the user, are manufacture B workshopPT e th n .i d

With cobalt source e irradiationsth Fricke th f eo s dosemeter e doseth d - san metercalibratee b o t s e usuallar d y performed sequentiall beae th m n yo axi s e phantomith n r irradiation.Fo s with accelerator recommendes i t i s o irrat d - diate both dosemeters simultaneousl botn o y h beae sideth mo t f saxi o d san swop them several times during the irradiation in order to overcome beam in- stabilities.

89 Each dosemeter SLiOJU obtai n absorbea n r thidFo sdos . f aboucasGy o e e0 4 t a random uncertaint r cobal f aboufo o y L ttNP irradiate+0. e quotes i th 5 % y b d d % confidenc 5 9 ampoule e th et a sleve l wit degree8 h freedomf so determino .T e this uncertainty f ampouleo e samt th se e f a so batc, s irradiatei h d with cobalt in the NPL at about the same time as the irradiations take place in the cen- ters. These ampoules are evaluated together with the returned dosemeters of the participants. Since 1977, further independent cobalt irradiations have been car- ried out in the PTB in order to rule out "travel effects". The differences resulting from the absorbed dose determinations by the PTB and the NPL have always been les. s% tha5 0. n

(Afte a pilor t stud n Novembei y r 197 e regula2th r Fricke dosemeter service r Germafo n hospital d othean s r interested irradiation centres startey Ma n i d 1973 e tabl.Th e illustrate e developmensth t till now.

Table. Number of participating centres and of dosemeters irradiated in Germany between 1973 and 1978.

Number Dosemeters irradiated with Dat f issuo e e f centreo s Co electrons photons

May 1973 9 41 19 10 November 1973 6 7 33 11 May 1974 9 25 40 16 November 1974 4 7 18 8 May 1975 7 23 21 13 November 1975 8 25 28 24 May 1976 7 25 26 10 November 1976 11 35 23 34 May 1977 7 26 27 12 November 1977 11 31 31 8 May 1978 9 25 27 18 November 1978 9 28 31 20 Total 97* 298 324 184

0 differen4 * t centres. Som f theo e m took part several times.

Fig show2 . s frequency distribution ratie th f absorbe o f o s d dose determined by the user to absorbed dose measured by means of the Fricke dosemeter r cobalfo s, electrons60 t megavoltagd ,an e photons. Additional- e frequenclth y y distributio e cobalth f o nt irradiated dosemeters (left side below) is split into two fractions- Intercomparisons made during the first period froy 197y 197Ma Ma m 63o t (left side above d thos)an e during tne second, period from November 19?6 to November 1978 (left side middle). e mosTh t striking featur f theso e e distribution e asymétrith s si e shape. Wherea e asymetrth s onls i y y slightly indicated durin e initiath g - pe l s morriodi et i ,marke d durin e lateth g r one explainee .b Thiy ma s s a d follows: In the beginning the users could not refer to reliable calibra- tion factor f theiso r lomzation dosemeters. Henc distributioe th e s i n wide-spread. Later on some users adopted the calibration factor obtained

90 from a previous participation in the Fricke calibration service. Other institutions used calibration factors obtained froe manufacturerth m , the Physikalisch-Technische Werkstätten Freiburg (PTW). There are, how- ever, some indications thae calibratioth t n factors that originate from this laboratory tend to be lower by 1.5 % than those originating from the NPL. The difference may eventually be due to the primary standar- dizing laboratory which is the PTB. Therefore the PTE is going now to investigate this phenomenon carefully.

The fact that it is possible to resolve such small effects, proves e precisioth n claime r measurementfo d s with Fricke dosemeters. This i s n essentiaa l advantag e Frickth f eo dosimetry, which shoul e takeb d n into consideration for intercomparisons, when a total uncertainty of less than 2 % is required.

The results of the electron irradiaticns are poorer. Several facts increas uncertainte th e f electroo y n interconparisons r instancefo , : a) Strong dependence of the absorbed dose conversion factors or. the elec- tron e effectivenergth t a y e poin f measuremeno t t whic usualls i h y differen e ionizatioth r fo t n e chambeFrickth d ean r dosen:eter. Unknow) b n contaminatio e primarth f o ny electron bea y photonb ~ r strao s y electrons.

Furthermore one has to rc.i'.ize that rrost of zni chsnbers have not been designed for electron irradiations and nught have suffered from a "pola- rity effect" (2) t shoul.I d als mentionee b o d thanese th tt significant discrepancies occured whee electroth n n energ s belo e recommendewa y th w d lower ]im:t of 8 "eV. Allowing for all these sources of uncertainty, the results are quite satisfying.

Similar considerations are valid for the megavoltage photon irradia- tions. Of course the- asymétrie structure of the cobalt distribution is also reflecte e electroth y d photob d an n n distributions since many insti- tutions carrie ; intercomparisonou d s usin e samth g e calibrated ionization chamber for HJ 1 three types of radiation.

Finally two outstanding results of this caiinration service are to be mentioned. The first result is that a discrepancy between absorbed dose determinations based on the C^ concept and on the measurements with Fricke solution respectivel V bremsstrahluns beerMe ha y ,2 & foun r fo d g already in 1973 (3). On an average, the absorbed dose determinations by means of Fricke solution usually give values that are about 3 % higher than the results of ionization chamber measurements for this radiation quality. This might arise fro a trum eabsorbee valuth f o e d dose conver- sion factor tha s highei t r thae valuth n e recommende e ICRUth n I y .b d 1974, a discussion on the discrepancy between the C and the C^ concept was launched, mainly by Greening (4). Now it is commonly agreed that the compositio e ionizatioth f o n n chamber wall affect conversioe th s n factor

91 and increase bren'Tt.rohe V recoir-endeth "r s 2 £- r fo 1.unp, c' " vajvi, y : e if iiri ior.izaLion chnr-jtsrr •*!•„;, a*, r '.:•;•; i v« .or:' *alls> :s •,.£•.>.;:! !L>;. Tp.vrs.Ti- j:atior.B c't. the ï'Tiî ccnf :.ri; ed î.ht-i'.e f .:r)!i:::p:: •: '.

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:. I c--( '. y ff::.firre- d thr rcr-,;l;:; oo^oi:.« ri iv T.'-.o .'r:::K(! co".rn( *,.prs;. IL har, e r.-I.rb o :t i l.' tr.<-ie «r ,W:.Gh r t > affr.i r r..t.i":^ r I :-;i:.rT r rv.-s: erio;:£,. Any a y* 'vi.c1 Fricke col it/ration srrv. ce i.a£> vrever-tcd that ss^riojs; hc.rr1 A'JIS cajnec. '"iir ".otnor /-ratof i.Py ackr:oA'lrd,~t .•; r-r\:. v Ji:rf..'. r:i :•"'.:<• F:oriî: v::h "T. F. C. KJlis of the N;-i: ioîiFil rjysicc'.i L,;"j(.'i ûL": y 'i < i:<:. r.f.icin.

i'ri' er on fee:

(1) rljis, F>.C., 7r. ;:;;•;L rc - Ir.fil.icr f o Jjiisor'ije. d dos,o star.darri y chrii.icsb s i dosimetry nec::;ir K-I.i . i-.:-.c c /,-.. ^h jse. iv.f -o i ::cBC-ioter, Ion: /.inj', Radi;:- tion Xetroloci'i eti: '.' i; ;:y i: . Car.,",:1..! (197"! (2) Markus , lor.Ü. , i z;-,:, lor. cr.".-i."< ri >, fret f c polarit- y {.fie , rta intende d for electron dccir.ctry , IAEA-S"-"n')" '3'-

(3) y'o-.Rt. , ErfeL-r.'H. , . s f.;r>cDouco : a noTor-Vrrfli'ic'.'.i-dierictt's; cier J'T3 ;:r- .t tols cnerinohcr "or- ;,,;:: : i •..>:-, Mod inir-ch. :/ o F:.yr,: n Fcrachunfi k d un , Praxis, edited oy A. Kiiui 'I3'76; (^) Grecnint; , DOP. i : P . J converaic:, . fictcr. r electron:;fo s , Phys. Heo. 3 G (1974) 7/.6 (5) /• J-Tor.c: , F. 1?., Sverinr.cri , :-;., loniî'.fi! ior. c:.r. :.'•:.<.• r nosiiie'ry for phoron and electron bear u , Acta had:o:. Vnc.r. rhys. ;;-Ol. J^C >: (1Ü77) 177 i > (6) Feist, !!., Urr>.t ru'.:c. :.:r.f) des Konvcrn:or.r.f;:k'cort. >:ur P(:s~.:"..uri£> der F.nerp.i t'dosîis in 'J.a:;scr f'.:r !!r(;r::a Lr;.::lurip vor. ^-? "cV C.-rc'nzenc'rf ie , Vedizir.ischie . i'hysiü r- , eic D 7 kh l-.rr.p., iiUth;;- Vcrln;- Koidnibcrp, j.r Druck.

92 !Ul uM iUl

CD

214

eCDn

230

polystyrene Sketc. Figl th . f ho e water phantom with holdechemia r rfo - cal dosemeter.

93 020- 60rCo (May!973-Moy!97GI 0 15- (130) 0 10- electrons 0 05- 0 20- (May 1973-Nov 1978) (316) 0- i ,,M,l | i | |I l 1 || , . Il 015. 10 025- 0 10- 50Co 020- (Nov 1976 -Hov 19781 ° °5" 015- 1136) o- /^H[- ^al - Il Ml h M -u 080 B11 092 5 0910 5 0 1. 010-

005- 1 r I 1 : o-i lit. ,1 I i f ,,,,,, megavollage photons 10 ; 025- 020- (Hay 1973-Nov 19781(187) \ 020- Co total fl]sj (Hay1973-Nov 19781 015- (266) 010-

010- 005- 1 1 1 1 0- i 005- -4J-1- v1—f- — n r l h - - • . 083 092 095 10 105 110 n- |.| l i , I.. 1 1 1 i . , t , 0 1 l 5 10

Fig. 2. Frequency distributions of the ratio R of absorbed dose deter- mined by institutions to absorbed dose measured by NPL Fricke dosemeters for various radiation qualities. In brackets time period and number of ampoules.

94 FeSOF SOMO N THI E EUS PRACTICAL ASPECTF SO

HIGH-ENERG4 Y PHOTO ELECTROD NAN N DOSIMETRY A. WAMBERSIE, M. PRIGNOT, Cliniques universitaires St-Luc (U.C.L.), Bruxelles, Belgique A. DUTREIX Institut Gustave-Roussy, Villejuif, France

Abstract f FeSOo n e somi ,us e e practicaTh l aspect f high-energo s y photon and electron dosimetry. e advantageTh f FeSOo s e discussear , d with respecs it o t t applications in practical high-energy photon and electron dosimetry: (1) the calibration oE ionization chambers, (2) the evaluation of the importanc n recombinatioio f o e n chamberi n s expose o higt d h dose e determinatioratesth ) (3 , f absorbeo n d dos n radiobiologicai e l samples 'and (4) the use of FeSO, as a transfer dosetneter. The absorbed dose conversion factors, C or C\ of an ionization chambee determineb n ca r y comparisob d n with FeSO,.The response e FeSoth fO dos e G-valuee th mete a r functio e (o beas ra ) th m f o n 4 quality can be considered as constant for high-energy photons and electrons in the usual energy range.An FeSO, dose meter can also be use o evaluatt d e importancth e n recombinatioio f o e a chambe n i n r expose o higt d h dose-rate f electronso s , sinc s responsit e s i e independen. ) 0 Gy.1 s x f dose-rat2 o t o t p (u e Examples are given to illustrate the interest of FeSO^ for measurement f absorbeo s d dos n biologicai e l samples, mainl n depti y h in electron beams wher e dosth e e gradien s high.FeSOi t e b n ca , assume e insensitivb o t d o energt e y variatio o dose t n dept i nr -(o h rate variation); it does not introduce any heterogeneity and no dis- placemen e applieb t o factot s dfinally; ha r e dosth , e meter solution n occupca a volumy e identica e biologica th o that lf o t l systemo t s e irradiated.Fob r these applications e resultth , s obtained with FeSO are compared with those obtained with other dosimetric systems. r experiencOu e with FeSO, a transfeuse s a d r dosemete r interfo r - comparisons between center s reportedi s .

INTRODUCTION

Although ionization chambere dosemeterth e ar s s most commonly used for high-energy photon and electron dosimetry, the FeSO, chemical dose mete s propertieha r s which mak t particularli e y suitabl r severafo e l applications.The purpos f thio e s o papet s i r repor e maith tn r experiencpointou f o s e wite Frickth h e dosemeter in practical dosimetry of high-energy photon and electron beams.

95 The main advantages of the FeSO, dose meter can be summarized s followa s (Ref 1 ,2,3). : A hig ) h(1 degre f reproducibi1ito e y (l%).Foe applicationth l al r s considered in this paper we shall rely only upon the reprodu- cibility of the FeSO,, and not upon its accuracy. r negligible(o o N ) (2 ) variatio e "responseth f e FeSOo nth f ,o " dose meter (optical density/ unit of absorbed dose or G-value) a functio e s radiatioa th f o n n qualite rangth f higho n ei y - energy electron o d abouphotont an 0 MeV p 4 - u ts - s. e respons Th e FeSO th ) .f (3 o e dose mete r G-value(o r s independeni ) t Ï — 6 of .the dose-rate up to 2 x 10 Gy. s (4) No ( or negligible) heterogeneity is introduced by the detector s containerit (an de irradiate th n i ) d medium.A a consequences , under usual conditions, there is no (or negligible) modification of the electron flux introduced by the detector. e dosTh e ) mete(5 r solutio e irradiateb n ca n n thii d n layers w millimetersfe a ( r radiobiologicafo , or ) l experimentse th , FeSO, solution can occupy different volumes and, in particular, volumes identica o thost l e occupie e biologicath y b d l systems to be irradiated.

e disadvantageTh e FeSOth f , o sdos e mete e alsar ro well known. Thee mainlyar y : w radiosensitivitLo ) (1 ) t leasGy a 0 r 5 t (o : dose yy G f abou o s0 10 t e needear r precisfo d e measurements; (2) The FeSO, solution has to be prepared and handled very carefully and kept in perfectly clean containers.

Taking into account these general properties of FeSO,, its interes n practicai t l dosimetr f high-energo y y photon d electronan s s wil e considereb l d with respec o fout t r application: s

e calibratioTh ) (1 f ionizatioo n n chambers; e evaluatioTh e ) importancth (2 n f recombinatioo nio f o e n i n ionization chambers expose o higt d h dose-rate f electronso s ; (3) The use of FeSO, for determination of absorbed dose in radiobiological samples; f FeSOa o transfe s e a ,us e r Th dosemeter ) (4 .

1.CALIBRATIO F IONI2ATIOO N N CHAMBER R HIGH-ENERGFO S Y PHOTONS

D ELECTRON——————————————————————————————————AN Y COMPARISOB S N WITH FeSO. 4

e measurinTh g instrument commonly a locause s a dl standarn i d a radiotherapy departmen s stili t n ionizatioa l n chamber.Foo C r (or 2 MV x-rays), calibration of an ionization dose meter can be obtained r checkefroo - - standarm y b d d laboratorie n termi s f exposuro s e

96 (röntgen) or absorbed dose (gray). In France,such facilities exist at the L.M.R.I. (Laboratoire de Mesure des Rayonnements Ionisants) at Saclay (Réf.4 ). However r high-energfo , y photon d electronsan s , calibration t easilfacilitieye t yno available.Fo e ar s r these conditions, direct comparison wite FeSOth h , dosemeter provide n acceptabla s e solution for calibration of the reference chamber in a radiotherapy department.Thi s beee methoha sth n r dCente ou user man n fo i rdy years (Ref.5,6). e chambeth s s beeA ha r n calibrate, calibratioCo r fo r d fo n high-energy photons and electrons is obtained by comparing, in Co,

photon and electron beams, the readings of the chamber and of the FeSO, dosemeter.We have checked that the FeSO. dosemeter does 4 4 not introduc y heterogeneitean e assumw d an ey thas responsit t s i e independent of beam quality (Ref 2,7). This beeha s n measured recentl n veri y y careful setf o s experiments carriey COTTENb t ou d S (Ref.3 r electrofo ) n energies rangin o g14.t fro5 5 3. MeV.m A G-valu f 1.60o e 0.030 _ 1 + 4 . 5 mol -kg . Gy was found for 7 to 14.5 MeV electrons and a G-value of 1.597. 10 mol.kg . Gy for 3.5 MeV electrons.Moreover a survey e G-valueth f o s obtained from calorimetric measurement s beeha s n published by SVENSSON and BRAHME (Ref.8).This survey indicated that the difference between the G-values could be partly related to inaccuracie e determination n i s a mea d n an sG-valu f 1.60o e 0.017_ 7+ , 10 mol.kg .Gy was calculated. s alreadA y mentione e FeSOus e , w d onl r relativfo y e measurements e applicationth n i s considere n thii d s paper. FeSO n easilca . e b y calibrated by measuring its "response" (optical density, 25°C,304my) to given doses of gamma-rays.Absolute calibration of each part of the Fricke dosemeter system (spectrophometer, solution) would normally require long and difficult experiments. Calibration obtained with this method is valid even if the beam energy is not known with great accuracy. Whe n ionizatioa n n chamber dose mete s exposei r o t d high-energy electrons e absorbeth , d a watedos n i er phantom e expresseb e y formulth ma y b da (Ref.2)

Dw=M.Nc.CE (1) where : = absorbe D d poine dose(in wate th i f measuremen o tt ) a r Gy n t whee chambeth n r syste s replacei m y waterb d . = instrumen M t reading correcte r temperaturefo d , pressure and humidity.

= exposur C N e calibration e chambefactoth f o rr dosemeter for Co garama-rays.

97 C - overall conversion factor to absorbed dose in water. C„b includes: a correctio- n facto r attenuatiofo r f photone o n th n i s chambe o radiatioC r walr fo ln during exposure calibration which is assumed to be 0.985 (Ref. 9); - the ratio of mass stopping powers for water and air, which is valid for the mean energy of the primary electrons at the point of measurement; - the perturbation correction factor. C values have been recommended r differen(Reffo ) .2 t E initial electron energies and different depths in water. Similary r high-energfo , y photons n particulai d an , r for the reference radiation quality ( Co), the absorbed dose e poinath tf measuremen o t a wate n i tr phantoe expresseb y ma m d by (Ref.!)

DW = where : D , M and N have the same meaning as in Eq. (1) C. = overall coconversatioi n factor to absorbed dose in water (in Gy/R). The recommended value of C, for Co is 0.95 (Ref,1)

Measured C values for a Nuclear Enterprises chamber are lj presented in Table I and compared with the C values recommended y ICRb U (Réf.2 d derivean ) d froe calculateth m d dat f BERGEo a R and SELTZER (Réf.10 d KESSARIan ) S (Réf.11).The irradiation technique e chemica th s wela ss a l l methods have already been published (Ref.6 ,12) A clos. e agreemen e s reachei tth r fo d conditions which have been studied: electron beams from 10 to 33 MeV (incident energy) produce y threb d e different type f generatorso s . e statisticaTh l e measurementerrorth n i s s (confidence leve f 95%o l ) are indicated in the Table.A set of six Nuclear Enterprises chambers 3 of the same type (vol. = 0.6 cm , diam.=6 mm) were compared. Although the N factors for Co were different (1.01,1.04,1.05, 1.06 and 1.08), the observed C value$ as a function of electron energy were the same for all the chambers, within the limits of reproducibility of the measurements.

EVALUATIOI I E IMPORTANCTH F N RECOMBINATIOO NIO F O E N IN IONIZATION CHAMBERS EXPOSE O HIGT D H DOSE-RATES

With the higher dose-rates actually available with modern electron beam generators, ion recombination needs te be taken into account for the usual ionization chambers.The main reaso s thae i dealn on t s with pulsed radiation; moreover, when a n electron bea s "scannedi m " ovee irradiatioth r n field e ratith , o is still higher betwee e "instantaneousth n " dose-rate th r (o e dose per pulse) and the "average" dose-rate(which is measured).

98 Correction factors for ion recombination can reach several per cent n treatmeni s t conditions d evean , n more durin» calibration procedures or biological irradiat ions.(We only consider hero conditions clos o thost e e encountere lit e t n therapyi no d o d P W , consider t lie "ver y high dose-rates" which can be obtained with r accelerators)a « n i l l a i tp »c s . e dose-raten Tabli th d , I e e nl e s e date s th r p usear F o d were low, so thai corrections for ion recombination in the chamber wore smal r coulo l e eenegb t A d maximu l . . lec o mt correctio d ha X I f o n applied (Ref .-Correc) .6 n n factorrecombinatioo ti io r fo s a n i n chambee determineb n ca r d theoreticall r experinontaly.Io y a n first sot of experiments, the correction factors were determined i'rom the variation of the dose meter reading associated with a variatio e voltagth f o n e appliee chambeth o t d r (DUJ'REId an . A X COHKN L . , unpublished dat a , 1 9 7 5 ) . The results were, in a good agreement wite theoreticath h l calculations derived froe th m formula propose y BOAb d (Kef.13G• • ). T.a f seconexperimentsno t se d e readingth , a commercial f o s - ly available Nuclear Enterprises chamber were compared with the. respons e KeSOth ,f o edos e meter,sinc s assumei t i e d thae resth t - ponse, of the latter is dose-rate independent up to 2 x 10 Cy.s"' (Ref.2). These measurements were performed wite Sagittairth h e linear accelerato e Instituth f o r t Gustave-Roussy.In this accelerator 100 pulses of 3-ys duration are emitted per second, and the irradiated field is "scanned" by the. electron bcani with a frequency Kecaus. e scanninth s f o e6 og0. f system e ratith , o betweee th n average dose-rate and the instantaneous dose-rate is complex and depends on electron energy, as the size of -the primary pencil beam varies with electron energy. r resultOu e presentear s n Tabli d whicT I e h shows that correction factors derived from comparison withn i FeSO e ar , »ood agreement with those obtaine e ionisatioth y variaf b do n iio n chamber vol tage . Figure 1 compares our experimental C,. values taken fro I witmT Tablea htheoreticad an I s l curve derived f Uof.2o 7 3. . frog Fi m A systematic study of recombination has been performed more recentl s wor s i ha Th ky MARINELT. b . y ) 4 1 . d Collf an e O (R . shown for example that in a 30 MeV electron beam produced by a linear accelerator Sagittaire, the ion recombination in a Nuclear Enterprises chambea mea t a s nabou wa , rdos 77 te rate of 1.7 Gy bu-t reached 16% at a mean dose rate of '3.8 Gy.

,9,9' E FeSOTH F .O DOSEMETEE US l R DETERMINATIO——————————————————4————————-———————————————————————————Il FO R F ABSORBEO N D — DOSE l'.î BIOLOGICAL SAMPLES

e previouTh s paragraphs dealt with absorbed dose measurements at the level of the maximum of the depth/dose curve, wher e depth/dosth e e curv s relativeli e y flat ("plateau region") .Déterminâ f absorbeo n tio d dos n depti e h raises several problems.Accurate depth/dose determinations are needed for studies of RBE as a function of electron spectrum in depth in a high-energy electron beam (Ref. 12). Firs f allo t e respons,th n ionizatioa f o e n chamber (esu/Gy) varies with depth since electron energy decreases. a consequenc s A a correctioe n relate o electrot d n energy e applied.Thib o t s ha s assumes thae electroth t n energy at the point of interest in known with accuracy., e seconTh d problem concern e poin th sf measuremen o t t e ionizatioth f o n chamber.On n admica e t n thatelectroa n i , n beam e poine referreb th , o whico t tt e dos th s hi d e lies betwee e anterioth n e e chambecenterth th walf d o rr an l o thas e uncertaintth t y abou s positio it t mostta , ,is n equal to the radius of the chamber.Us ing cylindrical chambers of various diameters (Fi, irradiate2) g d perpendicularl o theit y r axiSjDUTREIX and DUTREIX (Ref.15) found that in a 20-MeV electron beae pointh mf measuremen o t t liee n fronth i s f o t e radius.Howeverth centef o a distanc 3 t a r2/ f o e , this distance may vary with the electron energy, the depth and the typ f chambeo e r (diamete f r centracavito ai d f an o yrl electrode etc.).HETTINGE . (Ref.18al t e R )e th foun f o a distancd 4 3/ f o e radiu e centen fronth i s n f electroi o rt n beams produced'ia n 35-MeV Brown Boveri betatron. Whee dos th s nrathei e r unifore "plateath n i m u region" f littlo thi s i s e importance t whe e dosbu , th n e gradiens i t high thin introducca s e considerable errors.For example, at the 30% isodose level in a 20-MeV electron beam, a change m correspond n dept1m i f o he a changth o n t si f abou o e% 10 t absorbed dose.

A FeSO, dosemeter doet presenno s t such disadvantages:

(1) It can be assumed to be insensitive to energy variation in dept r dose-rat(o h e variation) t doeI t introduc no s) (2 y heterogeneitan e o displacemenn d an y t e appliedb o factot s ;ha r

100 (3) The dosemeter solution can be used in thin layers (a few mm) n occupca r a o volumy e identica e biologica th o tha t lf o t l system o irradiateb o t s d (for example suspension f bacteriao s , yeast, etc.) in order to avoid any "geometrical" error (see Figs 3,4,5 and 6).

However, a practical problem arises when the dosemeter solution is used in thin layers, for example in Perspex cells: s importanii t o avoit t d chemical reactions wite wallth hf o s s.Therl l thee e e fore cellth e s mus e cleaneb t d very carefulld an y must be pre-irradiated at a high dose (a 1000 Gy).Ac cording r experiencetou o a ,reproducibilit f betteo ye b n r ca tha % 1 n achieved with these precautions (Ref.12).

F FeSOO A TRANSFE E S A ,US E RITH V DOSIMETER.

e mosth tf o interestin e On g application e Frickth f eo s dosemete s usea transfeit s . a s i r r dosimete r comparisonfo r s between different radiotherapy centres.The advantage f suco s h comparisons in maintaining consistency are generally recognised and it is for this type of application that IAF.A is indeed mainly interested in the FeSO,. r experiencou s a r fa e s witA h intercomparison s concernedi s , e performew n 197i d 3 (Ref.21 a compariso) e dosimeteth f o n r calibration for Co. Twenty centres ( from France, Belgium and Switzerland) too e kstudy.Eac th par o t t h centre receive 6 FeSOd , samples to irradiate at doses ranging from 70 to 150 Gy.The mean of the standard errors observed for each centre was about 0.57 which indicate e higth s h leve f reproducibio e lmethod th f o .y t li This reproducibilit t leasa s tr bette wa yo equa , to rl than, that achieved by other groups with FeSO, or with other techniques (Ref.22 , 23 ) . As already reported in detail, 2/3 of the centres were withi % fro2 e mean.Thre_ + th nm e d centrean % 5 so t diffe 3 y b r five centers differ by more than 5%.Our solution samples have not been mailed, but have been distributed taking opportunity of meeting r travelo s f somo s e membere differenth f o s t centres. a secon n I d serie f experimento s s (Ref,24), FeSOs wa . use o compart d r dosimetrou e y with Edinburgh.Furthermore,as the two centres were using FeSO,, this opportunity was taken to compare the responses of the solutions and the spec trophoto- meter (value of c) . The observed agreement was better than 1% for each compared parameter: absorbed dose, e, and G.

101 CONÇU i ON :s .

Tu conclusion, I' lie I'd SO, close1 i:>ot. or has certainly boon l.ho only available-: 1:10. Clio <1 for h i ;>, h-o. no r j;y photon ;!ii(l electron dosi- d no . i H o Un a r t foie ) c öl K1 1 y : checkinu ap s r o r o ( o ch • n li ROtr r e th n gi y s L n n o chamber; o i i ' : i ; (. ; i a . v timf . i f r a 1 o ;e0: o : : vit: c i.o. 1 uhe:n ; a r b ii l .h-ene . 'P (for .r ;» y electro d photoan n n beamsy an ) error arisHng fron an inaccurate, evaluation oC beam energy of the si>ej!:run is avoided. The same remark applies when recombinations in i o n i •/. a t ion c h a PI b e r s a re b p c o m i n f, i m p o r f. ;-i n l. . When an ?eSO, dostür.e t e r is no_t _ ava_i_labl_£ in a laboratory o a;>rew (and e that »real: s (-ari needee d with t'eSO^ o t obtai, n

reproducible moa suroT.en t s) , l.''eSO/ can be used as a "transfer" dose •noter and p r e p a r e d a n d re a d by n a t ion a l a n c! i n 1: e r n a C i o n a l I a b orator i e s . i-'injilly, in hi. gii-ener gy electron r a d i o b i o l o K y , KeSO^ is probabl e mosth y te absorben suitabli m r er . t systec e di d er t cioo e t mm si . i no s t s y s 1 a c i g o l o i b n d i oso.

S K C l-R N E K E R

) tI.CIU(1 i .h w ;s Repory , ra : Radiatiomi( a X-ray - Ç y r e n.' a .r l ni td i an s o D n Maximum Photon Energies between 0.6 ai:cl ">() Me.V, International Commission on Radiation Units and Measurements, Washington, i). (1969) .C . (2) ICKU Report 21, Radiation Dosimetry: Electrons with Initial Energies, 15c.twe.en 1 and 50 Me V , ! n te rna t i onal Commission or; Radial: ion Units and Measuromen !: s , Washington, D.O.(1972). (3) COTTMNS , F.. : Ueabsorbeo rc.l e dosis k al or inie t r i c by hoge énergie e 1 ok tronenbunde 1 a en onder i-.oek van de L j zer sul f aat dosimeter Cent 1979. (-'i ) (Hi 1 HO , J . P . , Structure de 1 ;: rr:é 11 c 1 og i.e en Franc.e, Laboratoire de Metrologie des Rayonnements Ionisants, C.K.A . -C.M . N./Sac 1ay , (1974) (r)) IMJTKF. IX, J., UKTRRIX, A., WAMBKRSIL1., A., Etalons secondaires en dos imctric , .T.Belge. Radiol./ij) (1966) 157. ) KAMBiCRSlïï(6 , DUTREIXA. , , VR1GNOÏA. , , DUTREIXM. , , Calibratio . J , n of an ionisation chamber by comparison with FeSO, for 'nigh en?rgv electron beam:; t.u i.ophS 6 ,R (19712 d. . 7 ys 16 )

102 (7) ELLIS, S.C., "The dissemination of absorbed dose standards by chemical dosimetry - mechanism and use of the Fricke dosemeter", in Proc. International Cours n Ionizino e g Radiation Metrology, Villa Monastera, Varenna, Lake Gomo, Italy 3 Sept 1972 , Oc -4 (National Physical Laboratory, Teddington, Great Britain, Rep.Radiât.Sei.30, Dec.1974). (8) SVENSSON, H., BRAHME, A.: Réévaluation of ferrous sulphate dosimetr r electrons.Internationafo y l Symposiu n Nationao m d an l International Standardization of Radiation Dosimetry.Atlanta, c 1977De 9 USA.5- . (9) SVENSSO^, H., PETTERSON, S.,Absorbed dose calibration of thimble chambers with high energy electrons at different phantom depth, Arkiv Fysi ^ (19673 k 7 37 ) (10) BERGER,M.J., SELTZER, S.M.,Quality of radiation in a water medium irradiated with high energy electro n Booi n 7 beamsk 12 . p , of Abstracts, 12th Int. Congr.Radiology, Tokyo, 1969. (11) KESSARIS, N.D., Absorbed dosd cavitan e y ionizatio r highfo n - energy electron beams, Radiât.Res. 4_3 (1970) 288. (12) WAMBERSIE , ContributioA. , à l'étudn e l'efficacitd e é biologique relative des faisceaux de photons et d'électrons de 20 MeV du betatron, J.Belge Radiol.,Monographi l (1967)n° e .

(13) BOAG, J.W., Ionization Chamber Radiatio' 4, h C , n Dosimetry (HINE, G.J., BROWNELL, G.L.,Eds) Academic Press w YorNe , k (1956) 153. (14) MARINELLO, G., DUTREIX, A., CHAPUIS, G.: Etude de l'efficacité de collection des chambres d'ionisation cylindriques irradiées dans faisceaule s e rayonnemend x t puisé d'un accélérateur linéaire,J.Radiol. Electrol. 1976, 55, 789-800. (15) DUTREIX , DUTREIXJ. , , EtudA. , e comparée d'une série d e chambres d'ionisation dans les faisceaux d'électrons de 0 MeV,Biophysi1 t e 0 2 (1966_ _3 k ) 249. (16) HARDER, D., "Energiespektron schneller Elektronen in verschiedenen Tiefen", in Symp.High-Energy Electrons, Montreux, 1964 (ZUPPINGER , PORETTI,A. , EdsG. , ) Springer Verlag, Berlin, Heidelberg w YorNe , k (1965. 26 ) (17) WAMBERSIE , DUTREIXA. , , PRIGNOTA. , : ExpériencM. , e f FeSOo n e somi ,us ee practicath n i l aspect f higho s - energy electron dosimetry n Proc.Symp.Biomédica^i l Dosimetry, Vienna, 10-14 March 1975, IAEA (1975).563. (18) HETTINGER PETTERSSON, . G , , SVENSSONC. , Dis, ,H. p lacement effect of thimble chambers exposed to a photon or electron beam fro betatrona m , Acta Radiologica 6 _1967( . 1 ) 6 ( 19) WAMBERSIE, A., DUTREIX, A., "RBE as a function of depth n higi h energy electro d photoan n n beams",Frontierf o s Radiation Therap d Oncologyan y , (VAETH, J.M. ,Ed) 2_Karger. ,S , Basel Yorw 1968Ne /( k ) 104,

103 C/ÎO) MNTIITFIJ , J. IJI.ANC, , I)., CASANOVAS , . DUTRKTX J , , WA. A, MUIRS, K I A., l'R1.0NOT,M , "N?suro . a l répartitio e d . a l dos o ed n :i ô \o öt e l n Plexigla n f , é i ln i un r r s i n s a d r u o d i : o f o r p n e c ô ; .- o p . àê par un faisceau d ' o l PC t rons monnc i né t iques de 10, 13, 20 t res S ., n y 0 , . r.io3 Mr i u(Tt.-ily) Le>d t n s V" Sy.ii l'ro o 2n d ö p. . r M r r i , 20-24 Oc.l-, 1969 o (1970- F , - F.urnlor,d )? ) " 437 i ' i ' ! . (.M) '.vAMBULiSlïî , OU'RK A. , ,j'RlOJOT A. , X T : . ResultatV , d s comparaiso l omiag a ' G L J s dosimotre e do rcenlo ed nt i s n ro . s n nioyoa o o 1'oSO . d Kiid. f. nF.lc . l J l o pouo r i , c t e l r 1973, _5£ , 835- 839. (22) AI. MOND, P . K . , I.AW, J., S Vïï.NS SON , II . : Comparisons of radiation dosiuiotry between Houston (U.S.A.), r j>u Eol hb n i(U.K. ) , P>i , . ) M? . y3 1972en l d .inec . 1 o e 5i v :, S 64-70 ( ,U17 ra oa . (23 Ol'I ) V TN Q^R, PFAT.ZNF. . R , R, P.M., KTSF.NT.OH , . MAT.Oi l R, , S.A., SAM KT.HVICI , A., NA CL , J . : The TARA program in medical radiation dos i 1=10 t ry , Aim . N.Y. Aca

104 TABLE I. Cb_ AND C,A VALUES FOR DIFFERENT ELECTRON AND PHOTON ENERGIES DETERMINED BY COMPARISON WITH FeSO,

Type of electron e Energth f o y e poinDeptth f to h C measured for a C h E generator incident electron of measurement (d) beam (E /MeV) Nuclear Enterprises recommended values (d/g.cm~2)(a) chamber

Allis-Chalmers (c) betatron 10.0 2. 0.881 + 0.008 0.895

"Sagittaire" linear accelerator 10.0 2.0 0.888 + 0.019 0.893

Brown-Boveri betatron 14.7 0.871 + 0.009 0.857 Allis-Chalmers betatron 9.0 2. 1 0.84 + 0.003 5 0.841

Brown-Boveri betatron 29.0 2. 1 0.813 + 0.005 0.810

Brown-Boveri betatron 33.0 2. 1 0.80 + 0.012 0 0.800

Type of Energy C, measured for a C-, A A (e) generator Nuclear Enterprises recommended values chamber

6°Co 1.25 MeV gamma-rays 0.95

Allis-Chalmer betatron 21 MV X-rays 0.910 + 0.008 0. 90

(a) Measurements made in Perspex. The point of measurement is assumed to be at a distance of 2/3 of the radius in front of the centre of the chamber (Ref.15). ) (b Assumin e differena constang th d an to tC G-valubeams r fo e.

(c) p = 0.05 (d) Interpolated between values given in Table 6.2 by ICRU (Ref.2). ) (e ICRU Repor3 (Ref.25)2 ° n t . TABLE II. ION RECOMBINATION IN A NUCLEAR ENTERPRISES CHAMBER (APPLIED VOLTAGE 225 V) ("al EXPOSED TO HIGH DOSE-RATES OF HIGH-ENERGY ELECTRONS^ '

Energy of the Depth of the point Recombination factors determined by : incident electron of measurement recommended Comparison with Variatiof o n bea E /MeV( m ) b o > < 2 _ chamber voltage (d/g.cm ) values FeSO,(d)

11.5 . 7 0.878 1.0+ 0.04 2 . 05

14.2 3.0 0.878 1.03 + 0.01 1 .05 o\ 31.6 3.0 0.812 1.1 + 0.03 1

) (a Sagittaire linear accelerator. Averag3 Gy.mi4. d nean dose-rate2 4, , 4 4. s for 11.5 , 14.2 and 31.6 MeV respectively.

e poinTh e f radiumeasuremeno tth e ) n f fronth i o (b s f 3 o t 2/ s assumei te b o t d e chambecenteth f o r r (Ref.15).

(c) Interpolated between values given in Table 6.2 by ICRU (Ref.2).

(d) Assuming a constant G-value for Co and electrons at the dose-rates used. Confidence interval (p=0.05) calculated from statistical fluctuatiof o n ratio f readingo se e FeSOchambeth th f d ,o san dosemeterr . 0.9S-

0.90

o 0.85

0.80-

I i . i . . . i l ... i 5 tO 15 20 2S MEAN ENERGY E Of THE ELECTRONS AT THE POINT OF MEASUREMENT (M.V)

Fig.I. Absorbed dose conversion factors C (see text, Eq.(l)) determined for a Nuclear Enterprises ionization chamber by comparison with FeSO,. The open and solid circles correspond to the data of Table I and II respectively. The mean energies E of the electrons are calculated by the Harder's formul E (1-d/= E a ) (Ref.16R e Th ). o p theoretical curv s derivei e d fro f (Réf.2)mo Fig7 3. . . From Wambersi d Coll.an e , 1975 (Réf.17).

100l

20 MeV Electrons

50

c o -*-to• N 'c o

19 0) QC

Fig . Dept2 . h ionization curve V electrosMe obtaine0 2 a n n i d beam with cylindrical chambers of the same type (groove n Perspexi d f differeno t bu ) t diameters, irradiated perpendicularly to their axis. From the extrapolation of these data to "zero diameter", the displacement factor (see text) can be obtained (Réf.15). 107 •100

110

Fig. 3. Perspex cell used for the irradiation of FeSO, or microbiological suspensions in identical geometrical conditions. The thickness o^ the cavity is 2 mm (Ref.19).

Electrons

lonization Chamber Bacteria-Yeast or Fe SO/

Fig. 4. Arrangement used for irradiation of FeSO, and biological systems in thin layers and in identical geometrical conditions. Horizontal section through the beam axis. The Perspex cells containing the "detectors" can be placed at different depths in the electron beam. Two ionization chambers are used as "monitors" (Ref.19). 108 K»- 30MeV BBC Electron Beam

• FeS04 • Liquid lonizalion chamber

UJ in O Q so

LU

IU K

DEPTH (cm Perspex )

1" J f;. J- (,'omp.i r i son of depth/dose curves measured, in ;i 30 MeV « Ice L ron beam, with PeSO, and a liquid ionization ch;iTnber, J''eSO, soliitioi irradiates i i n ' condition: d s illustraten o d e paralle Th d -'Fig an (. 3 . l platt- liquid ionization charibe s fillei r 1-pey h t de n m tanwiti r t ph (thicknesf o s the liquid : 0.9 mm). This chamber does not Introduce heterogeneity and no displacement factor has to be e assumeb appliede insensitiv b n o ca t dt i ; o energt e y variation in depth (Kef.20) . A close agreement is readied between the curves obtained with these two tech ni qui: s .

109 KM - 20 McV AC Electron Beam

• Liquid lonization chamber

o Baldwin lonization chamber

g 50

> fr<~

5 10 DEPTH ( cm Pcrspex )

. ComparisoFig6 . f depth/doso n e curves measured 20-Me. a n i ,V electron beam, wit a Nucleah r Enterprises (Baldwin) ionization chambe a liqui d an rd ionization chamber (Ref.20) e reading Th e Nuclea.th f o sr Enterprises chambe e correctear r e variatiodth s onlr it fo yf o n respons a functio s a e f electroo n n energ n depti y h (see text) o correctioN . s appliee i liquin th o t dd ionization chamber readings (Fig.5) e discrepancTh . y observe ) correspondd mm o betweecurve 2 tw - e ( sth n s to the displacement factor of the Nuclear Enterprises chamber (2/3 of the radius) (Ref.15).

110 POSTAL DOSE INTERCOMPARISO HIGR NFO H ENERGY X-RAYS AND ELECTRONS WITH TLD

B.-I. RUDÉN Division of Life Sciences, International Atomic Energy Agency, Vienna P.J. BIGGS, A.L. BOYER Department of Radiation Medicine, Massachusetts General Hospital, Boston, Massachusetts, United State f Americso a K.A. JOHANSSON Radiation Physics Department, Sahlgren Hospital, Universit f Göteboryo g Göteborg, Sweden K.R. KÄSE, B.E. BJÄRNGARD Joint Cente Radiatior fo r n Therapy, Harvard Medical School, Boston, Massachusetts. United States of America

ABSTRACT

This study concerns the accuracy and precision of the IAEA/WHO LiP TLB system use intercoraparison di maiy n b absorbe f lo d doses 7-radiationo froC m , 4-25 MV X-rays, and 4-20 MeV electrons. The system employs 160 mg LiP powder in polystyrene capsules, which are placed at 5 or 7 cm depth in water for Co 7-radiatio d depthigm c n an wate hn 2 i h 1 energo rt 0 y1 X-rayt a d san for 4-2 electronV 0Me irradiated san doseo (2.0d t d ra 0 s 0 closGy)20 o .t e The dosimeters are mailed to the IAEA Dosimetry Laboratory and read out under condition minimizo st e variation instrumenn si t sensitivity precisioe .Th f no the readout technique, using 3 capsules per irradiation and the readout of 5 ali- quot capsuler epe characterizes ,i 0.2y db $ standard deviatio resultine th f no g mean* Since random errors during the irradiation are added, the detectable systematic discrepanc dosn yi e $ confidencdelivery95 e th t ,a e levels ,i higr fo h $ energ3 12-2r ± electronsfo V , y 0 $ Me Co X-rays 3 + r d fo .,an $ 2 ±

For electrons of 7-11 MeV energy, the detectable difference is estimated, on less solid grounds However» aboue b 5$ o i t,t lattee ,th r expectefigure b y ema d reducee tenerge ob th f ydi dependenc thin ei s determine e rangb n eca d with

111 highe rlower o accuracy V r Me energy 4 t .A , considerable difficultiee b n sca

expecte energo t e yddu dependenc randod ean m errorsP response Li .Th e th f eo dosimeter to X-rays and electrons, compared with that for Co 7-radiation,

was determined to decrease from 1.00 for 4 MVX-rays to 0.98 for 25 MV X-rays an0.9o dt 12-2r 6 fo electronsV 0Me .

INTRODUCTION

The IAEA/WHO has, for several years, conducted a postal dose intercomparison service for Co 7-radiation with thermoluminescence dosimeters (TLD).' The purpose of this activity has been to intercompare the absorbed doses given with Co radiotherapy machines at different institutions and, by informing the participants of their results, to improve the accuracy of the clinical delivery of the radiation dose. The participants have been asked to irradiate polystyrene capsules containing 160 mg LiP powder to a known absorbed dos watern i e dosimetere .Th s have then been sen Vienno t a through WHO channels, and read out at the IAEA dosimetry laboratory, which, based on its own calibration, has assigned a certain "measured dose" to the

dosimeter. This measured dose is then compared with the "stated dose", i.e.

th capsule dosth o et e estimate participante th y db statee .Th d accuracy thir fo s intercomparison servic $ confidenc95 bettes e ei th rt a e tha% 5 n- level.

This TLD intercomparison service has been extended to orthovoltage dosimetry.

In this energy range, the energy dependence of the LiP dosimeters introduces an additional complication but pilot studies have shown that intercomparisons can be performed with an accuracy of better than - 10%,

The purposstude th yf e o reporte d her bees eha evaluato n t feasibilite eth f yo applying the same technique for high energy X-rays in the energy range 4-25 WV and for high energy electrons in the energy range 4—20 MeV. The usefulness of such dosimetry intercomparisons is determined by the accuracy that can be achieved, i.e confidence .th e with whic hdiscrepanca y between "measured dose" and "stated attribute e doseb n "ca systematia o dt c differenc calibration ei f no machine outpu dosd tan e delivery betwee participatine nth g institutions. Errors

that tend to interfere with the detection of such differences originate partly

in the short- and long-term variations in the TLD instrument sensitivity,

including variations in the amount of LiP powder used for each measurement.

112 These minimizee errorb n sca carefully db y selected procedure completelt no t sbu y eliminated. In addition, the calibration methods used by the IAEA Dosimetry Laboratory mus considerede tb . Finally irradiatioe ,th dosimetere th f no s participatine ath t g institutio subjecs ni randoo t m error machinn si e function, instrumentation used for calibration, and positioning of the dosimeters. The present study aims towards assessin magnitudee gth thesf so e effects. When comparing different radiation qualities, such as X-rays and electrons of various energies, the posibility of an energy dependent response of the TLD cannot be excluded. An effort has been made to extract this information from the data collected in the experiments reported here.

METHODS 1. TLD Techniques

The dosimeters consisted of polystyrene capsules of 5 mm external diameter, powdeF Li containinf ro (TLD-700g m 0 g16 , Harshaw Chemical e Co.)th l .Al LiF powder, used in any one of the experiments, was from the same virgin batch of powder, annealed at 400°C for 1 hour and at 80°C for 24 hours before distribution. When returne IAEe th A o Dosiraetrdt y Laboratory after irradiation, the powder did not receive additional annealing since at least four weeks lay between irradiation and readout, and the signal related to unstable traps in the LiF had therefore been eliminated.

The powder in each capsule was divided into 5 aliquots, using a vibrating dispenser. The aliquots were read out in a Harshaw 2000A and B ÏILD readout instrument. The readouts of the experimentally irradiated dosimeters were interspersed with readout referenca f so e powder,7 irradiateo C a n i d beam as a large batch at one time under conditions to ensure uniformity. Five aliquots of the reference powder were read out each time. The average signal from the two bracketing readouts of the reference powder was used as relativa e measurinstrumene th f eo t sensitivity, applicabl capsulee th r efo s that were read out in between.

Experimenta. 2 l Irradiations

The institutions participatin thin gi s study have bee Joine nth t Center for Radiation Therapy (JCRT) and Massachusetts General Hospital (MGH), both of Boston, Massachusetts, USA, and Sahlgren Hospital (SH), Go'teborg, Sweden.

113 In each experiment participante ,th s irradiated three capsules each with

C -radiatioo7 n with various X-ray energ e beamth n yi s rang ewitd 4-2an hV 5M

various electron energ e beamth n ysi range 4-20 MeV capsulee .Th s were irradiated timea t a , same e "buth on et setu putpud pan t calibratioe n on wer y ean user dfo radiation quality. During the irradiations, the plastic capsules with the LiF o C werdeptm c r X-rayV e5 M h fo place 5 d 2 deptm san c water n 7 i dhfo t ra

and the other high energy X-ray beamst For electrons, the capsules were placed in water at 1 cm depth for 4 and 7 MeV and 2 cm depth for other energies. A plastic rod was used to hold the dosimeters in position, as shown in Figure 1. 60 This arrangemen IAEA/WHe same th uses th ea postao n s C di ti O l dose inter- 2 comparison service.

3. Determination of Absorbed Dose

The output froradiatioe mth n unit always swa s calibrate measurementy db s with ionization chamber time irradiationf th eo t sa measuree .Th d ionization

was converte absorbeo dt E factordC dosd an Table( s ^ usinC ee IV)gth . Com- parisons betwee werH n MG eJCR d madTan e durin experimentse gth . Some further detailcalibratioe th f so n procedure institutionse useth y db givee sar n below.

JCRT irradiated with 8 MV X-rays, 4 and 7 MeV electrons from a Siemens Mevatron 12 linear accerlerator and with 4 MV X-rays from a Varian Clinac 60 4 linear accelerator, in addition to the irradiation with Co. The calibration 60 tpchnique for Co was somewhat different in different experiments: the institution measured the dose rate in air with a 0.5 cm Exradin A-1 ionization chamber, in polystyrene with the same chamber, or in water with a 0.35 cm PTW 30-312 chamber. Both chambers have air-equivalent plasticV M walls4 r .Fo

and 8 MV X-rays, the calibrations were made either in polystyrene with the

Exradin ionization chamber, or in water with the PTW instruments or with a

Capintec model P0.6 chamber e electro.Th n calibrations were mad waten ei r with the PTW instruments. The ionization chambers used were either calibrated by

National Bureau of Standards (NBS) and controlled by constancy checks, or calibrated against suc n instrumen ha experimente timth e th f l e o t al a t n .I

cases, either a Keithley 610C or 6l6 electrometer was used. electronV Me 8 1 n d si an 5 1 irradiateH MG , X-rayV 12 M 5 d 2 s an d d witan 0 h1

addition to Co. The X-ray beams were provided by Varian Clinac 18 and

114 Clinac 35 linear accelerators respectively, and the electron beams were provided

by Varian Clinac 18. The MGH used a 0.6 cm Farmer ionization chamber (Nuclear

Enterprises 2505/3) wit graphita h e thimbl Keithlea d ean 6 electromete y61 r

calibrationso forth . This chambe7 o beed C rha n r calibratefo S NB y db radiation. The initial determination of the output from the MGH Co unit was

based on a series of five measurements over a six week period. The first three

calibrations were in air, the remaining two in water. Measurements of the output

wero iC n D eirradiationwate TL madr e rfo e th time agaif th o e d t na san compared wit calculatee hth d decay. Agreemen s alwaytwa s bettee r Th tha. 1% n

measurement X-rayr fo s d electronsan s were mad watern i e .

participateH S onl n di experimento ytw s compared e wit th five hth f eo 60 othe institutionso rtw addition .I irradiationo nt beamo C s wit ,e hth dosimeters were exposed to 5 MV X-rays from an A.KI linear accelerator and 8 MV and 16 MV X-rays and 10, 14, 17 and 20 MeV electrons from a Philips SL 75/20 linear accelerator. The SH reference instrument was a Farmer (Nuclear Enterprises 2505/3) ionization chamber, calibrate Nationae th t da l

Institut Radiatior efo n Protectio Stockholmn ni l'herado. .A electromete2 M sR r

was used. All calibrations were made in water.

IAEA Dosimetry Laboratory irradiate fifteef o t se n da capsule e th r sfo purpos calibratinf eo sensitivite systemD gth TL e absorbee .th Th f yo d doses selecte rangde werth 175-22f eo n ei d (1.75-2.25ra 5 Gy). These irradiations were performed wit Pickeha teletherapo C r y unit, withie weeth e nf on ko expérimental irradiations SecondarL NP n .A y Standard Level X-ray Exposure

Metor, Tyne 2560, and an NPL Secondary Standard Chamber, Type 2561, with a calibration factor obtained from tho National Physics Laboratory (NPL), United Kingdom, were used for the output calibration. Some additional details

calibratioe ofth n have been nublished elsewhere. These calibration capsules were read out under the same conditions and at tho same time as the experimentally irradiated capsules. The calibration factor was determined using a least square, resultine th o lineat signalD t gTL r fi s (normalize readinge th y db s from reference

nowder absorbe. )vs d dos watern i e .

RESULTS

eacr Fo h capsule aliquot,5 s wer corrected ean reat instrumenr dou fo d t sensitivity using the reference powder in the manner described above.

115 followinge Ith n resultine ,th g value callee sar d y.. wher,, e inde denotexi s IJK

the sequential number of the aliquot for each capsule (i = ït 2t 3. 4t 5)» sequentiae indeth j x , 3) l capsul, e numbeexperimene 2 th th , 1 f n o ri e= j ( t

an k identified experimene th s t (energy, institution, date) e standarTh . d

deviatio sample th f fivo n eacf ei t no se readouth r capsulpe s s calcuewa -

lated as

) (1 'jk'

where y., is the mean of the five readings for the capsule jk. The mean

value of the readings for the three capsules in each experiment was then

calculated: I 3 - -L 5 3 k j-1 —* 1 3 *^ -^L — i i ji= 1 i J ^

e meaTh n standard deviatio e thre e samplth th er f capsulefo eo n n eaci s h

experiment was also calculated as 1 3 s § = ) (3 k j 1 = J 3 k

e thre th range er th wels a capsulefo es la s

) (4 k j y n mi - k j y x ma = k r

Tables I and II list the values of r, /y. for the various experiments and K K. the average relative standard deviation s, /y, , both expressed as percentages.

The measured values x.., for the ROCo irradiated calibration dosimeters,

corrected usin e referencth g e powde s describeda r , wer e followe th use n i d-

ing way. The mean value for each capsule was calculated, x., . The dose J K- to which the capsule wa's irradiated is called c., . A linear fit v ( bk+ cjk ka a V was determined, using a least square program, with the data set -{x., , c ./I. *• JK JKf r eacFo h grou experimentf po s pertainin particulaa o gt r dat Tablen I ei I , sI

differente b y ma parametere , th b . d I an II , d sa an

The mean values y, for each experiment were converted to "measured dose" d, , .C K K frorelatioe mth n *k = «k+ Vk (6) Strictly, d, is the absorbed dose in the Co 7 beam, calibrated by the

IAEA, which would be expected to give the average value y, . The "measured

dose1* d, was finally divided by the "stated dose" IX, i.e. that dose to

whic participane hth t institution claime havo dt e irradiate capsulese dth .

116 This gives the ratio

varioue th includI r I s Tablefo d value e experiments^ an R eth sI f so .

three eacr th eFo f h o participatin g institutions average ,th thesf eo e X-rae th yd beaman o C ratiocalculates wa employed e , sR th r dfo . These

institutiono tw value presentee e ar th sR r Fo Tabln s di . thaeIV t performed 5 separate experiments for each radiation quality used, the Standard deviation thesf o samplee5 alss swa o calculated, usin same gth e kin formulf d. (l)o eq ,s aa The resulting values can be seen in Table IV. This calculation was not per- formed for SH, since this participant took part in only 2 experiments . (and for the experiments with electrons for the same reason)

DISCUSSION

1. Precision of the readings The sources of variations that manifest themselves in the ObLtmatud standard deviatio e primarilar , ns. y difference exace th tn i samoun f o t J K F aliquotpowdee Li th n ri s dispense five th e r readingfo d eacr fo sh cap- i sul d short-terean m fluctuation sensitivite th n readoue i s th - f o yin t

strument.

s 0.7-7% i , value n /y I I I , Table. n s i d s e an th I se averag l Th al f eo

the absence of any capsule-to-capsule effects (see below), this is the

best estimate from the measured data of the relative standard deviation

when reading aliquots taken from capsules which have been irradiated

identically. The values s, and s,, closely follow normal distributions.

Thus standare ,th d deviatiofive th meae e f th readingno f no r eacsfo h

capsule would be expected to be 0.77//F = 0.34%.

. 2 Precisio capsule th f no e values

If all three capsules in each experiment were identical in all respects,

including irradiation and readout, the only source of variation among the

mean values of five readouts per capsule would be the short-term variations

discussed above. Thus relative ,th e , amonrang mean/y e , r th gethret fo s e

capsules would be expected to be /3~ times the standard deviation of the same

mean5 or 0.34/5 = 0.59%. The average relative range for the n = 12 "values

117 for 60Co y beams in Table I is 0.64% and Lhe corresponding figure for the

X-ray irradiations is 0.63% (n = 26). From this, it is concluded that the

capsules were irradiate a reproducibl n i d e manner with X-ray s wela ss a l

o y. Sources of error that could have affected the ranges r, among cap- K suies but not the spread of readings for individual capsules are variations

n actuai l exposur acceleratoe eth timinn i r o g r monitor. Positioning vari- ations could, also have contributed.

Sinc suco en h errors appea introducee b o rt d when irradiatine gth three capsule eacn si h experiment standare ,th d deviatio meae r th nfo f no the three capsules is the same as for fifteen aliquots, i.e. 0.77 //15 = 0.34/T3 = 0.2/0

3. Precision of the experiments

Tabl showV eI resultine sth g average ratioeacr fo h s R participan d tan radiatio JCR d X-raysr nan T fo quality H casMG e ,f th eo thi n .baseI s si n do

five experiments and for electrons on two experiments; in the case of SH, on two experiments for X-rays and electrons. The results from the individual standare quantite Th th experiment. s a , d yR I II listed e an sar Tablen I i dI , sI deviations of these ratios R, have been calculated, using a formula analogous to eq. (l), for the five values per radiation quality for the two Boston

hospitals valuee .Th thir sfo s standard deviatio somewhae nar t higher rfo the X—ray experiment meae th n , valueCo s tha sr beinnfo g 1.6 X-rayr $fo s

an. dCo 1.0 r $fo

In the following, it will be assumed that the difference between these

X-rayd an variatio significants o si C r nfo . Thi plausibles si , since ther additionae ear l source errof so r that limi reproducibilite tth r yfo irradiations with X-rays compared with Co. standare th , Co d deviatios determiner wa Fo . R 1.0$e b f no o t d. Of this, it has been previously shown that the standard deviation of the three th mea er capsulenfo s use 0.2$s di . Thi causes swa d primarily yb

variations in the readout process, including the aliquots dispensed. These errors also pertai calibratioe th o nt n dosimeters irradiatey b read t dan dou IAEA.. Since 15 capsules (75 aliquots) were used for this purpose, the stan- dard deviatio estimatee b qualite n th ca f 0.77/fT5s n, o da y b ~0.2/{5~($)= n .I

118 addition, ther c variationar e e geometricath n i s l setu d timinan p f tlio g e

exposure. Tlio.-- e e IAE intoccus y Laboratorth oDo ACr t a r e th y t (T,a d )an

partUtpatlng Institution (i2). This gives the relation

2 2 2 2 ) (8 2 T l.O0.2= + + (0.2//-, + 5)

Tt is reasonable to assume that T, = T,, which means that eq. (8) can

solvee b 0.7%= 2 T d .= wit ! T h e X-rath yr irradiationsFo e IAKth ,A calibration proceduree th e ar s

same and the TJ = 0.7% determined remains valid. However, TZ is no longer . s Thuschange ha e totaT e sam t th ,o th t bu edl standard deviatio f Ri_(lo n . 2 X K e divideb n s ca a d

1.62 = 0.22 + (0.2//5 )? + 0.72 + T (9) 2 X

e randoth d m an errors e participancauseth y b d e thuar t s estimatee b o t d

= 1.47.T . 2X

ft. Comparison among institutions

Accordin a t-test o t g , neithe moae f th rtheo n ; results froe twelvth m e

60Co experiments nor the mean of the 60Co results from any ono of the three

institutions is significantly different from unity. Thus, it can be assumed

that any systematic differences in tho 6nCo calibration among the four par-

ticipants arc negligible compared with the random errors. Thcso random

errors are suiniari x.ofi by e<[. (8) nnd a

dard déviation, as discussed above.

Figure 2 shows the values K^ (measured dose/staled dose) for the X-ray

experiments as a function of the X-rny energy. Tt should be noted.that the

measured dos s thai e t dos 60f o eC o photon-; that would givsame th ee TI,D read-

ing as was actually measured. Tho d.ita in the figure indicate a slight de-

crease of this ratio R, with increasing energy. The solid line in Figure 2 is a least square fit to the measured data and indicates that the ratio Thes. MV drope5 R value2 abouy o sinfluenceb e t fro$ sar V 2 t m4M y db the factor Guthat the participants have chosen in the calculations of "stated dose". Thes value^ eC indicatee sar Tabln i dWhil. valueeIV e eth s e consistenar t amon participantse gth , ther uncertaintiee ear e th n si C values.

119 Assumin valueg^ C thacorrecte e sar tth interprete,e b Figur y ma e2 d as indicative of a slight decrease of the TL response of the LiF dosimeter used with increasing X-ray energy in this range. The energy dependence of dosimetethiL T sF typLi higr f rfo eo h energy X-ray bees sha n studie othersy db .

Almond and McCray observed a lower response (0.93) for X-ray energies around f"f\ n compareV M 0 2 d whil, witCo he thaMansfielr tfo Suntharalingad dan foun, m d

less tha variatio$ n1 response th f no rangX-raye o et th en si 4-4 . 5MV

Electron irradiations

The energy of the electrons at the phantom surface was determined using

the extrapolated range from depth ionization curves in water.

The electron irradiation JCRTy sb , March 1979i were performe tima t dea when the monitor chamber of the accelerator malfunctioned. An ionization chamber was inserted in the water next to the TLD capsule. At 4 MeV, the spread of the 5 readings per capsule is very much higher than for other irradiations, which is interpreted as evidence of some disturbance by the ion chamber. The resulting value of measured/stated dose has been rejected from the calculations.

Figure 3 shows the resulting quotients of measured to stated dose as a function of electron energy. From and including 12MeV, the data have a mean of 0„96 with a standard deviation of 1.0^. Thus, in this energy range the performance of the

intercomparison system is similar to that for X-rays and Co. However, the data

were considered somewha uncertaino tto , statisticall includee b o yt Tabln di . eIV Belo MeV 2 dat w1 e scatterede ,th a ar reasone diagnoset .Th no thir e sfo sar t da this time reflectt ,bu , accordin precedine th o gt g discussio precisionf no , some real difference irradiatioe th n dosimeterssi e th f no . Further experimentatios i n needed before the energy dependence below 12 MeV is ascertained with an accuracy comparable to that at higher energies. That the detectable systematic difference

does not exceed - 5/£ is made plausible by the data, presented in Figure 2. This 9,10 is still small enough to allow clinically meaningful intercomparisons to be done.

CONCÖJSIONS

The IAEA/WHO TLD postal dose intercomparison system has been tested in this study wit s .measuremenl A hal t procedures subjecs i t ,i systematio t d randocan m errors factn .I ver e ,th y purpos intercomparisoe th f eo deteco t s ni t systematic participante th parerrore f th to n so .

120 For Co, the precision in one experiment, consisting of the1 irradiation thref o e capsules expressee b n relativ,a ca s da e standard deviatio% 1 f no (Table 17). This implies that a value outside 0.98-1.02 with 95$ probability reflects a systematic difference in absorbed dose determination between the IAEA and the participant. This takes into account a certain random error by the participant techniquD TL e .Th e itsel somewhas fi t more precise diss wa -s ,a cussed in connection with eq. (8). The result that 2$ is a significant discrepany at the 95$ confidence level, should be compared with previous state- ment sneedes i tha $ reaco 5 tdt h this leve confidencef lo .

Por high energy X-rays, the random errors introduced by the participating institution somewhae seeb o mt (9). s showeq twa « y highes nb a o C r thar nfo To detect a systematic difference in absorbed dose determination between the participane $ confidencth 95 IAE d e an Ath t ta e level requires thadiscrepance th t y exceed ' Thi s3$ supportes si face th t y dthab standare tth d deviatioe th f no measured values, divided by the corresponding values on the curve in Figure 2, is 1.4$ statemene «Th significana ts i tha $ 3 t t discrepancy presupposes thae th t

IAEA conversioreadinD TL e absorbeo th gt f no d dos waten ei e bases th ri n do curve in Figure 2, and that there is no significant systematic error in this curve. Furthermore, the statement that a 3$ discrepancy implies a 95$ probability that a systematic difference exists, is of course not valid if the participant introduces greater random errors in the irradiation of the dosimeters than was the case in the experiments reported here.

indicatioo Thern s ewa thin ni s studsystematia f yo c differenc absorben ei d dose determination betwee Swedenn i hospitale e nth on . e WhilBoston th si d enan H compareMG JCR d dosimetre Tan dth y procedure experimentse th pars sa f to , they previouslt hadno y intercompared dosimetry wit. hSH For electrons of 12-20 MeV energy, no energy dependence seems to be present.

The precisio similas ni thao X-raysr rt fo t - .un MeV2 1 Betweee d th , an n7 certaint energe th n yyi dependence remains considerable detectioa t ,bu n limit of ± 5$ is consistent with the experimental results. Below 7 MeV sufficient availablt no dat e aar therd ephysicaan e ear l reason expeco st t great difficulties in performing meaningful intercomparisons at these low electron energies.

121 ACKNOWLEDGMENT

authore Th s wis' expreso it s their gratitud . H.HDr .o et Eisenlohr rfo

his suppor never-failind an t . GirzikowskyR g. Mr interes o t performeo d ,wh an t d

the measurement D dosimetersTL e th f so . This investigatio bees nha n possible thanks to the support through the IAEA Research Contract Programme.

REFERENCES

Tl.l H.H. Eisenlohr, J.G. Haider B.-Id ,an . Rüde Proceedingn ni e th f so Fifth International Conferenc Luminescencn eo e Dosimetry (Justus Liebig University, Giessen 1977) P. 350.

f2.1 H.H. Eisenlohr and S. Jayaraman, Phys. Med. Biol. _22_, 18 (1977).

B.E] f3. . Bjärngar B.—Id dan . Rüden Intercomparison ,i n Proceduree th n si

Dosimetry of Photon Radiation, Technical Reports Series No. 182 (inter- national Atomic Energy Agency, Vienna 1978) p. 155.

F4.1 B.E. BjSrngard, 'B.-I. Rüden, H.H. Eisenlohr, R. Girzikowsky, and J. Haider, in Proceedings of Symposium on National and International Standardization of Radiation Dosimetry, (international Atomic Energy Agency, Vienna 1978),

Vol. I, p. 319.

P5.1 R.D.Evans Atomie ,Th c Nucleus (McGraw-4îill Boo19.55), kGo , p.901.

F6.1 A.E. Nahu J.R.Greeningd man , Phys. Med .(1978)4 89 Biol , ..2£

T7.1 P.R.Almon K.McCrayd dan , Phys. Med .(1970)5 Biol33 , ..15

[8.1 C.M. Mansfield and N. Suntharalingam, in Proceedings of Symposium on

Biomédical Dosimetry (international Atomic Energy Agency, Vienna,1975 335» )P .

[9»1 L.H. Lanzl, Why Is A High Accuracy Weeded in Dosimetry, Technical Reports Series No. 182, International Atomic Energy Agency, Vienna 1978.

riO.~|The Report FROM THIS AGM p. 7-

122 TABLE I

e resultTh f !:ho s e oxperirenty s o witC " h

e ratiRfcth ,f o r:'lc e rangth >f o e si^/v], e averagth , e üiejsured close i-.o averse reading relative S.D5 r .fo In:;t: ifuEion_____Dace______state capsulas3 r To ,d_ .'<____reading__ dose r capsule,spo %

JC:ÎT June 1978 1.022 1. 6 0. 86 Oct. 1978 1.016 0. 4 0. 68 Nov. 1978 1.003 0. 6 0. 73 Feb. 1979 0 .998 0. 8 0. 72 May 1979 0 .997 0. 2 0. 65

MCI! June 1978 0.999 0. 3 0. 90 Oct. 1978 1.007 0. A 0. 77 Mov. 1973 1.018 0. 2 0. 68 Ma veil 1979 0 .99:5 2. 3 0. 48 Mny 1979 0 .991 0. 2 0. l; 8

S H Marc ii 1979 1.001 0. 6 0. 63 May 1979 t .006 0. 1 0. 70

123 TABLI I E

The results of the experiments with X-rays

r Rk, the ratio of k/yk range ,th f eo sk/ye k,th average measured doso t e average reading relativ. S e D. for 5 Energy Institution Date stated dose fo capsules3 r ,% readings per capsule, % V M 4 JCRT June 1978 0.975 0.2 0.88 Oct. 1978 0.996 0.5 0.70 Nov. 1978 1.000 0.6 0.68 Feb. 1979 1.003 1.4 0.73 May 1979 0.999 0.0 0.49

5 MV SH March 1979 0.995 0.9 1.16 May 1979 0.991 0.5 0.83

8 MV JCRT June 1978 0.978 0.4 1.50 Oct. 1978 0.988 1.6 0.81 Nov. 1978 0.998 0.3 0.73 Feb. 1979 1.000 1.5 0.81 May 1979 1.036 0.2 0.85

H S V M 8 March 1979 0.987 0.1 0.79 May 1979 0.990 0.5 0.85

10 MV MCH June 1978 0.998 1.3 0.74 Oct. 1978 1.001 0.8 0.71 Nov. 1978 1.005 0.4 0.99 March 1979 0.982 0.3 1.01 May 1979 0.978 0.1 0.43

H S V 1M 6 March 1979 0.975 0.8 1.02 May 1979 0.978 0.1 0.72

H MG V M 5 2 June 1978 0.969 1.8 0.54 Oct. 1978 0.978 1.2 0.66 Nov. 1978 1.013 0.6 0.65 March 1979 0.983 0. 1 0.74 TABLE III The results of the experiments with electrons

R, , the ratio of r the range of s /y , the average relative S.D. Energy Institution Date , , , kAc' measured doso et avarage reading for fo readingr5 capsuler spe ,% stated dose 3 capsules,%

4 MeV JCRT March 1979 (1.008) (2.4) (5.0) May 1979 1.396 2.3 1.33 7 MeV JCRT March 1979 1.029 2.6 1.28 May 1979 1.014 0.4 0.65 V Me 0 1 SH March 1979 0.937 0.4 0.93 May 1979 0.972 0.1 0.55 11 MeV JCRT March 1979 1.049 0.5 1.17 May 1979 1.009 0.8 0.69 12 MeV MGH March 1979 0.956 0.3 0.82 May 1979 0.944 1.2 0.76 14 MeV SH March 1979 0.955 0.7 1.06 May 1979 0.952 0.1 0.66 15 MeV MGH March 1979 0.960 0.2 1.00 May 1979 0.960 0.5 0.42' 17 MeV SH March 1979 0.950 0.4 1.10 May 1979 0.956 0.1 0.66 18 MeV MGH March 1979 0.979 0.2 0.60 May 1979 0.952 0.2 0.57 20 MeV SH March 1979 0.968 1.2 0.75 May 1979 0.958 0.2 0.83 TABLV EI

Summar e resultth f yo s

R, the average ratio of Estimated relative Radiation Institution measure o statedt d dose standard deviatio% , , R f no CA

60_ Co 7 rays 1 JCR1. T 1.007 0.95 MGH 1.002 1.0 0.95 — SH— 1.004 0.95 4 MV X-rays 1 JCR1. T 0.995 0.94 5 MV X-rays SH 0.993 —— 0.94 8 MV X-rays 1 JCR2. T 1.000 0.93 — SH— 0.988 0.93 10 MV X-rays MGH 0.991 1.2 to 0.93 o\ 16 MV X-rays SH 0.977 — 0.92 25 MV X-rays MGH 0.985 1.8 0.90

CE 7 MeV electrons JCRT 1.022 * — 0.89 10 MeV electrons SH— 0.954 0.885 11 MeV electrons JCR— T 1.029 0.88 12 MeV electrons MGH 0.950 — 0.874 4 Me1 V electrons — SH— 0.954 0.86 Me5 1 V electrons MGH 0.960 —— 0.859 7 Me1 V electrons SH— 0.953 0.85 18 MeV electrons MG— H 0.965 0.848 20 MeV electrons SH— 0.963 0.84 0 W* il ^ 8 B Dept m h5c Lwoter Surfac^ e > '/ (7cm,25MV | I ) —I —

c fj

^ 1 ~ -— Plastic Rod ^ :m CT > r o 1 —————m c 4 1 S ^^^^^^^^^^ : - * — —— ^

/ y

r ^

^^ J 1 . „__^ Î

Figure 1

The setup used for Co, X-ray and electron irradiations of the capsule

containing LiF polystyrene Th . e capsul m5 m s i ediamete m0 3 m x rlon g with

m1 m wall thickness t I LiPcontain .plastig e m Th .0 supportind cro 16 s e gth

capsule is 1 cm diameter with 1 mm wall whickness. It extends to the surface of

th capsule th wate d s insertei ean r d int holoa appropriate th throug t a t i h e depth.

These depths were: Co 7-rays and X-rays up to 20 MV,5 cm; 25 MV X-rays 7cm;

Me7 Vo 4t electrons ; 12-2cm 01 , MeV electrons. cm 2 ,

127 0 2 5 1 10 25

Figure 2 X-RAY ENERGY (MVl

60, The results of the experiments, showing R, , the measured Co equivalent dose divided by the stated dose, as a function of X-ray energy. The measured dose

threaverage e ith sth er capsulesefo , irradiate eacy db h participane on y an n i t experiment. The data points show the results from the different experiments:

triangles = JCRT, diamonds = MGH, circles = SH. The line is a least square linear

fit to the data points.

î A 1.396

\

\ A\ \ discarded A \ A \ \ \

\ 0 u O .A. 0.950 - * 8 " 0 * 0940 \^ i 1 1 » 0 357 10 11 12 It 15 17 20 Figure 3 Electron energy (MeV)

60 result e experimentse Th th f so , showinmeasuree y equivalenth o r , g-C R d t dose dividestatee th y ddb dose functioa s ,a electrof no n energy measuree Th » d

dose is the average for the three capsules, irradiated by each participant in experimente on y an date .Th a points shoresulte wth s frodifferene mth t experiments: triangles = JCRT, diamonds = MGH, circles = SH. 128 ABSORBED DOSE DETERMINATION WITH IONIZATION CHAMBERS IN PHOTON AND ELECTRON BEAMS

K.A. JOHANSSON. L.O. MATTSSON Radiation Physics Department, University of Göteborg, Göteborg, Sweden

The International Commission on Radiation Units and Measurements (ICKU) has published general recommendations on dosimetry procedures for photon (1CIUJ r electro1969fo d )an n beams (ICRU 1972). These have been supplemented by national or regional suggestions covering practi- cal details of routine dosimetry procedures. In the Nordic countries such regional recommendations were publishe n 197i d 2 (NACP 1972). These beehavw nno e revised (NACP 1980). There were several reason r thifo ss revision. Sinc e firsth e t protocol several papers have been published giv- ing new data on various effects of importance for the corrections used with ionisation chamber dosimetry. The Si-units for the radiological quantities should be applied. The former Nordic recommendations were mainly based on investigations with betatrons, while withi e Nordicth n : countrie- se w no s veral other kind f acceleratoro s c usear s d with usually different properties, which had to be considered. e recommendationth f o m ai giv o e L eTh s i hospitas l physicist a s"cod f o e practice" to be followed at all radiation therapy centres in the Nordic coun- securo t s triea e o s uniformit f dosimetro y y procedures weightinn I . g high accurac theoreticad an y l strictness against practical usefulness, -the latter s givewa n more emphasi o thae procedures s th t e performeb y ma s d easily.

General concept dosimetrn o s y

6

In order to measure the absorbed dose, D , given to matter of à medium, m, at a point of interest, P, a small piece of the medium centered at this- poin s replacei t e detecto probee th th y db r o r. Generall probe th y e consists e radiatiooth f n sensitive mann i material d y an case , i , s a alswall f o , container r coveo , r surroundin e sensitivth g e material e dimensionTh . f o s the probe shall be chosen small enough to give the required spatial resolu- e measurementh tio f no o reducet d s mucan a t , s possibla h e under given requirement f probo s e sensitivity y influenc e an particl, th n o e e fluenct a e wheP probe th n s insertedi e . This general descriptio probe th f eo n applies

129 l kindtoal f dosimeteo s r systems, e.g., ealorimetric dosimeter ionid an s - zation chamber s wela s s chemicala l , photographic, theriuolurninoscend an t radiophotoluminescent dosimeters.

The performance of the probe method consists of two principal steps, namely: 1) The determination of the mean absorbed dose to the probe material, D from the dosimeter reading, using either the appropriate calibra- tion facto r performino r n absoluta g e measuremen f 1).o t .

2) The determination of the absorbed dose to the medium, I) , at the ID e absenc th e detector th n i poinf a calculatio o e , y P tb , n e baseth n o d knowledg. D f o e

In the case of an ionisation chamber the absorbed dose to the medium, e e calculateb b n n ca ca , , Dd froe e meamth th a n absorbe de detector dosth n i e, D. , m i e well-knowbth y n Bragg-Gray relation.

) (1 . ) (? T ! D m i y 'm, i

c wher e weighteth es i (?> . d) mea ne collisioratith f o o n stopping power J 111 j I of the medium, in, to that of the detector material, i. Equation (1) can be used for both photon and electron beams with energies above 1 MeV for a sufficiently small detector.

e procedurTh e Nordith n I ec protocol

In vie f theiwo r simplicit precisiond an y e methoth , f usino d r ioni/agai - tion chambers is recommended in the new Nordic protocol.

The modified Uragg-Gray equation (2) is recommended for the determina- e absorbeth tio f e referenco nth t da dose, e e e wateD ,pointh th n n i i rt w absence of the chamber at the users radiation quality. In the case of a cylindric chamber this give e absorbeth s d positioe doscentre th t th ea f o ne e ionizatiooth f n chamber.

Thus u (w,air) r ai uDw = D . • p s . . (2) where

Dair - ND ' Mu

130 and mea= n absorbe e e cavitionizatioth th D f n i o yd r dosai n o t e chamber measure usere waten i dth t sa r radiation quality in Gy. s, = mass stopping power ratio, water to air, at the reference point at the users radiation quality, p - total perturbation factor including corrections for - lack of water equivalence in the ionization chamber mate- rial at the users radiation quality - perturbatior e insertioai th e e fluenco th t th f e f o no n du e cavity - locatio e effectivth f no e poin f measuremeno t e cylinth f o -t dric chamber due to the curved ionization chamber wall. absorbe= d r ionizatiodosai N o t e n chamber calibration facton i r Gy per nC or Gy per div. M -= meter reading at users quality corrected for temperature, pressure, recombination, etc., in nC or div.

e use b r botEquatio fo dn hca electro) (2 n photod an n n beams.

aUbrationC f_> _th_ej _ iojnza tion _b_e_m _cha r

A calibrated ionization chamber e determinatiomus th e use b r t fo d e th f o n absorbed dose to water, D . The chamber in use shall be calibrated at r n standards laboratorie o

where W mea= —n energ pain io r y r r electroformeexpendepe pe d r ai an d n n i d e _1 charge (W/e is equal to 33.85 J C ) k „ - attenuation and scattering in the Ionization chamber material at the att 60 calibration in the Co-

131 k chamber material dependent factor correcting1 for the lack of air equivalenc e ionisatioth f o e n chamber material, - fractio - e energe secondarth th f f o ng o y y charge1 particles loso t t bremsslrahlung in air (g is ai (To- • beam close to 0.00-i). M mêler reading at calibration corrected for temperature, pressure r divo C .n etcn i .

Values of the factors k and k for lypical cylindrical chambers are Litt III given by Johansson el al (1077). For a Farmer O.(i CM; chamber with walls of graphite or similar materials and with a pcrspex build-up cap (it) the k times k for a Co--/ beam is equal lo u.!)7-i.

——Th—e —tota — —••*••l perturbatio• ••••-———-..-..-——jn factor,- pjj e totaTh l perturbation facto s i introducer e modifieth n i d d Uragg-Cîray equation (2) tu correct for the disturbance of the parLk-lc flueiice caused e insertioth e ioni/.atioy th b f o n n chamber e correctioe valuth Th f . o e n factor depends on the ionizalion chamber si/.e and construction and on the radiation beam quality.

e totaTh l pertui-balioti factor include correction r throfo s e different effects, namely : 1) a correction for the lack of water equivalence of the ionizalion cham- ber material. This will disturb the electron fluence in the air cavity, e electrons soma th f o e s then wile produceb l a non-wal n i d er equi- valent material. This effect depends on the material and thickness of e chambeth r wald variean l s with radiation beam quality.

a correctio 2e )differen th r fo n t scattering propertie e wateth d f an o rs the chamber (wall and air). For electron beams this correction could o severat p r u cent pe e l b . This effect depend e sizgeod th an en -o s metry of the chamber and varies with electron energy.

3) in the case of a eylindric chamber a correction for "the effective ii point of measurement due to the curved ionization chamber wall. For absorbed dose measurements at the reference point a correc- tion factor shoul e appliee b dreading- th ey o e centre t d th Th . f o e lindric chamber shall then be placed at the depth of the reference point.

Total perturbation factors for eylindric ioni/.ation chambers with a dia- meter of 5 mm have been given by Johansson et coll. (1977).

132 The mass stopping powe) r. ratio s ( , ______" ______w.air u e modifieth f o e d us Bragg-Gra e Th y equatio ) require(2 n n accurata s e knowledge of the stopping power ratio (s . ) . For electron radiation \Vj ulJr u the stopping power ratios from Berger et coll. (1975) are recommended and for photon radiation those from Lhe [CRU (19(i9, Table A3).

Two different sets of stopping power ratios should strictly have been used, a chambe r r equivalenfo ai f e o ron t wall d anothe an a schambe r fo r f o r water equivalent walls. However electron i , nseto f beamdatiw o s e a th s differ with less than one per cent. For inosl practical purposes this small difference can be ignored. Therefore, for simplicity, only one set of (s . ) is recommended, w.air u

Measuring procedures

r photoFo n beams with maximum energie electrod an s V abovnMe beam1 e s with energies above 10 MeV, the absorbed dose at the reference point should be determined in a water-filled phantom. The ionization chamber should be protected durin e wategth r measuremen a tub y eb t manufactured from poly- methylmethacrylate. The tube should be attached to a holder that can be adjuste r measurementfo d t varioua s s depths e symmetrTh . ye th axi f o s chamber must be positioned at the reference point.

For electron energies in the range 1 MeV to 10 MeV the absorbed dose in the reference point should be measured in a solid phantom. A plane parallel ionizalion chamber should the e usednb .

Conclusio consistencd nan y

The here presented procedure will be introduced in the Nordic countries. Difference e absorbeth n i s d dose determination usin e methodgth s given in NACP (1972) compared to methods given in the new protocol can be r cen extrempe n i t 4 o t s large3 a casess a e . Such case e electroar s n beams with energieMeV0 1 o t , V a whersplan frow Me eno em1 paralle l chambe s recommendedi r .

In table 1 is shown the total conversion factor in Gy per R to be applied e meteth o t r readin a Farme r gfo r ionization chamber with wall f grao s - phite or air equivalent walls. The chamber has been calibrated in a Co-^ beam wit a perspeh x build-u fren i ep e calibratioairpca Th . n facton i r R/nC or R/div have been used. For photon beams with energies above 4 MV the new NACP (1980) have conversion factors which are 2-3 per cent higher than the old factors for the type of chamber mentioned above. This

133 s whai t coul goon i e expecteb d ds i agreemend dan t with other investiga- tions. Almon d Svenssoan d n (1977 d Nahur an )Greenind an a g (197G)r Fo . electron beams there is a good agreement for energies above 10 MeV between the new and old conversion factors.

Total conversion factor (Gy/R)

Radiation quality Depth NACP NACP 1CRU ICH U mm 1980 1972 1969 1972 D 60 Co v- -ray 50 0.00949 0.0095 0.0095 X-raV M y8 GO 0.00946 0.0093 0.0093 20 MV X-ray 100 0.00926 0.0091 0.0090 X-raV 3M 0 y 100 0.00918 0.0090 0.0089

" c V Me 0 1 = - K~ 20 0.00873 0.0089 0.0088 o E - 20 MeV e 30 0.008-13 0.0085 0.0084 o e V Me 0 3 - E 30 0.00817 0.0082 0.0082 o

E -• The mean energy of the electron beam at the surface of the phantom. W 1) The factor is equal to k ) q (2)c (3 , e se — p • • k s att m e 1 w,a u a Farme r fo ( ) an0. r(4 d (4) for a Farmer 0.6 cc ionization chamber with wall of graphite. 2) Correction for perturbation is made.

References

ALMOND P.R. and SVENSSON II.: Ionization chamber dosimetry for photon and electron beams. Acta radiol. Ther. Phys. Biol. 16 (1977), 177.

INTERNATIONAL COMMISSION ON RADIATION UNITS AND MEASURE- MENTS (ICRU): : RadiatioRepor14 o N t n dosimetry. X-ray d gamman s a rays with maximum photon energies between 0.6 and 50 MeV. Washington, D.C. 1972.

- : RadiatioRepor21 o N t n dosimetr : yElectron s with initial energies between 1 and 50 MeV. Washington, D.C. 1972.

134 JOHANSSON K.-A., MATTSSON L.O., LINDBORG L. and SVENSSON H.: Absorbed dose determination with ionization chambers in electron and photon beams with energie sMeV 0 betwee5 : d InternationaIn .an n1 l sym- posium on national and international standardization of radiation dosimetry. Atlanta, 1977 (IAEA-SM-222/35).

NAHUM A.E GREENINd .an G J.R.: Inconsistencd n derivatioyi an A C f no C_. Phys. Med. Biol. 21 (1976), 862. &

NORDIC ASSOCIATIO F CLINICANO L PHYSICS (NACP): Proceduren i s radiation therapy dosimetr electronV Me roentged 0 y5 an s wito t d 5 hnan gamma rays with maximum photon energies between 1 MeV and 50 MeV. Acta radiol. Ther. Phys. Biol. 11 (1972), 603.

- Procedures in external radiation therapy dosimetry with electron and photon beams with maximum energies between 1 and 50 MeV. Acta radiol. Oncol. Rad. Phys. Biol (1980)9 1 .. 55 ,

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135 HIGH ENERGY RADIATION DOSIMETRY AND CAVITY THEORY A re-examination A.O. FREGENE Dept Radiatiof o . n Biolog Radiotherapyd yan , Colleg Medicinef eo , Lagos University, Lagos, Nigeria

Abstract

High energy dosimetry by a solid or partly solid cavity of material different from the medium, either by an ionisation chamber and applying the concept _ n generaC i LiFy b d s r ,an Cha o ,^ l been carrie t varyina t dou g radiation energies with the cavity or wall material and its thickness virtually ignored. This approach which entails the application of Bragg-Gray relation appropriatn a t andno e cavity expressio datn_ C cannoa d an e rightb t\ G . ji obtaine limitea y db d semi-empirical expression which takes full accounf to chamber wall material and thickness are compared with C^ and C_ data by the only other approach in the literature (Nahum and Greening 1978) which takes accoun walf to l materia thicknessd lan . Recommended ICRÜ values (l969f 1972) are also presente obviour dfo s reasons.

A similar parameter, the LiP response to high energy radiation relative to Co photons as estimated by the semi-empirical approach, is also compared wit£. existing theoretical data and normalised FeSO. estimates.

) Introductio(1 n

Tne concept leading to the introduction of C,\ and CE, was proposed by Greene and Massey (1966); these two parameters are of considerable importance in high energy dosimetry and are generally in use. However, their values as recommende ICRe th U y d(1966b , 1972 todae )generallar t yno y accepted, (Nahud man Greening 1976). Pregene (l977a) argued that a shortcoming of previous analyses including ti.at of the ICRU. is that both the chamber wall, and its lining of material different fro mediue m th ignoree mar thein di r derivation neee ;o th d t suitablwala e y th allolb r wfo e cavity theor stresseds y wa alter n a s A .- native, Pregene proposed that chambers may be constructed such that the wall and same lininth r equivaleneo e gar mediue tn wall-lesa o ( mt s cavity situation). Green Massed ean y (1978), Pitchfor Bidmead dan d (1978) etc. have agree principln di e thawale tth l effect mentione Fregenn di e (l977a) shoul takee db n accoun. tof

(2) The parameters C^ and C„ - conversion factors of dose in roentgens in absorbeo t r ai d dos radn ei waten si r hav unie eth t rad roentgenr spe e Th . particulaa t a _ C r ro value hig^ C hf so energ dependene yar whicn o t f ho the following three approache assume s sestimatioi e d th an n ^ di Cj f no „

137 assume w f I e that dosimetridean a y lb s Bragg-Grai y cavitys yga have ,w e

C» or C-, = - (S.-L v ...... (i) ' v ' ' ^ A - (S.- = C-E, v L e ^ rn'i'E or \

as —W, has the same units as C^ and C_, equation (i) is dimensionally balanced. o calibrationC t tie no o t ds I i t .

If on the other hand we assume a finite sized wall-less gas cavity whose dimension at Go energy is characterized by a displacement factor A, then

...... (ii , S ( ) - A. = ^ C r o GX ' ^ v w x mji)^ e or E E A

The perturbation correction (P_ \), following ICRU (1972) is taken as

unity e expressioTh . sam e s applieth a e s i n ICRn „ (iii dG Ur )recommendefo d ü datacorrecs wall-lesa i r t :i fo t swallea chambet no - d t ex one rbu e .Th pression for C;\ is also correct for the hypothetical wall-less gas chamber whic t higha h radiation energies, witcorrectioe du h displacementr fo n , approximates Bragg-Graa y cavit normat ya l thimble sizes.

In practical measurements a walled cavity of material different from the mediu useds i m thin ,i s instance, neither equations (i)nor (ii applicablee )ar . In this cas ea limite d semi-empirical expression base n lineao d r principles of energy deposition along thin wails, which takes account of wall material and thickness (x) at energy E, such that the seondary electron range is r , may be applied.

E orA""'*P (iii)

Althoug walleha d chambe uses ri practicen i d , howeveapplicatioe th n i r n of C^ and C values, the condition fcr a wall-less chamber i.e. equation (ii), the same as in ICRU (1972) estimation of C is used; the C^ format also did not take account of the wall. Pig. (l) illustrates schematically the three situations above.

) Apar(3 t fropreliminare th m ydat„ publicationG Pregen n ai d an e^ C f so (l977b) which were obtained by applying the limited semi-empirical cavity expression onle ,tn y otheC whic d r an hvalue ^ takC f eso accoun chambef to r wall and thickness are in Nahum and Greening (1978), who used a modified Spencer-Attix cavity theory. Their work provide opportunitn sa comparo yt e dat„ C ad witan h^ C those estimate semi-empiricae th y db l expression which itypicae s th vali r lfo d standard chamber wall thicknes ;.ign si h energy beams. It shoul notee db d that Burlin's (1906) general cavity theor alss yi oa modificatio Spencer-Attie th f o n x theory. Whil photoe eth n beam component of Burlin's theory has been widely accepted, the electron beam component i.as been widely criticised Almon McCrad an d y (1970)| Paliwa Almond lan d (1975), Holt et al. (1975), Pregene (1976) and Shiragai (1977).

138 worts Ii t h noting tha Narmn i tGreenind an m g (1978), they took accounchamber'e th f to s wall ^materia' en( )ter a y mlb which allower dfo direct photon interactions with it. However, for electron beams in which no photon is present their expression should reduce in effect to that for a Bragg-Gray cavity or rather that of a wall-less cavity, identical to the ICRÜ approach. This is also reflected in the closeness of their C„ data

with ICRU (1972) tabl» valueE C r e sfo (ii) .

Tables (i) and (ii), show the values of C^ and C„ as given by the semi-empirical expression, Nahum and Greening (1978), and ICRU (1969 and 1972). ICRe Th ^ UdatC a differ considerably froothee mth r two, whil C_date eth a agree very well with Nahu d Greening'man s C_,. .CJ

Relative Respons LiFf eo .Cavita y Effect

(4) A similar problem to that of the Ci and C_, values, is tr,e relative 60 response of LiF to high energy radiation and Co photons, this response has been analyzed on the basis of the semi-empirical approach which relates detecton mediui n thicknesi f ) doso ) dosD d , m( eD rw an ( em.b , sx y

+ * 1 - * S w m mo

The relative response for LiP obtained by expression (iv)in table (iii), is in excellent agreement with the normalized comparative PeSO experimental value determines sa differeny db t authors (Pregene 1977c) woult I . d seem that for commonly used sizes of LiP, about 1 mm thick, a 1% decrease in LiF response to higi energy radiation relative to Co photons owing to the solid cavity naturoccursP Li f eo . conclusionn I ) (5 shoult ,i statee db d that dosimetr generan yi l evey nb tiny detectors, if not completely matched to medium, should be based on an appropriate cavity expression commoe ;th n approximatio thesf no e situations by the Bragg-Gray relation is not precise.

A semi-empirical expression based on linear energy deposition by secondary electrons has produced data which not only confirm reliable experimental finding of response of LiP to high energy radiation relative to Co photons but agrees quite well with Nahum and Greening's (1976, 1978) Cjy data; both of which differ appreciably from ICRU data. The revised C„& data by the semi- empirical approach differ slightly (ove belo% r1 MeV0 1 w ) from ICRNahud Uan m Greening'd an s which oddly enough agree quite well.

139 References (1) Nahum A. E.; and Greening J. R. Phys. Med 4 (1978. 89 Biol , )23 . (2) Greene, D., and Massey J. B. Phys. Med 9 (1966. 56 Biol , )M . (3) ICRU 1969, Radiation Dosimetry: D-rays and Gamma Rays with Maximum Photon Energie 0 MeV5 s d ,between an Repor 6 . (ICR0. 14 t U Publication, x 30165Bo . P,0 . Washingto C 20014D n , U.S.A.). ) (4 ICRU 1972, Radiation Dosimetry: Electrons with Initial Energies between 1 and 50 MeV, Report 21 (ICRU Publications, P. 0. Box 30165, Washington 20014C D , , U.S.A.). (5) Nahum A. E.; and Greening J. R. Phys. Med. Biol. 21, 862 (1976) (6) Fregene A. 0. Phys. Med Biol. 22, 1017,(1977a) (7) Greene D. and Massey J. B. Phys. Med. Biol. 23, 172, (1978) ) (8 Pitchfor d Bidmeaan . . G dM d Phys. Med. Biol , 33623 ., (1978) ) (9 Fregen. 0 . A e Nationa d Internationaan l l Standardizatio f Radiatioo n n Dosimetry in Proceeding a Symposiu f o s m IAEA SM-222-27; Vol Atlant, .II a Dec. 5-9, (1977b) CIO) Burl in T. E. Brit 7 (1966Radiol. .J 72 , )39 . (11) Almond P. R.; and McCray K. Phys. Med. Biol. 15, 335 (1970)

(12) Almond . R an Paliwal . ; P dR. . B , Phys. Med. Biol. 20, 547 (1975)

(13) Clard , EdelsteinHoltG. an k , . J T.E,R. . G ., 9 (1975 55 PhysBiold , )Me 20 ..

(14) Shiragai A. Phys. Med. Biol. 22, 490 (1977)

(15) Fregene A. 0. Radiât. Res. 65, 20. (1976)

(16) ßitiks C. Phys. Med. Biol. 14, 327 (1968)

(17) , Crosb ; AlmonShaleH. . R; J . . . E yP d R k Phys. Med. Biol , 13111 . , (1966)

(18) Laugh!id Pinkerto. an S . ; G Hol. nJ H. . . J t nA Phys. Med. Biol. 11, 129 (1966)

(19) Bristovic. M., Maricic Z., Greenfield M. A., Breyer B., Duornik K. Slaus I., and Tomas P. PhysBiold , 414Me 21 .. , (1976) (20) Fregen. 0 . A e Int. J. App. Radiât, and Isotopes 28, 956 (1977c).

140 DEPTH DOSE PROFILE CAVITY 100 -,

UJ S a RADIATION fc 50 -

BEAM

POINT CAVITY;BRAGG-GRAY CAVITY

_____ 100 _

RADIATION

SO. BEAM

- AIR CAVITS WALUS YL- - DISPLACEMEN T FACTO" R"A m -,

RADIATION

Wall a BEAM

>*«- WALLED '—————_r AIR-> WALLED CAVITY-WALL THICKNESS (»^DISPLACEMENT FACTOR 'At

141 Comparison of Recent C» Values and ICRU Data

Photon Energy Nahu Greenind man g (MY) (1978) ICRU 1969 S emi-Empir ical

2.0 .950 .950 .950 60 Co .957 .950

4 .94

5 .959

6 .954 .94

10 .93 .954

12 .92

]4 .939 (13MV) .92

15 .948

18 .91

20 .936 (19MV) .90 .942 25 .936 (26.8MV) .90 .929 (26.8MV)

30 .921 (31 MV) .89 .928

35 .913 (31MV) .88 .922

40 .919

Table (i)

142 Compariso f Recenno E ValueC t ICRd san U Data

EQ Initial Energy Nahu Greenind man g ICRU 1972 Semi-Empirical Electrons (1978)

2 .933

5 .920 .922 .912

]0 .890 .893 .883

15 .858 .852

20 . 845 .848 .840

25 .830 .826

30 .815 .816 .815

35 .804 .802

40 .794 .795

correcte ICRo dt U recommended depth assuminy sb g

a 2MeV/cm energy loss with depth

Table (ii)

143 Comparison of Cavity Theories and FeSO4 Data by

Respons Higo et h Energy Badiation Relativ o C Photon o et s ß A

ELECTRONS

NORMALISED FeSO4 CAVITY THEOEY VALUES Paliwal Burl in Holt and et al. et al. Almond Shiragai Present No. Author Values 1969 1975 1975 1977 Work

1. Binks (1968) .888 .917 2. Crosby et al. (1966) .935 3. Pinkerton et al. (1966) .916 4. Fregene (197 6) .945 5. *Bristovic et al. (1976) .930 6. Almon Crae M y d& (1970 ) .938

Mean .921 .69 - .850 .91. 8- .905 .96 - .98 .935

PHOTONS

7. *Bristovic et al. (1976) .940 8. Almon McCrad& y (1970) .930 9. Crosby et al. (1966) .925

Mean .932 .935

Mean of Ten Best FeSO4 Values (Photons and Electrons) = . 929 ± . 014 *Use dChemicaa l Dosimeter (althougt hno

Table (ill)

144 ANNEX

Procedure Externan si l Radiation Therapy Dosimelry with Electro Photod nan n Beams with Maximum Energies Between I and 50 MeV

Recommendations by the Nordic Association of Clinical Physics (NACP'i

These recommendations have box-» prodviced by the Swedish Association of Radiation Physics and the Nordic Association oi'Clinical Physios aided by y large number of their members. The members of ihe Topic Group, vvcre H. Sven^son (chairman) . LindborL . g (secretar . JohanssoA . . Dis«N K . yd 1 . an nValuabl e s gratef\ilii criticis d ai d \m an acknowledged . AlmondP : . BrahmeA . . j-'iatbyJ , , D. Harder, C>. Mrtnsson. I. Uotila, and ihc FJh.D. students arid teachers from the K;uli;uion Physics Departmen J.inkopingn i t . The meetings of the working party wece siipponcd both by the Swedish and Danish Cancer Society.

Reprinted with permission from Acta Radio!. Oncolog( 9 1 y

145 Introduction The Internationa] Commission on Radiation Units e phantoath t m surface where plane-parallel cham- and Measurements (ICRU) has published general re- bers shall be used. Such procedures will be ex- commendation n dosimetro s y procedure r phofo s - plained in a supplement to this protocol to be pub- tons (ICRU r electron1969fo d an ) s (ICRU 1972). lisheneae th rn di future . These should preferably be supplemented recommendatione bth y f nao -m ai e givo Th t s ei s hos- tiona r regionao l l suggestions covering practica- de l pital physicists a 'code of practice' to be followed tails of routine dosimetry procedures and taking into at radiation therapy centre Denmarkn i s , Finland, accoun e particulath t r requirement provisiond an s s Iceland, Norway and Sweden so as to secure uni- countre oth f regiond yan . Local recommendations formit n dosimetri y y procedures. They covee th r have been prepared for the United Kingdom (HPA testd measurementan s s both when dosimetrs i y 1969. 1971 (SCRAA , 1975)US e Dth . 1966, 1971, first performe dtherap w witne ha y apparatun i d san AAPM 1975). West Germany (DIN 6809 1976, DIN the continuous supervision necessar ensuro yt e that e Nordith 680 d c0an countrie) 197b . 5a s (NACP the dosimetry is properly employed in radiation 1972). therapy. In weighting high accuracy and theoretic The present report contains a revised Nordic pro- strictness against practical usefulness, the latter has tocol. Several reasons have motivated this revision. been given more emphasi o thae procedures s th t s After publication of the first protocol several reports may be performed easily at all therapy centres. have been published giving new data on various Principal features. The dosimetric method of us- effects which can change the factors used with inr ionizatiogai n chamber stils si l recommender dfo ionization chamber dosimetry. The Si-units for the linking the national standard to the local reference, radiologie quantities should be applied. Another im- mainly in view of their general availability, simplic- portant reaso s thai e nforme th t r Nordic recom- ity and precision. For the radiation quantities of mendations were mainly base n investigationo d s concern here the ionization chambers shall be cali- with betatrons, while within the Nordic countries brate t nationaa d l radiation standards laboratories now several other kinds of accelerators are used in 60Co-7 ray beams.

(standing wav travellind ean g wave linear accelera- Since the formerly used CE- and Cx-values were tors and microtrons) with usually different proper- onl r yequivalen ai vali r fo dd watean t r equivalent ties, which have to be considered. Improved con- chamber walls, respectively, a new procedure for cepts for stating beam quality and beam uniformity the determination of absorbed dose is recom- etc are therefore introduced in the present report. mended e procedurTh . s basei ederivea n do - ab d

Similar revisions are being carried out by the ICRU sorbed dose ionization chamber factor (ND) giving anAAPMe dth . the ratio betwee meae nth n absorben i d r dosai o et Difference e absorbeth n i s d dose determination the ionization chamber cavity and the scale reading. 60 using the methods given in NACP (1972) compared ND is derived from a calibration in air in a Co-y methodo t s presene giveth n i n ts a protoco e b n ca l ray beam e absorbeTh . d dos wateo t e t varioua r s large as 5 per cent in extreme cases. It is recom- radiation qualities is then obtained as the product of

mende protocow dne thae th tl wil e adapteb l t a d meter readings , stoppinD N , g power ratio perd san - various centre calibrationw s soone a s s na f ionio s - turbation factors. Stopping power ratio d peran s- zation chambers have been achieved. turbation factors are both listed. The latter are given e presenIth n t report shall means compulsory for chamber f r eithewateo so r ai r equivalen- ma t for compliance with this report and should means terials, the equivalence of concern being the prop- strongly recommended. ert f generatino y g secondary electrons. Water o r These recommendations do not include the com- air equivalent material e recommendear s e th r fo d plete procedures for dosimetry of electron beams ionization chambers at least for reference instru- in the range of ! to 10 MeV mean electron energy ments.

146 Table 1 Energy quantities for specifying radiation beams

Quantity Use Determination Energy range

£p.a On accelerator £p..-£p.«+25coiLi • A*, eq. (1) 1 MeVs=£p.aas50 MeV console

EP.O Specification of £p.o=Cl+C,W0+C3A| eq. (2) 1 MeVss£p0ss50MeV absorbed dose C,=0.2V 2Me 1 distribution C2= 1.98 MeV cnr 2 C3=0.0025 MeV cnr

As reference to £o=C4A50 eq. (3) 5 MeV«£0=s30 MeV 1 dosimetric constants C4=2.33 MeV • cm'

The increasing number of accelerators of different Therefore, analogous energy quantities can be de- type ofted san n quite different beam qualities neces- phantoe fineth r dfo m surfacey an r fo , d indean , xo sitates a simple unified comparison of the quality of depth z in the phantom, index z. These different one beam with another. The main therapeutic and electron energy quantitie recommendee sar e ar d dan physical propertie depte th f hso dose distributiof no summarized in Table 1 and Fig. 1. Their principal the beams are therefore characterized by new para- uses are: meters not used in NACP (1972). £p,a (the most probable - energac e fronn th yi f o t celerator window): For a given accelerator beam setting different beam scattering foils or decelerators Energy determination at accelerators are often used. However, the energy instruments A knowledg radiatioe th f eo n qualit necessars yi y e usuallar y constructe givo t d a measure e th f o e because stopping power value d perturbatioan s n electron energy of the intrinsic beam. Therefore, it factors recommended here for ionization chamber is recommended that the energy indication meter dosimetry, are energy dependent and because stand- and the energy selection setting on the console desk ardized depth dose tables may be used for accelera- be calibrated in an energy quantity which is inde- tors similar in construction, provided the energy is pendent of the materials in the beam. £p.a should determine unifora n di m manner (SvENSSO HETN& - be the energy quantity to use for this purpose. TINGER 1971, SvENSSON 1971). Furthermore, qual- £p.o (the most probable energ phantoe th t ya m sur- ity parameters may be desired for the comparison of face): To indicate the energy of an absorbed dose one beam with another. Depending on the parameter distribution, £p,0 shal usede b e reasol Th . s thani t f intereso t different energy quantitie e recomar s - this energy quantity is well related to the practical mended r electroFo . n beams recommendes i t i , o dt range , whicp A , h generall uses yi r energ dfo y deter- use a therapeutic range to describe the radiation mination. £p.0 is in most accelerator facilities 1 to 2 quality in irradiation procedures. MeV lower than £ pr energie.afo s below som0 2 e MeV. This difference may increase with energy. Electron beams 0 (th£ e mean energphantoe th t ya m surface)n I : Energy quantities. The intrinsic accelerator beam, absorbed dose measurements wit n ionizatioa h n electroe i.eth . n beam just befor exie eth t windof wo chambe relevane rth t stopping power ratio perd -san the accelerato t afterbu r beam handling magnetd san turbation factors must be known. These are in this energy defining certaia slits s ha , n energy distribu- protoco depte th lf d ho give functioa an s 0 na £ f o n tion. This can be characterized by its maximum the chamber in the phantom (Tables 5,7). [In NACP

energy (£m ,s mosa)it , t probable energy £p.s a,it (1972 e absorbeth ) d dose conversion factors (CE) mea energs it n- d energin y an e sprea, a th y£ ; a dr were correlate meae th no dt energ phantoa t ya m de standa x r acceleratorfo s beae th ms A .passe s depth, a quantity estimated from the relation throug e exith h t windo d differenwan t materials fro exie mth t windo e phantoth o wt m surface th e energy will decreas energe th d yean spread increase.

147 at accelerator exit window (a)

•m a e distributioTh Fig . 1 . f electrono n n energi s e th fronn i y f o t accelerator window (a), at the phantom surface (o), and at the phantom depth ordinal(;)e .Th e show differentiae sth l distribu- tion in energy of the one directional plane fluence, NEt normal- mosvalue s izeit th t o dtt ea probable energy, NEP.

P R 0 "5 5 "8 "100 In this equation £0 was approximated by £p 0- In the DEPT WATEHN I m R/m present protocol it is considered that £0 may be a e deptTh Fig. h2 .absorbe d dose distribution with definitionf o s the parameters used in the text. D is the level of maximum ab- loweV fewMe r than £ thereforepd .0an , tha detera t - m sorbe surface dth doses i s e dos£> , e depth m measurem 5 , 0. t da minatio Êf nOo shoul made.e db ] ux is the photon background, G is the dose gradient, /?,„„ is the Energy determinations. Ep.o should be determined depth of dose maximum, RBi is the therapeutic range, R-M is the half-value depth, and R0 the practical range. (From BRAHME & by analysing the central axis depth dose curve mak- SVENSSON 1979.) ing use of the empirical relation between the prac- tical range in water, /?p, and £p.0 (Table 1). In the energy range 7 to 20 MeV eq. (2) gives, within ±1 used, i.e. ^ 120 mm x 120 mm for energies up to 20 per cent same th , lineae Eth ps .r0a equation recom- MeV and ^200 mm x 200 mm above that energy. mended in NACP (1972), i.e. /?„=£„.„• 0.52-0.3. source-surface Th e distance (SSD) shoul 3=e . db 1m Outside this range the difference increases. For the With some plastic phantoms the relation between R p energy range 1 to 50 MeV the relation recommended in water and in plastic may be calculated from the here (eq. 2) fits experimental (MARKUS 1964, HAR- formula (MARKUS 1961 1976)N ,DI . DER & SCHULZ 1971) and calculated data (SELTZER t colle . 1977 withio t cent)r pe n2 . e practicaTh l range ) (Tabls (2 i ,. ) /?1 eeq pn ,i e defineintersectioth s a d n e tangendeptth f o h t (4) through the steepest point (inflection point) of either depta h absorbed dose curv depta r o e h ionization eff.H20

curve and the photon background (Fig. 2). The In this equation (Z/A)eff=2fl(Zi/Ai), where £ is the curves should be measured as described on page 17 fraction by weight of the constituent element of making use of the concept of the effective point of atomi relative c th numbe d ean , atomirZ c masp , sA, measurement. is the density. Index pi stands for plastic. Eq. (4) 2 Depth absorbed dos deptd ean h ionization curves e use b r material fo dy ma s with (Z /A)eff<4 (DIN. iwatena r phantom givee withith m nm abou2 o t 1 t 1976); values of some materials are given in Table 2. same p valu(SvENSSOK f eo HETTINGEN& R 1971). -ÊO should be determined from the empirical eq. (3) e determinatioth r Fo f £„, no e measuremen „th f o t (Tabl e hal) relatinth 1 e f o t valu t i g e depth, /?50, depth ionization curves is recommended. Abov er cen1pe 0 t0 5 dept define- e e deptth ab hth f s ho a d MeV both cylindri d plane-parallean c l chambers sorbed dose in a water phantom (Fig. 2). The linear could be used but below about 10 MeV only plane- eq. (3) should be used in the energy range 5 to 30 parallel chambers should be used as they have the MeV. The relation between /?30 and E0 outside this best defined effective poin f measuremento t r Fo . range, should be taken from Table 5 and Fig. 3. energies above 10 MeV a water phantom shal s strictli l ) be(3 y . valiEq dn infinit a onl D r fo ySS e ; used, wh !e below 10 MeV either a water or a plas- but may also be used for SSD down to l m for tic phanto usede b n .m ca Larg e field sizes muse b t energies up to approximately 20 MeV (Fig. 3).

148 40

30

0>

20

10

l ! l ! l l l l l l l l i i i 50 100 150

^507 mm

Fig. 3. The relation between RM and E? for largo field sizes. The depth absorbed dose curves with SSD=1 in, and the dash-dotted solid linM determine s R valii e r to d d from beam axis dept- hab linbear efo m axis depth ionization curves with SSD. m =1 sorbed dose curves with SSD==, the broken line tor beam axis

Table 2 losseelectrone th f l scatterino sal n i s g materialn i s Some characteristics of phantom materials the radiation beam, e.g. window, scattering foils, transmission chamber aird san , mus addee e b t th o dt Phantom Composition o k 3 electron energy, £„.„. The thickness of the various material cm"• g Weir materials, A,Yj, which the beam passes from the in- Water H,O , 0.555 1.000 tube r sidth ef ne eo windo phantoe th wo t m surface Polystyrene CeHn 1.05 0.538 1.018 must be known as well as the collision stopping Perspex C.H.O, 1.18 0.540 1.148 power of each material j,-C()lu. Materials in the beam A 150 see ICRUf 1977) 1.12 0.548 1.106 very near the phantom surface should, if possible,

be removed in the measurements of £p.0 as eq. (1) Above that energy inverse squar correctionw la e s gives an incorrect estimate of Ep a with materials nea phantoe rth m surface. shoul performede db shoul0 5 K . e measuredb d with large field sizes and should be determined from a depth absorbed dose curve but may be evaluated Photon beams from a depth ionization curve and the graph in Energy determinations. For a proper choice of Fig. 3. stopping power ratios and perturbation factors in Ep.a shoul e calculatedb dn i accordin) (1 . eq o gt photon beams a measure of the photon beam quality Table 1. The calculation means that the energ e estimateyb n ca d from depth ionization measure-

149 2.10

2.00

1.90

1.80 \

1.70

1.60

1.50

1 40

t I I i 10 20 50 ACCELERATION POTENTIAL/MV e ratiTh o Fi 4 JgWO IJW<, (^Dlot)c a a functioID e s zma th ) f o n irons tha r lineanfo r accelerator microtrond san l ratioAl s s over celeratmg potentia fiela r hv shows d i (o mdlSSDa ) an r nm fo = l e froar mV 2betatrons0M , while thos e takear e nV beloM 0 w2 size of 100 mm x 100 mm For accelerators with the same ac- from linear accelerators JmoU^m 1S recommended as input data celerating potentia e ratioth l s differ from beams v.ith different dir)u targets and flattening filters and are as a rule smaller for beta

ments (BRAHME & SVENSSON 1979) The lomzation photoe th n beam quality rather than measurements

at the depth of 100 mm and 200 mm m a water of the half value depth, Ra0, as the values of A,0 phantom is measured for a field size of 100 mm x depend upo e contaminationth f electronno e th n i s 100 mm and an SSD of l m and the ratio /i0o/-/>oo peak absorbed dose of the photon depth dose curve determined The ratio is stronger related to the mean e maximuTh m photon energy photoe ,th hvn i mn, photon energy than the maximum photon energy estimatee b bea n mca d witdiffereno htw t methods Therefore, if the ratio is calculated from published When both photon and electron beams are available data and plotted against the maximum photon en- from the same accelerator the maximum photon en- ergy, a rather large spread is found (Fig 4) The ergy may, within 1 or 2 MeV, be approximated by

JioMzoo method is recommended for estimation of £p a The energy meter on the accelerator is usually

150 copper indicator

hole

,, proposed SSD dowel copper indicator \ engraved reference line thickness

film dowel engraved X line 5 Polystyren g Fi e phanto e use b r bea fo do mt m alignment chec smalA k l misaiignemen s indicatei t e figure th th s a em d soli brokedand ncoincid linenot Ligh- sdo - - e t bea Radiam— - tion bea • Beam•- m axis designe givo dt emeasura electroe th f eo n energy as a beam quality parameter for use in choosing before the exit window and photon target. The me- e stoppinth g power ratios necessar r ionizatioyfo n thereforn ca r te calibratee b e e th d r againsfo a p E t chamber dosimetry (Tabl. e6) electron beams (see page 5). Alternatively a meth- threshol) on d , base(y n do measuremente b y sma Geometric considerations used (NACP 1972). This method make a direcs t calibration of the energy instrument in the maximum The position of the radiation beam must be de- photon energy, h^m, possible maximue Th . m photon fined and indicated to be able to perform accurate energy has conventionally been used to specify radiation therapy thin .I s section some simple proce- depth dose distributions. dures are given. The discussions are limited to Recent investigations have shown thashape th t e rectangular unmodified beams only, e.g. without e deptoth f h absorbed dos ee meacurveth nd an s wedges or blocks. energy for photon beams may be more dependent on the construction of target and flattening filter than Beam alignment on a change of a few megavolts in accelerating po- beae Th m alignment shal- in checkee b le th n do stallation of a new therapy unit. The manufacturer tential, i.e. in change of Em& (PODGORSAK et coll. 1975, NAHUM 1978). Therefore t considereno s i t i , d shoul e heldb d responsibl adjustmeny an r efo - re t necessary to carry out determinations of hvm, using quired befor e acceleratoth e s handei r d over fo r methode th s mentioned, neithepurpose th r fo f r eo routine treatments. dosimetry nor for the specification of depth ab- The proper alignment of the different types of sorbed dose curves Jioo/Jzooe Th . metho uncers di - beam axes (collimator rotation axis, geometric beam tain for the estimate of the maximum photon beam axis, radiation beam axislighd an , t beam axis a s energy, but is well related to the mean photon en- define Appendixe th n di ) shal checkee lb d before eth ergy and should therefore be used for dosimetric absorbed dose distributions are determined. Practi- procedures e ionizatioTh . n rati s recommendeoi d cal beam alignment procedures have been detailed in

151 Table 3 small depths due to electrons scattered from, for Depth referenceof plane instance, collimators thosn I . e case depte e sth th f ho reference plane shoul e minimue taketh b d s a n m Type of Depth of reference plane radiation values given in Table 3. Uniformity beamthe of Photons !-<10MeV 50mm V 100mMe 0 5 m - 10 A useful measure of the beam uniformity is the Me5 < V - 1 PeaEleck -absorbe d dose uniformity index (see Appendix). This index should V PeaMe k0 1 absorbe m < m 5- 0 1 iron dn dossmi r eo exceed reference 0.8th n 0i eabsorbee planth r efo d 10-<2 V Pea0Me k absorbem m 0 2 dn dosmi r eo dose at field sizes larger than 100 mm x 100 mm 20- 50 MeV Peak absorbed dose or min 30 mm for both photo electrod nan n beams additionn I . e th , beam uniformity should be such that the absorbed dose at any point in the reference plane should not the case of electron and photon beams by HPA r cenreference excee f th pe tha o tt 3 a t 10 d e point. (1970). AAP e consulteb My (1975ma dd whean ) n For accelerator beams the physical penumbra (see the checks are carried out. Also the International Appendix) shall not exceed 8 mm at an SSD of about Electrotechnical Commission workina (IEC s ha ) g 1 m..Some accelerator e overflattenear s t smala d l group dealing with such procedures. phantom depth orden si achievo rt gooea d uniform- An alternative metho teso positioe dt th e t th f no ity index at large depths. Then for any plane parallel light beam in comparison with the radiation beam referencthe to e plan absorbethe e d dosany of e appears in Fig. 5. The test should be carried out in arbitrary poin than i t t plane shoul t exceedno 7 10 d the following order. The bottom sheet of the phan- per cent of its value on the beam axis. tom is placed perpendicular to the collimator axis The radiation beams should as minimum require- with the front surface at the SSD in use. The light ments fulfil the values given but each hospital physi- beam sizpositiod an e n shall coincid- e en wit e hth cist should work for achieving as good beam uni- graved line on the bottom sheet. The numerical field formit s possiblya e generally aimin absorben a t ga d size shal e notedb l a lighfil A . n mi t tight coves i r dose variation within the target volume of less than placed on the bottom block and a top block with cenr 4 pe t 5 (ICR± U 1976). metal indicator places si d wit hfile carmth n witheo - The uniformity, the radiation field size and the out moving the bottom block. The thickness of the physical penumbra may be measured in various top block shoul approximatele db y refe equath - o t l ways. Photographic a polystyrenfil n mi e phantom erence depth (Table 3). After irradiation 4 dots on offers the advantages of high spatial resolution, sim- the film are observed from the indicators. These plicit f handlingyo , short irradiation time abovd san e dots should be used for comparison of the position all the fact that it will lead to simultaneous record- of light and radiation beam. The uniformity index, entire th in f ego radiation field. With some caree th , the radiation field size and the physical penumbra figures given for absorbed dose uniformity may be may also be determined from the same film. The equate e samth eo t d figures obtaine t filne m r fo d beam and the collimator axes shall agree within 2 blackening. A disadvantage of the film method is, mm and the position and size of the radiation beam however, s besthai t i t used wit n automatiha r o c and light beam shalD lSS agren a t ea withim m 2 n semi-automatic density plotter. With the film meth- f abouo . m 1 t e beath md o uniformity shoul e investigateb d y b d mean f photographio s c ligha fil n mi t tight covef o r Depth of liet reference plane regula radiatioa r f thickneso t no n t fluorescenbu s t Recommended depthreference th r sfo e planr efo material; industrially pre-wrappe usede b d y fil.mma various radiation qualities are given in Table 3. For e filmTh shoul exposee db polystyrena n di e phan- electron beams the depth of the absorbed dose maxi- tom (Fig. 5) and the absorbed dose should be about mu s recommendemi e referencth s a d e plane- in , a typica( y G l 2 treatmen o t 1 t absorbed doseo s ) steafixe a peakee f dth o d o deptt de depthdu - hab minimizo t s a influence eth f initiao e l perturbations sorbed dose curve r som energfo sw lo e y electron in accelerator beams and of shutter movement beams. However, for some accelerators and beam in 60Co--y beams. Before irradiation, accelerators size maximue sth m absorbed dos occun eca t verra y should have been run under operating conditions for

152 sufficiena t perio f timdo effeco et propea t r warm- these absorbed dose determinations a constancy e relatioupTh . n between film blackenine th d gan check procedure shal incorporatede b l . absorbed dose depends critically on the develop- ment procedure used; parameters of importance are lonization chambers and electrometers typ f fild developereo man , development timd an e Reference instrument. Each radiation therapy temperature. All these should be combined to pro- centre shall hav t leas elocaa e on t l reference (stand- duc a lineae r relationship between blackenind gan ard) ionization chamber, together wit electron ha - absorbed dose ove largra e range aperture Th . e dia- meter selected as a reference instrument for calibra- meter of the density reader should be selected to tio f fielo n d ionization chamber d othean s r dose- exert negligible influenc e spatiath n o el patter- nre meters. A reference chamber may also be used for corded. The variation in film density on a homo- the first calibration of a new therapy machine. How- geneously exposed film shoul lese db r s pe tha 2 n± ever, due tp good stability of modern electrometers cent; only a few types of film seem to meet these a reference electromete usee b dy als rma other ofo r requirements (RASSOW et coll. 1969, DUTREIX 1976). purposes. The reference chambers shall be cali- e filmTh density versus absorbed dose shoule b d brate standardizina t da g laboratory particularlr yfo checked regularly and at least every time a film 60Co-y rays in air. The reference electrometer shall batc developer ho changeds ri . also be calibrated at a standardizing laboratory. The Alternativel semi-conductoya r detecto smala r ro l calibration is preferably carried out separately for ionization chamber (i.e. diameter of not more than 5 the ionization chambe measurine th d ran g assembly. mm) coul e use db r traversin dfo e e beath gth mn i The chamber should be re-calibrated at a standardiz- reference plan watea n ei r tan gantrr kfo y anglet sa ing laboratory at least once every 2 years. A longer 90°, 270possibld °an fro° y0 verticae mth l position. interval can be acceptable for the electrometer, if This method will produce higher precision than the its stabilit checkee b independenn n a y ca n di t way. film method, provided that in connection with ac- response Th reference th f eo e instrument (ioniza- celerators, a monitor probe is used to correct for tion chamber and electrometer) should be checked output fluctuations e monitoTh . r probe shoule b d t leasa t quarterly agains a suitablt e radioactive placed either outsid e regioth e f interesno t (th0 e5 source at the radiation therapy centre, e.g. 60Co-y per cent isodose curve) or in the centre of the beam, source (half-life 5.27±0.01 year) changy - An re . n ei in which case the shadowing effect must be taken sponse referencth f eo e instrumen f moro t e tha1 n into account when evaluating the results. For other per cent reveale e constancth y db y checks should gantry angles the beam could be investigated by lead to a thorough investigation of instrument and mean poJystyrena f so e block - witde he holeth r sfo subsequent re-calibration at the standardizing lab- tector (NAYLO CHIVERALL& R - S ab 1970) e Th . oratory. sorbed dose distributio reference th n ni e plany ema A cylindric chambeo t rr volum 0 witai 10 n h a f eo the e equate nb e lonizatio th o t d n current distribu- 3 shoul mm e use b d0 s referenca d100 e ionization tion. chamber. If the chamber is to be used for calibra- tions of field instruments under conditions other than those at the standardizing laboratory (for in- Determination of absorbed dose at stance in a phantom) it is essential that the air vol- reference points ume diameter in the chamber is between 4 and 6 mm e absorbeTh d dose determination shal e madb l e lengte a wale th ans f Th lesf dha o lh. o s thamm 5 n2 by air ionization chamber measurements performed chamber should be homogeneous graphite or tissue/ b a yqualifie d persondeterminatiow ne A . n shall water or air equivalent material. The thickness of made b e whe conditionw nne irradiatiof so - em e nar the graphite chamber wall should preferably be ployed. The determination shall be confirmed perturbatio e witth s ha m aboum n5 factor0. t s reported an independent dosimetric method for instance calo- here have been determined with this wall thickness rimetry or ferrous-sulphate dosimetry and even less (ALMON SVENSSOD& N 1977, JOHANSSO t collNe . accurate methods such as those based on solid state 1977). The wall thickness is of less importance for dosimetr e usedb y . ma yBot e absorbeth h d dose water equivalent chambers. It is important that the determination and confirmation shall be performed materia sam e build-ue e th th thas s th e i f a f lo tp o pca before irradiation of patients. In connection with wall. In order to avoid mistakes the build-up cap

153 should be clearly marked and shall belong to a cer- ments (ICRU 1972) r pulseFo . d radiation beame sth tain ionization chamber e centraTh . l electrode measured charg plottes ei d agains inverse e th t th f eo shoul same made db th f eeo materia wale d th an ls a l polarizing voltag regioe th n lossef ei n o s belor pe w5 should preferably not be too massive. Leakage cur- cent e releaseTh . d charg s determinei e lineay db r rent, radiation-induced curren currend an t t generat- extrapolatio thin i s plo infinito t e polarizing voltage. stee th m n i mus d e negligiblee b t ratie Th .o between Electrometer. precisioA currenw nlo t measuring the ionization currents measured- at positive and electrometer shall be used. The electrometer is usu- negative polarizing potential shal e checkeb l d dan ally based on a high gain amplifier with a low leak- shoul e lesb d s tha nradiatioy 1.00an r 5fo n beam currene ag t working eithe charge/voltaga n ri e mode quality. This polarity effect increases with decreas n integratina -n i r o g Townsend-balance modeA . ing electron energ d shoulan y d - thereforcy a r fo e digital display is usually preferable. A solid state lindric ionization chamber be determined at various electrometer may be built with either field effect depth a phanto n i s a bea V r f maboumfo o Me 0 1 t transistors (MAUDERL BRUN& Y Oa 1966y b r )o mean electron energ surfacee th t ya . varactor bridge input amplifier (JOHANSSON et coll. Field instruments. e ionizatioTh n chamber used 1972). The scale on the electrometer should prefer- for the assessment of absorbed dose must fulfil cer- ably be marked in coulomb and ampere. The elec- tain requirements. A cylindric ionization chamber trometer should hav gooea d long term stability over should be used at ail photon radiation qualities and a number of years. t electroa n beams wit hmeaa n energphane th t ya - e instrumentTh s shal e constructeb l o t s a o s d

tom surface , 0 abov£ , MeV0 1 e plane-paralleA . l minimize the effect of external electrostatic, mag- chamber should be used at electron energies, E0, netid electromagnetian c c fields. Howevere th , equar leso so t ltha MeV0 1 n supplemenA . f thio t s strong electromagnetic field thatd existan n i s protocol will trea measuremene th t t procedure used around some accelerators may affect the reading of for the plane-parallel chamber. the instrument. Special attention is needed to ensure e cylindriTh c field chamber should have dimen- that this does not occur. However, large mistakes sions like the reference chamber. Chambers with un- in the dosimetry due to these effects will be dis- known wall, central electrode material and thickness covered as 2 independent methods shall be used in r wito a hthi n laye f inneo r r conducting material absorbed dose determination at an accelerator. shoul e subjectedb speciaa o t d l response test, i.e. be calibrated against the reference chamber for all Calibration nationalat standards laboratories radiation qualities used. Leakage current, radiation- e locaTh l reference chambe d measurinan r - gas induced current and current generated in the stem sembly shall be calibrated at national standards lab- must be negligible. oratories in a beam of 60Co-y rays. The calibration e respons Th e fielth df o einstrumen t shoule b d of the ionization chamber shall be made in air at a checked at least quarterly against a suitable radio- distance of about l m from the source to the cham- active source or against the reference instrument .a fiel t r x centra d be m d siz m f abouan e o e 0 10 t Any change in sensitivity of the field instrument of 100 mm. The cylindric chamber should have an ad- more than 1 per cent revealed by the constancy ditional cap of water or air equivalent material for check should lead to a thorough investigation of the chamber r equivalen f wateai so d an r t walls, respec- instrument and subsequent re-calibration against the tively, to assure electron equilibrium. The total reference instrument. thickness of wall and additional material should be Ion recombination. The losses due to ion recom- 0.45±0.05 g cm~2. If a perspex cap is used instead binatio e generallnar y less r cen thar conpe fo t1 n - of the recommended materials and if this protoco1 tinuous radiation or pulsed radiation of an absorbed is followed the systematic error introduced would be dose to air in the chamber cavity per pulse of 1 less than 1 per cent (ALMOND & SVENSSON 1977, mGy or less if the collection voltage is higher than JOHANSSO t collNe . 1977). e typ th f chambe eo r fo V 0 r mentione30 d abovef I . International recommendations now exist for pri- the losses are less than 1 per cent, re-combination mary standards laboratories to derive air kerma correction will not always be necessary. Correction from exposure measurements, using agreed upon for recombination e madeb losse n ,ca s eithey b r conversion factors e relatioTh . n betwee kermr nai a

calculation (BOAG 1966, ICRU 1964measurey b r )o - (tf exposurd airan ) (ICRs i ) e(X U 1971)

154 (5) Table 4 where m valuesk cylindrickalfor and , ionization chambers sizesof re- commended thisin protocol differentfor materials wallthe of and cap combination. The values are expected to be dependent g =the fractioe energe secondarth th f f o o ny y on the shape, size and electrode design charged particles lost to bremsstrahlung in air 60 (g is at Co-y rays close to 0.4 per cent, Bou- Chamber wall and ka« km TILLON 1977) materiap ca l WI e=mean energy expended in air per ion pair formed and per electron charge. (W/e is equal Air equivalent 0.990 1.000 to 33.85 J • C-MCRU (1979).) Graphite 0.990 0.991 Tissue equivalen 150A ( t ) 0.990 0.963 The laborious use of the Si-units for exposure (C kg" somn 1i ) e application n the e overcomca sb n e from the use of air kerma (unit Gy). The Nordic km =chamber material dependent factor correcting standards laboratories will be able to provide air for the lack of air equivalence of the ionization 60 chamber material. kerma calibration factors (NA-) at Co-y beams de- fine: dby correctioe Th n factor havm k s ed k atbeean t n dis- (6) cussed extensivel literaturee th n yi , recently e.gy .b ALMOND & SVENSSON (1977) and JOHANSSON et coll. (1977). where The symbol A with various indices is often used instead of katt and km; different authors giving dif- A"e centrn ionizatioa th alr f t .o ca e=kerm r ai n n i a chamber in the absence of the chamber at ferent meaning to the symbol. The factors recom- mended (Table 4) are those given by JOHANSSON the calibration radiation quality in Gy et coll. (1977). MC = meter reading at calibration corrected for absorbee Th d r ionizatiodosai o et n chamber fac- temperature, pressure humditr yo etcC n .i div. tor, NO, is derived from eqs (6) and (7) as (General re-combination corrections shoult no d be necessary to perform at the calibration in 60Co-y (8) beams wit typee hth f chamberso s recommenden di this protocol.) coulD N derivee ionizatioy db an r dfo n chambet rbu e valueth Table n onli sar y4 e vali r chamberfo d s described on p. 11. ND could be stated by national Derivation of absorbed dose ionization standards laboratories or be calculated at the hospi- chamber factor tals. If given by standards laboratories the factors kau and km must be clearly stated in the protocol. meae Th n absorbed dos airo et , £>air, r insidai e eth cavity of the ionization chamber has to be evaluated (N relates Di exposurn a o dt e calibration factor (Nv) through the formula fro observee mth r kermadai , Ks suggestea ai[ , ,if d in this report, the Bragg-Gray relation is to be used for determinatio f absorbeno d dos watero t e e Th . ) (9 , k — , following relation between £> ATd .an useds .i : air calr c where

~gk )' (7) a k, = 1.00 with N* in C kg-' C~l 14 where k,=2.58 10- C'R n .i wit) * hN attenuation and scattering factor, correcting for Absorbed dose determination at the attenuation and scattering in the ionization reference point chamber material at the calibration in the l photoal r nFo radiation beams with maximum 60 Co-y beam. l electroenergieal d an n s V radiatioabovMe 1 e n

155 Table 5 trance surface a large, r water phantom shoule b d

Recommended electronfor u p valuesair (s^ )und radiationu of use thao distance ds th t e will neve e lesb r s tha0 n5 at the reference point in a » ater phantom The absorbed dose mm The lomzation chamber should be protected maximum is assumed to be at the minimum reference depths during the water measurement by a tube with a wall given (s^ Tablein alrThe /u3 shall takenbe from Table doseit 7 maximum and therefore the reference point is situated at larger thickness of 1 mm manufactured from pohmethyl-

depths takene b than\ fromma u gi\enp e TableTablen i Th 3 . 5 methacrylate This tube should be attached to a criticall\not is it as dependent depththe on holder that can be adjusted for measurements at various depth e symmetrTh s chambeye axith f so r E, R* Ä* Minimum (Sv. air'u Pu must be positioned in the reference plane (MeV) (absorbed (lomzation reference dose measure depth For electron energies in the range 1 =££,,«; 10 MeV measure ment) (mm) the absorbed dose in the reference point should be ment) SSD=1 m measure solia n di d phanto plane-parallemA l lom- SSD=1 m (mm) zation chamber should be used (see supplement to mm be published) effective Th e poin measuremenf o t c\hndna r fo t c 1 3 3 2 1 144 __*** 2 7 7 4 1 137 - lomzation chamber is displaced from the centre of 3 12 12 6 1 122 - the chamber toward radiatioe sth n source (ÜLTREIX 4 16 16 8 1 108 - & DUTREIX 1966, HETTINGER et coll 1967) How- 5 21 21 10 1 097 - ever r electrofo , n radiation- hn y c centre e th ,th f eo 6 25 25 10 1 078 _ dnc chamber may be placed at the reference depth, 7 30 30 10 1 061 - as this is situated at a dose plateau or at least on - 8 34 34 10 1 048 a slow varyin e gdept th par f ho t lomzation curve 9 38 38 10 1 036 - 10 43 43 20 1 053 (0 975) r photoFo n radiation e chambeth , r centre shale b l placereference th t da e conveniencdeptho t e du , e 12 51 51 20 1 033 0980 14 60 59 20 1 018 0985 In this case correction factor e includear se th m d 16 68 67 20 I 006 0985 total perturbation factors belo ordewn i correco t r t 18 78 76 20 0 997 0990 for displacement 20 86 84 30 1 001 0 990 Measurements should be made for all combina- 22 94 92 30 0993 099> tion r irradiatioo s n condition honzontaA s r vero l - 25 107 104 30 0 981 0995 tical beam directio employee b y nma d With wedge 30 128 123 30 0965 0995 35 146 140 30 0952 0995 fields wedge edge th th f , eo e shoul placee db d paral- 40 163 154 30 0942 1 000 lel to the symmetry axis of the lomzation chamber The measurements should be made at the two pos- 45 30 0934 1 000 50 30 0930 1 000 sible 180° different onentations of the wedge and the average result should represent the absorbed dose * Values from BERGE t cole R l (1975 f energ) of wit t = cu A yh 15keV The Bragg-Gray equation is recommended for the ** Values from JOHANSSO t colNe l (1977 cylmdna r fo ) c ioniza- determination of the absorbed dose at the reference tion chamber with f diametetissue/wateo m m 5 r r equivalenr o t point in the water in the absence of the chamber at r (graphiteai ) equivalent material the user's radiation quality u Thusw D , . planA * e"* parallel lomzation chambe s recommendei r r fo d £,«10 VIeV u~*-' air)u 110) where beams with £0 above 10 MeV, the absorbed dose at the reference point shoul determinee db watera n di - £>air u =mean absorbed dose to air m the caviu of filled polymethylmethacrylate or polystyrene phan- the lomzation chamber measured in water witm to h outerx dimensionm 3 0. x t m leas a s3 0 t user'e ath t s radiation qualit\ G ym e thicknes Th phantoe th m f so 03 m walls oriented (•s« air)u=mass stopping power ratio, water to air at toward radiatioe sth n sourc r leso esm shoulm 5 e db the reference point at the user s radiation The water filling should be at least 0 25 m If the quality distance between the edge of the beam and the edg etota= l Pperturbatiou n factor including correc- of the phantom becomes less than 50 mm at the en- tion r lac sfo f wate ko r equivalence th n ei

156 Table 6 metry work. pu-factor r differenfo s t radiation beam Recommended photonfor p« values au ,radiationrand (s )u of at qualities and ionization chamber materials are given referencethe pointa water in phantom. variationsThe the of i n. (j 6 wTable .d air)an u s5 value - e founTa ar s n i d stopping-power ratios with depth depthsfor beyond absorbedthe ble 7. dose maximum consideredare negligiblebe to (NAHL'M 1975)

** symboe I nt th specifie ano „ , r)s (s l i u type th df stop eo - Radiation J itxJJ-axt (•Su alr)u* Pu graphite Pu water beam ping power ratio. Two different sets of stopping power quality ratios should strictly have been used, one for a chamber of air equivalent walls and another for a chamber of water equivalent walls. In the first case Harder's extended 6 1.97 "Co-y 1.150 0.970 0.990 Bragg-Gray cavity theory (HARDE e usedb R o 1965t , s i ) 4MV 1.84 1.145 0.970 0.990 which means s assumethai t i t d tha delta t equiliby ara - 6 1.71 1.140 0.980 0.990 rium exists in the air cavity due to the air equivalent 8 1.63 1.135 0.980 0.995 wall, (i.eenerge th . y carried int cavite oth delty yb a rays 10 1.59 1.125 0.985 0.995 is balance energy db y carriedelty b t a dou rays) airU )(5 u. 12 1.56 1.120 0.985 0.995 shoul collisionade th the e nb l mass stopping power ratio 14 1.54 1.115 0.985 0.995 water to air. In the second case, Spencer-Attix theory is 16 1.52 1.110 0.985 0.995 usede distributiob e o t Th . electroe th f no n fluence down 18 1.50 1.105 0.985 0.995 to a certain cut-off energy must then be known at the point 20 1.49 1.105 0.985 0.995 of measurement in the water phantom and the restricted 22 1.47 1.100 0.985 0.995 stopping powers shoul usee db r thi dfo s distributione Th . 25 1.46 1.095 0.990 0.995 cut-off energy is dependent on the size of the chamber. 30 1.45 1.090 0.990 0.995 However electron i , nseto beamf dattw o s e a th sdiffe r 35 1.44 1.080 0.990 0.995 with less than one per cent when using the mean electron 40 1.43 1.075 0.990 0.995 energy calculated according to BRAHME (1975) for deter- mination of the collision stopping power ratios in the 45 1.43 1.070 0.990 0.995 Bragg-Gray-Harder theor d whean y n using BERGEt e R 50 1.42 1.065 0.990 0.995 coll. (1975) electron fluence distribution to determine the * Values from ICRU (1969). mass stopping power rati Spencer-Attin oi x theory. Fur-

** pu-values from JOHANSSON et coll. (1977) for a cylindric thermore, experiment botn si h electro photod nan n beams ionization chamber with diamete. mm r5 wit r equivalenhai wated an t r equivalent chambers show thasame th t e stopping power data withir n pe abou e on t cent could be used for the two types of walls (JOHANSSOs t colle . 1977). Therefore r simplicityfo , f o t ,se onle yon ionization chamber materia e user'th t sa l (s<* a.r)u is recommended. The (sv air)u from BERGER et coll. radiation quality, perturbatio e fluth - f o n (1975 e recommendear ) electror dfo n radiatio thosd nan e ence due to the insertion of the air cavity from the ICRU (1969. Table A.3) for photon radiation. and location of the effective point of meas- urement of the cylindric chamber due to Illustrative example the curved ionization chamber wall; only for photon beams. Calibration at standards laboratory. The national standards laboratory has performed a calibration of the ionization chamber, whicdiametea s hha 5 f o r With the assumption that mm and a graphite wall of about 0.5 mm. A build-

„ D 3 f graphito calibratioe p uuses th pca t ewa da d nan

" Mc Mu the thicknes p togetheca f s wal0.4d o s wa an 5rl 2 the absorbed dose at the reference point in water is g-cm" e followinTh . g informatio e ionizath n o n- obtained from: tion chamber calibration factor e e giveth ar s n i n calibration certificate: r kermai e a Th calibration factor obtaine* N , r dfo £>w.,,=N,>Mup,,(swa,r)u (11) the ionization chambe 60e Co-th beae y n ri yth ra mt a where a d an m m laboratory 0 10 x fiela m t a d,m siz0 10 e focus-detecto : founs r be distanc wa o dt m l f eo Mu=meter reading at user's quality corrected for temperature, pressure, recombination, humid- ity etc.; in C or div. NK=1.10Gy/div. at 22.0°, 101.33 kPa This is the essential equation for practical dosi- and 50% rel. air humidity

157 Table 7 Recommendedd f depthan o \aluesl „„.;„ finita n (z (i i nu „j « o Depth (Sv. air/u mean energ\ al the phantom surface E„ jor election radiation mm The \alues takenare from BtKGEK (.oller (1975) nit/i energ\ cut- Mean energ phantot ya m surface £,,/MeV o//A = /5 keV H\\aten=7l 3 eV an5 d4 !(atr)=92 0 4 9 eV 5 3 0 3 25 50

Depth 1 ^ -A air'u 0944 0912 0907 mm 0 0931 0923 0917 Mean energy at phantom surface £,,/MeV 10 0959 0 945 0935 0926 0921 0917 20 0971 0956 0 944 0934 0928 0924 1 2 3 4 5 6 7 8 30 0981 0965 0952 0942 0934 0930 40 0992 0974 0960 0949 0940 0935 2 09 1 2 11 I1 6 13 1 1 074 058 1 043 1 031 1 019 50 1 003 0983 0 968 0956 0946 0 940 1 10 1 4 12 21 4 14 1 1 081 065 1 049 037 1 025 60 1 016 0993 0977 0963 0953 0946 4 1 151 1 137 1 112 1 090 072 1 056 042 1 031 70 1 030 1 004 0986 0971 0960 0 952 6 1 157 1 147 1 122 1 099 080 1 063 048 1 037 1 047 0995 0 979 0967 0958 8 1 154 1 132 1 108 088 1 070 055 1 042 80 016 90 1 065 030 1 006 0988 0974 0964 10 2 14 I 7 15 1 1 118 097 1 078 061 1 048 100 1 085 045 1 017 0997 0982 0971 12 1 150 1 129 106 1 086 068 1 055 110 1 112 062 1 030 1 006 0 991 0979 14 1 155 1 139 115 1 094 1 074 1 061 120 1 122 079 1 043 1 017 0999 0986 16 1 157 1 146 125 1 104 1 082 068 130 1 117 101 1 058 028 1 008 0994 18 1 151 134 1 112 1 091 074 140 1 105 113 1 073 041 1 018 002 20 1 155 141 1 121 1 100 082 160 1 099 105 1 103 068 1 040 019 25 1 156 153 1 141 1 120 102 180 1 094 1 101 094 1 064 038 30 1 154 1 151 1 137 123 200 1 088 094 1 088 062 35 1 152 1 148 139 220 1 081 1 088 082 40 147 240 1 083 1 075 085 45 146 260 1 072 1 072 280 1 065

e absorbeTh d r (insiddosai cavitye o et th e ) loniza- tion chamber facto , recommendeN„ r e presth n -i d

Depth t-^tt air'u ent protocol, is mm Mean energ phantot ya m surface £,,/MeV N= Akattkm(l-g) 9 10 12 14 16 18 20 22 N„ = l lOGy/div N0=l 075Gy/div. c kau0 =099 O 2 2 t a 0 99 0 0 2 00 I 1011 0 980 0 972 0965 0 958 0952 km1 =099 r humidireai l u 5 1 023 1 015 1 001 0 990 0981 0 974 0969 0962 g=0 004 2 01 1 7 02 1t 0 6 03 1 1 000 0990 0982 0 975 0 968 15 1 050 1 038 1 023 1 009 0998 0989 0982 0974 3 03 1 3 05 21 0 6 06 1 1 018 1 006 0997 0988 0 980 Measurements in an election beam (1) A depth 25 1 083 1 069 1 045 1 027 1 OH 1 004 0995 0 986 lomzation curv s measurei e a larg r defo beam size 30 1 103 1 087 1 058 1 037 1 022 1 Oil 1 001 0 993 t a SSD^l. n ordei o Odeterminm t r e meath e n 35 1 120 1 105 I 072 1 049 1 031 1 018 1 008 0999 energy of the electrons at the phantom surface. 6 08 1 2 12 41 0 8 13 1 1 060 I 041 1 025 1 015 1 005 £„. In the measurements the effective point of meas- 4 10 1 7 13 41 5 4 14 1 1 075 1 053 1 034 I 022 1 Oil s used i e uremendept) Th 17 .t whica h p e ( t th h 50 1 144 1 120 1 091 1 065 1 046 I 031 1 017 60 I 138 1 119 1 093 1 069 1 051 1 035 iomzations are reduced to 50 per cent (/?-,„) is deter- e correspondinth 3 m Fro m g mFi mine4 8 o gt d 70 1 135 1 117 1 093 1 072 1 055 80 1 127 1 114 094 1 073 £,,-value is obtained and £„=20 MeV 90 1 129 1 118 1 097 (2) Fro e deptmth h lomzation curv a depte - ab h 100 1 128 1 118 sorbed dose curv calculates ei d usin ,» lir i g)( u-factors 110 1 121 1 124 from Table 7 The depth of the maximum absorbed 120 1 10 e absorbe5 Th 1 11m 1 dm 0 dos3 dos s fount e ea b e wa o t d

158 this reference depth is then determined from a meas- way from electron beam parameters suc s enerha - urement wit e centre ionizatiohth th f eo n chamber gy, field distribue e shapsizd SSDth Th an ef .eo -

at this depth. Insertion of the meter reading, Mu, tion dependens i s larga n o et numbe f construco r - (corrected for temperature, pressure, recombination tional details of the accelerators and they are only

etc.) and pu- and Uw.air)u factors from Table 5 in eq. partly contained in the beam parameters. Therefore, (KJ) gives the absorbed dose in water at the refer- as a rule, the distributions should be determined ence point: for each accelerator. When accelerator same th f eso design are used (SvENSSON 1971), common beam axis depth dose distribution appliee - b de y y db sma ND=1.075Gy/div. w.uy = G 1.05u M 9 partments only afte checa r f somko e distributions pu=0.990 by measurements. Significant difference- ap y ma s pearesula s ra f individua o t l adjustment smald an s l Measurements in a photon beam (1). The photon difference n thicknesi s f acceleratoo s r window, beam quality was estimated from the ratio JiooUzoo, foils, and in collimator design etc. whic 1.51s hwa . This corresponds roughl maxia o yt - The relative depth absorbed dose distributions mum photo accordinV n M energ 7 1 f Tablo gyt o e6 coul measuree db d with ionization chambers, semi- or Fig. 4. The reference depth is then obtained from conductor detectors, liquid-ionization chambers or absorbee Th . dmm 0 dos Tabl10 t thi ea s a s e3 dept h ferrous-sulphate dosemeters choice Th . f methoeo d is measured wit centre ionizatioe hth th f eo n cham- depends on the instruments that are locally avail- e mete t th thia s i sr u pointreadinbe M f I . g (cor- ablee relativTh . e distributions shoul e checkeb d d rected for temperature, pressure, recombination against depth absorbed dose curves measured with Tabl d . (11etc.an eq ) giv)e 6 e an ionization chamber metho r possiblyo d , when available, ferrous-sulphate dosemeters. The ionization chamber method is well estab- N0=1.07y 5G lished for measurements at depths equal to or larger Dw,u=1.173MuGy pu=0.985 than that of the dose maximum. In the measure- (*w.alr)u= 1-108 ment f relativo s e depth ionization curve e disth s - placement effect of the ionization chamber should absorbee (2Th ) d dos t dosea e maximu mdeters i - be taken into account for cylindric chambers. This mined frodepte ratie th m th f hoo ionization0 10 t a - effect should be corrected for by using an effective dosmd man e maximum depte Th . h ionization curve point of measurement. This point has been deter- is used for evaluation of this ratio. (The effective mined by extrapolating the geometric displacement poin f measuremento t , 0.7 , shoul5/• e useb d n i d e deptth f ho ionization curves, measure y difb d- measuring depth ionization curves.) ferent size f cylindrio s c chamber a zer o t os size chamber experimentae th n I . l determinatio pere nth - Determination of absorbed dose at any point turbatio t consideredn no effec s wa t thio s ,autos si - Relative absorbed dose distributions should be e effectivth maticall f o e us y e correcteth n i r dfo related to the absorbed dose at the reference point, poin f measuremento t e effectivTh . e poin f measo t - which should therefore be included in all distribution urement varies slightly with the electron energy determinations e distributioTh . n should appla o yt £p.o and phantom depth and is 0.5 r to 0.75 r in front large water phantom (page 14)completA . f o t ese of the chamber centre, where r is the radius (HET- distributions shoul e availablb dl combinaal r fo e - TINGE t collRe . 1967, DUTREI DUTREIX& X 1966, tion energyf so , field sizes, SSD, e etcus . n i tha e ar t JOHANSSON et coll. 1977). A value of 0.5 r is recom- for radiation therapy. The hospital physicist is re- mende r electrodfo n radiation e recombinatioTh . n sponsible for ajl modifications of these distributions e disregardeb losse n e measuremenca s th n i d f o t in clinical practice instancr fo , insertioe eth f leano d relative depth ionization curve thosr sfo e chambers block and bolus. recommended in the present protocol for most treat- ment units e relativTh . e depth ionization curves Beam axis absorbed dose distribution should be multiplied with (sw.air)u (Table 7) for dif- Electron beams. The beam axis depth absorbed ferent dept orden hi convero rt t these curve relao st - dose distribution cannot be specified in a unique tive depth absorbed dose curves.

159 SSO» E o t 2 3 in Q oo Q: SSD 100cm u! O Z uj er cr SSD 120cm o C3 i- O D a LU u. < oc 10 20 30 40 LU I Fi 7 Dosg e gradients r largfo e, C ,fiel d sizea functio s a s f o n the most probable energy at the phantom surface, £„ 0 The SSD= l m if not otherwise stated Experimental points are indicated with different symbols for different accelerators The upper two 20 30 40 curve e theoretiar s c data from BERGE SELTZE& R R (1969e th ) SSD= l m curve is derived from inverse square law corrections £Tpi0/MeV

Fig 6 The therapeutic range Ä8o for large field sizes as a func- e mosth tio f t o nprobabl e energe phantoth t a y m surfac0 p £ e of view s importani t i , defino t t treatmene th e t vol- The SSD=1 m if not otherwise stated Experimental points are indicated with different symbols for different accelerators The umrelevana m e consistand an t t way t leas,no o t t upper two curves are theoretic data from BERGER & SELTZER simplify comparisons between different treatment (1969), the SSD=1 m curve is derived from inverse square law corrections Near surface, line e obtainear s r thosfo d e beams centres' with£>s/Dm<0 85 The parameters that are recommended for use ap-

pear in Fig 2 Dm the maximum absorbed dose along At small phantom depths the air icmization meth- the beam axis, Ds the surface absorbed dose at 0 5 mighd o t introduce uncertaintie contaminao t e du s - mm depth (this depth has been chosen as it is ac- tion of low energy electrons and an incomplete cessibl r accuratfo e e absorbed dose measurement build-u 5-raf po y spectru measurementf mI t sucsa h and as it approximately corresponds to the radiation depths are desired a liquid lomzation chamber (HUL sensitive layer below the epidermis). D^ the photon TEN & SVENSSON 1975), or thin ferrous sulphate background absorbee th G , d dose gradient, Re ir)0th dosemeters (SVENSSON & HETTINGER 1967) could depth of the absorbed dose maximum, R^ the thera- be recommended Since, in general, it is only neces- peutic range, Rw the half value depth and Rp the sary to make these measurements in the calibration practical range procedure after an accelerator installation, joint Of particular importanc electron a r efo n beae mar measurement differeny sb t department e recomar s - G Experimenta d /?an 8c, d theoretian l c valuer fo s mended broad beams are given in Figs 6 and 7 A dose- oftes i t I n usefu investigato t l therapeutie eth d can gradient below r larg aboufo 5 e 2 beamt s indicates physical propertie electron a f so n bea describd man e that the scattering system and collimating svstem the somy mb e simple parameter Ther e severaear l f pooo e r ar desig d thanan t unnecessary large vol- reasons for introducing such parameters (BRAHME ume f normao s l tissu e irradiateear singln di e beam & SVENSSON 1976), thus: 'the increasing number technique f electroo n accelerator f differenso t type ofted san n Photon beams The beam axis depth absorbed quite different beam qualities necessitates a simple dose curves are less critically dependent on the unified comparison of the quality of one beam with beam parameters and simpler to measure than for another; the desirability of simple and accurate electron radiation. All the dosemeter systems men- beam diagnostics mak t usefui e focuo t l s attention tioned for electrons can be used but should be on a few independent parameters characterizing the checked againsr lomzatioai e th t n metho e difTh -d beam quality d finallyan , , fro ma therapeuti c point ference betwee relative th n e depth absorbed dose

160 O 3O 0 25 50 0 1020 0 T 0 15 100 50 DEPTH INWATER/inm

. Bea8 Fig. m axis depth absorbed dose distributio r photofo n n distribution are indicated. D,aJDtM"'Ju»IJtm which is input para- beams. Parameters often use characterizo dt qualite e eth th f yo meter for (s„ air)c in Table 6.

and depth ionization curves, when bot e normahar - both photo d electroan n n radiation beams. This lized at maximum, may be 1 to 2 per cent at a large metho simpls isodosede i th s e a directle sar y plotted depth (SvENSSON 1971, NAHUM 1975). These differ- and corrections are often not necessary to carry out. disregardee enceb n sca practicar dfo l dosimetryn I . spatiae Th l resolutio sensitive goos ni th s da e layer the measurement of depth ionization the displace- of the detector is less than a few mm'-. Systematic ment effect mus e considereb t e effectivth d an de errors could, however e introduceb , r somdfo - eac point of measurement must be used. The effective celerators, especially for betatrons, dependent on poin f measuremeno t t varies slightly with energy the radiation pulse shap d neutroan e n contamina- d phantoan m depth (HETHNGE t collRe - . Jo 1967, tion. Furthermore e curveth , s measured wite th h HANSSON et coll. 1977). A value of 0.75 r is recom- semi-conductor may differ from the relative isodose mended for all energies and phantom depths. The curve t smalsa l phantom depths (BRAHM SVENSE& - variations can be disregarded in practical dosimetry. SON 1976). The method should, therefore, be Published depth dose data for different peak ener- checked against ionization chamber measurements giee availablsar differenr efo t accelerators. Those or possibly, when available, ferrous-sulphate dose- data shoul checkee db measurementy db w fe a f o s meters. distributions both'at small and large field sizes. The absorbed dose of electron beams at points Parameters describing the physical and thera- outside the beam axis may be assessed by means of peutic propertie beae th mf o s axis absorbed dose photographic film placed paralle beae th mo t l axin si distributions are also useful for photon radiation. polystyrene phantoms significanA . t differenc- be e e define r selectro »ar ,ooR fo R , , s m a d D n , s radiaD - tween the relative depth absorbed dose curve and tion (Fig. 8). The ratio Jiuo/Aoo is discussed on page the relative depth blackening curve exists at depths 8 and is of importance for the choice of stopping smalle (LOEViNGErm tham 0 n2 t collRe . 1961. MET- power ratios. TINGER & SvENSSON 1967). The beam axis depth absorbed dose curve is first .measured and is then Iso-absorbed dose distributions used to assign a depth absorbed dose value to all A semi-conductor detector connected to an auto- points along the beam axis in the film. Isodensity matic recorder may be used for the absorbed dose curves joining points in the film with the same net distribution determination in a water phantom for blackenin assignee gar depte th o hdt absorbed dose

161 Table 8 ut u intiiiitenuncr ;iri>-jrnni tor accelerator* ami ""C.\;-y nniis

Checf ko Frequency of check

Once Once Once a Once a Once a day a week month quarter a > ear

Light bead man p. 20 pointers Radialion bea d lighman t p. 20 ""Co beam agreement fig. 5 ace. All mechanical p. 20 alignments H PA (19701 AAPMI1975) Abs. done monito 1 d patien2 . an rp t ""Co dose agreement ace. Abs. dose monitor calibr. p. 21 ace. ""Co factor constancy Abs. ilose monitor calibr. p. 21 ace. ace. factor (in)dependencf eo diff. param. 1 2 Energ . p y constancy Radiation beam1 uniformit2 . p y acc. •'"Co

at the point where they pass the beam axis. It is checking procedures prescribed by the manufactur- frequently sufficient 10 construct the isodensity r shoule followede db . curves without correcting for background blacken- e responsiblTh e physicist shoul r eacdfo h therapy ing.- unit write instructions on how to carry out the The same method for photon beams as for elec- relevant check theid san r frequencies logbooA . r kfo tron beams may be employed although the accuracy recording these measurements shall be kept. of .this method in the penumbra region is less satis- factory e filmTh . metho oftes di n less accurate than Radiation beam alignment checks measurements with semi-conductor detectors- An . A simple check on the light beam should be car- other approach is to use transversal measurements ried out daily. A white card on which is drawn a depth4 t a s wit ionization a h n chamber (decrement square fiel s placee i normad th t da l SSD. \Vite us h line method; ORCHARD 1964. ORR et coll. 1964) fol -numericae th f o l field size indicato correspondinra g lowe computey db r calculatio isodose th f no e curves field size is set up and the light field is compared (KALN/E SMuN& K 1972). with the drawing. Without moving the card this com- parison is again performed after the radiation head Maintenance program for the dosimetry is rotated through 180° t shalI . e checkeb l d thae th t f therapo y units cross-hair ligh e front imagth td pointeean r indicate e dosimetrTh y data whicn o , irradiatione hth e sar the centre of the light field and that, the cross-hair is based, shal checkee b l d regularl constancyr yfo e Th . projecte bace th kn dpointeo r tip. numbe checkf ro depeny sma somo dt e extene th n o t Check f agreemenso t betwee lighe nth t bead man behaviou e particulath f o r r therap- in s yit unid an t . the radiation beam should be performed even, week tended use. If previous examinations indicate few and each time the light beam bulb is exchanged. It and slow changes some decreas thein ei r frequency is often convenien combino t t e this check with that may be satisfactory. A maintenance program for of the radiation beam uniformity. The agreement ""Co-y unit acceleratord san suggestes si Tabln di . e8 should fulfil the values given in Geometric consid- wher frequencies.are eth e assumption e giveth n no , erations (page 10). that dual absorbed dose monitoring (page 21). Once a year a thorough alignment test should be exist thad san t measurement f absorbeo s d dosen so performed. Detailed informatio n relevano n t pro- patient e performear s d (page l technica22)Al . l cedure s beesha n given (HPA 1970. AAPM 1975).

162 Absorbed dose monitor checks between measurements. In some irradiation geo- Whenever performed the measurements of ab- metrie shoulD SS - t possiblse din thino th s i sd ean sorbed doses on patients should be checked for stead be kept constant. The ratios. JJJ». should be agreement with the absorbed dose monitor. related to the relevant energy calibrations, and the On accelerators the constancy of the absorbed plastic slabs should be marked and used for this pur- dose monitor calibration shoul checkee db d weekly. pose only. It shal possible b l relato t e e this e prichecth -o kt e ratioTh s JJJ» shoul t deviatdno mory eb e than mary absorbed dose calibration of the monitor. A ±1 per cent from the original ratios for photon special phantom made of plastic should be used be- beams. For electron beams the deviation should be cause of the convenience of handling. The position less than ±4 per cent. of the dosemeter should be close to the reference depth (Table 3). As several different reference Radiation beam uniformity checks depths mighf interesto e b tphanto e th , cony m-ma uniformite Th y shoul checkee db d wit photoe hth - basia sis f o tc block together wit serieha f slabso s graphic film method (page 10)n eacI . h chece th k marked and used for this purpose only. Monthly to maximum blackenin blackeninge th file d mth an f go - quarterly a suitable series of such measurements along the major axes and diagonals of the field should be performed for testing the monitor preci- should at least be determined. A full evaluation of sio stabilitd examinatior nan fo d yan calibrae th f no - the film blackening is of great value as the uniform- tion factor r independencfo s n monitoo e r setting, ity index then may be determined. The check should absorbed dose rate, beam direction, temperature, be made weekly with cyclic permutation of some r pressureai d an . Als e dependencoth calie th -f eo relevant irradiation conditions (e.g. radiation qual- bration factor on wedges and field size, flattening ity, beam direction and field size), i.e. each com- filte r scatterino r g foils shoul e checkedb r condfo - binatio checkes ni t leasda t every month e miniTh . - stancy. mum requirements e sectiogiveth n i nn Geometric On 60Co-y unit e absorbechece th th s f ko d dose considerations should be fulfilled in all uniformity monitor calibration may be less frequent but at least measurements. once a month. The check reveals timer errors, changes in 'shutter effects' and possible changes in Checks of absorbed dose given to the patient absorbed dose rate caused by, for instance, redis- tributio source th f no e (HANSEN 1972). absorbee Th d dose give eaco nt h patient shale b l The ratio between the monitor reading and the under proper control (ICRP 1970, LlNDELL 1976. determined absorbed dose value shall not deviate by ICRU 1976). For this purpose dual absorbed dose more than ±2 per cent from the ratio determined at monitoring systems and measurements of the ab- originae th l measurements. sorbed dos patientn eo recommendede sar duae Th .l monitoring system shall protect the patient against Radiation energy constancy checks overdoses caused by equipment failures. The pa- n therapO y units which could hav n unintena e - tient dose measurements should detec erroney an t - tional change in the selected radiation energy (i.e. ous absorbed dose caused by equipment malfunc- betatrons, linear accelerators) the energy constancy tion humad san n mistake thao ss t proper corrections shoul checkee db d onc eweeka . Thi performes si d in the following treatments can be performed. by checking the constancy of a ratio, JJJ2, between ionization measurements at two different depths. Absorbed dose monitoring systems e phantoTh r checmfo k measurement f absorbeso d Malfunctioning of 60Co-y unit timers have been dose monitor calibration should be used and Ji is reported (VELKLEY 1975). Also mechanical mal- the measuremen reference th t a t e depth meass i 2 .J - function e beath mn i s control system (sticking ured with an additional slab plastic material in front shutter, broken return spring, etc.) have cause- dex of the phantom. For photon beams this slab should cessiv unknowd ean n absorbed dose patientso st t I . be approximately 10 cm thick and for electron is recommende provido dt e 60Co-y unit- sin wito htw beams about R50 minus the reference depth (Fig. 2, dependent timer systems both capabl givo et terea - Table 3). The best geometric reproducibility is ob- mination signal to the beam control system. Detailed tained if the source chamber distance is unaltered recommendation e givear s n Radiotherapi n - Ap y

163 paratus Safety Medical Panel (RASMP 1975). Dua e lnumbeth f o f occasionao r l operator mistakef i s timer systems coping with these recommendations level one measurements are correlated to a 'select commercialle ar y available. and confirm' system. Occasional changes in patient Accelerators shal e provideb l d wito indetw h - positionin occasionad gan l equipment failures could, pendent absorbed dose monitoring systems whico ht however, be revealed only by level two dosimetry. advantage should have physically separated radia- On older radiation units with only one dose monitor tion detectors t lease A detecto. on t r system shall system leve measuremento tw l alsy osma replacea consis transmissioa f o t n chambe measurd an r e eth secondary dose monitor thorougA . h discussiof no full e patienbeath t m a flatteniny t an sid f eo g filter possible errors and control of the absorbed dose to or scattering foils. Both monitors shall be capable of e patienth r specififo t c therapy procedure s givei s n independently terminating the irradiation. The in- by MÖLLER et coll. (1976). tegrated signals from the detectors should be digital- Patient dosimetry system e useb do t s routinely ly displayed on the console and at least one monitor should besides reasonable precision possess simplic- should start from beginnin e zerth t oirradiaa n a f go - ity of handling. The demand for precision is deter- tion e readingTh . t leas a displae f so on t y instrument mined by an action level for open beams of ±3 per should be preserved in the event of any failure (in- cent r beamFo . s modifie a wedg y b dr compen o e - cluding power failure r interruptioo ) irradiae th f no - sating or blocking filter an action level of ±5 per tion, ft should not be possible to start another treat- cent should be used. At least small condenser ment befor e dosth e e monitor presettinge th d an s s ionization chambers (Sievert chambers), thermo- are reset. The absorbed dose rate shall be indicated luminescent dosemeters (TLD) and small semi- r eacconsole fo th hn d o incremenean dose th ef o t conductor detectors with suitable (partial) build-up monitor readings an acoustic beat should be given. caps can fulfil these requirements. dose Ith f e rate exceed certaia s n preset level (e.g. twice the normal dose rate), automatic termination Appendix e irradiatioth f o n should result. Fro e radiatiomth n For a proper understanding of the protocol some detectors signals shoul derivede db , whic e prohar - definition e necessaryar s , taken from ICRU (1976), portional to the output in different parts of the radia- (1970A NACd HP an ) P (1972) r slightlo , y modified. tion beam, so that the beam uniformity can be de- Beam: The electron or photon beam is the region tected. An abnormal uniformity should result in an in space traverse photony db r electronso s froe mth automatic termination of the irradiation. For a given source. Its edges are determined by the collimator, radiation qualit e dependencyth dose th ef eo moni - its cross sections perpendicular to the beam axis is r calibratioto n facto dosn o r e rate, beam direction, the field and its direction is that of photon or elec- temperature r pressurai d an , e shoul withie db r pe n2 tron travel. cent. The dependence on beam energy, field size, Beam axis: Four types of beam axes can be de- flattenind an g filte r scatterino r g foil shoul e lesdb s fineda properl n I . y adjusted syste l foumal r axes r centpe tha0 . n±3 will coincide definitione Th . s are: (1) Mechanical definition: The collimator rotation Absorbed dose measurements on patients axis is defined as the rotational axis at the collimator Absorbed dose measurements on patients could head. e divideb d o intleveltw of security o s r 'leveFo . l (2) Geometric definition e geometricTh : beam , measurement e e firson th tf o e e madon ar s t a e axis is defined as the line passing through the centre treatment occasion everd san y tim parameteea r (in- e beaoth f m flattenin e gmai th filte r n (o scatterinr g cluding patient anatomy s changedi ) . This enables foir focuo l f scannino s g magnet e systemth d an ) detectio f systematino c mistake e decideth n i s- ir d centrfinae th f l eo bea m limiting diaphragms. radiation procedure. 'Level two' measuremente sar (3) Radiation definition: The radiation beam axis made at every treatment occasion enabling detection (sometimes named reference axis defines i e ) th s a d of occasional operator mistake d equipmenan s t line passing through the centre of the effective radia- failures. tio ne centrsourcth f gravitd e areo e an th e af o y Preferably level one measurements should be car- within which the absorbed dose exceeds 50 per cent morn i riet e dou tha e fielde pointh non furf A .o t - of the maximum absorbed dose at the reference ther improvement may be obtained in the reduction plane in a phantom.

164 (4) Light beam definition lighte th : beam axiss i proposed treatment distance. The light field size is defined as the line from the effective light source the area inside the 50 per cent boundary of the light and the centre of gravity of the area within which the intensity; the light intensity in the centre being 100 light intensity exceede maximu r centh f pe o t0 s5 m r cent e numericape Th . l valuefiele th df so siz e ear light intensit phantoe th t ya m surface. e distancgiveth s a n e betwee e boundarnth e th f yo Reference plane: The reference plane is defined major axes. e orthogonath s a l e referencplanth o t e e a axi t a s Uniformity index: The uniformity index is defined given depth beneath d parallee phantoan th , , to l m e referencith n e plana specifie r fo e d quantity (e.g. surface. Recommended values for the depth are absorbed dose, ionization t filne m, densit r curo y - give Tabln ni . e3 rent from a semi-conductor detector) as the ratio of Reference point: e referencTh e poin s definei t d the area containing points where this quantit- ex y as the point of the inter-section between the refer- reference valus r cenit th ceed f t pe e a o t 0 s9 e point ence plane and the beam axis (reference axis). e areth a d wheran e t exceed i er th cen f pe o t 0 5 s Radiation field size: The field size is defined in reference point value. a phantom at the depth of the reference plane, with Physical penumbra: Physical penumbra is for a that plane at the proposed treatment distance. The specified quantit laterae th s ya l distanc majoe th t ea r field size is the area inside the 50 per cent leve l r cenof pe o t0 2 axee th r censd betweepe an t 0 8 e nth the absorbed dose in the reference point. The nu- points of this quantity with the value at the reference merical e valuefielth df o e ssize giveth ar e s a n point defined as 100 per cent. distance between the 50 per cent level at the edges e r majooth pe f 0 r e diamete5 axes th e r th o ,f o r cent leve circulaa n i l r field. Reprint e obtaineb y ma s d fro . LindborgmL . National Light field site:e lighTh t field siz s definei e t a d Institute of Radiation Protection. Box 60204, S-10401 the surface of a phantom, with the surface at the Stockholm. Sweden.

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167 LIS PARTICIPANTF TO S

ARGENTINA

Gonzalez, R. Division Dosimetria, Direction Radioisotope sRadiacioncsy , Comisiôn Nacional de Energia Atômica, Avenida del Libertador 8250, 1429-Buenos Aires

BELGIUM

Wambersie, A. Faculté de Médecine, Université catholiqu Louvaie ed n Tour Claude Bernard, U.C.L. 54.69, Avenue Hippocrat , B-120e54 0 Bruxelles

FRANCE

Simoen, J.P. Laboratoire de métrologie des rayonnements ionisants, Boîte Postal, e2 F-91190 Gif-sur-Yvette

GERMANY. FEDERAL REPUBLIC OF

Feist . H , Physikalisch-Technische Bundesanstalt, Bundesallee 100, D-3300 Braunschweig

INDIA

Subrahmanian . G , Divisio f Radiologicano l Protection, Bhabha Atomic Research Centre, Trombay, Bombay 400 085

NIGERIA

Fregcne, A.O. Departmen f Radiatioo t n Biolog Radiotherapyd yan , Lagos University, Private Mail Bag 12003, Lagos

SWEDEN

Johansson, K.A. Radiation Physics Department, Universit Göteborgf yo , S-41 Götebor5 34 g

169 UNITED STATES OF AMERICA

Bjärngard, B.E. Divisio Physicf no Engineeringd san , Havard Medical School, Binne4 4 y Street, Boston, Massachusetts 02115

Ehrlich, M. Radiation Physics Division, Center for Radiation Research, National Bureau of Standards, Washington, D.C. 20234

Morton, R. Bureau of Radiological Health, 5600 Fishers Lane (HFX-70), Rockville, Maryland 20857

UNIO SOVIEF NO T SOCIALIST REPUBLICS

Bregadze . Y , All-Union Research Institut f Physicotechnicaeo l and Radiotechnical Measurements, USSR State Standard (Gosstandart), Leninsky prospek , 117049 t 9 Moscow

WORLD HEALTH ORGANIZATION

Racoveanu . ,N Radiation Medicine, World Health Organization, CH-1211 Genev , Switzerlana27 d

OBSERVER

Duftschmidt . K , Österreichisches Forschungszentrum Seibersdorf Ges.m.b.H., Institut für Strahlenschutz, Lenaugass , A-10810 e 2 Vienna, Austria

INTERNATIONAL ATOMIC ENERGY AGENCY

Eisenlohr, H.H. Girzikowsky. R , Haider. J , Johansson, L. Nam, J.W. Rüden, B.-I.(scientific secretary) Ryabukhin. Y , Waldeskog, B.

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