Preparation and Modification of Thin Carbon Films
by
Callie Reynolds Massey-Reed Fairman
A thesis presented in fulfilment Of the requirements for the degree of Doctor of Philosophy
School of Chemistry The University of New South Wales Sydney, Australia
2010
CERTIFICATE OF ORIGINALITY
‘I hereby declare that this submission is my own work and to the best of my knowledge it contains no materials previously published or written by another person, or substantial proportions of material which have been accepted for the award of any other degree or diploma at UNSW or any other educational institution, except where due acknowledgement is made in the thesis. Any contribution made to the research by others, with whom I have worked at UNSW or elsewhere, is explicitly acknowledged in the thesis. I also declare that the intellectual content of this thesis is the product of my own work, except to the extent that assistance from others in the project’s design and conception or in style, presentation and linguistic expression is acknowledged.’
Signature ……………………………….
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COPYRIGHT AND DAI STATEMENT
‘I hereby grant the University of New South Wales or its agents the right to archive and to make available my thesis or dissertation in whole or part in the University libraries in all forms of media, now or here after known, subject to the provisions of the Copyright Act 1968. I retain all proprietary rights, such as patent rights. I also retain the right to use in future works (such as articles or books) all or part of this thesis or dissertation.
I authorise University Microfilms to use the 350 word abstract of my thesis in Dissertation Abstracts International.
I have either used no substantial portions of copyright material in my thesis or I have obtained permission to use copyright material; where permission has not been granted I have applied/will apply for a partial restriction of the digital copy of my thesis or dissertation.’
SIGNATURE: ……………………………….
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ACKNOWLEDGEMENTS
I am very grateful for the help I have received through out my PhD., not just from my supervisors and group members but from the school of chemistry, my friends, and most importantly my family.
Firstly I would like to thank my supervisors Justin and Brynn, for not only allowing me to undertake a PhD with them, but also for their guidance and support through out my studies. They have given me opportunities that I am grateful for. I especially would like to thank Justin, for his patience, and helping me to grow as a chemist and a researcher.
I would also like to thank the members of the biosensors and biodevices group, both past and present. You have all helped me grow as a researcher, ideas and thought’s are all appreciated. In particular I would like to thank Gouzhen Liu for helping me when I first started with the group, for putting up with constantly asking which wires were which. For Michael Jones, Paul Eggers and Paulo Da Silva for your guidance in all things synthetic. Michael and Paulo, I followed you from honours to my PhD, I enjoyed our coffee breaks, and the endless jokes. In particular from the echem group, Kate, Leo, Pauline, Lyn, Steven Yannolatuos, Josh P., Guozhen, Alicia, Kris, Till, and Erwann, I have had fun working you. The electrochem lab never seemed brighter! Kate, thank you for all your help, fun and guidance in the lab.
Thank you to all the staff in chemistry, you have all made my student life at UNSW such a great experience. From Ian and Paul down in the store and work shop to Anne in the office and all the academic staff. A special thanks goes to SOCS past and present, thank you for the fun nights, the Friday night drinks, the balls, and the general tom foolery had.
For the five weeks that I spent in Paris at ITODYS, Paris 7 university, thank you for letting me work with you, I had so much fun and learnt some very handy new skills. Thank you Michel Delamar, Vincent Noël, and Greg Marche.
I don’t think I wouldn’t have made it so far with all the ups and downs with out my friends. Kate, Leo, Nick P., Kasey, Sam, Sabrina, Paulo, Doug, Maggie, Pauline, Steven R.D.G., Matt, Bin, Oanh, Alisdair, Honman, Erica, Yeng, Sandra, Brad, Jason and Jason, Laurent, Michael, Trung, Lyn, Guozhen, Tom and all the lunch time people. You have listened to endless accounts of broken machinery, and missing parts. It has have been great fun to hang out with both in chemistry and outside as well. My friends out side of chemistry have also been
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a great support, Ken, Jane, Nick, Nep, Heidi, Liti, Simi, Emily, and all my church family. A special thanks goes to Samantha Furfari and Kasey Wood, thank you for the girl’s nights out, the coffees and lunches.
A special thanks goes to Kate, you have been such a great friend. You have put up with my ups and downs, helped me with problems, read my thesis with gigantic sentences. I am glad that I under took my PhD. just to have found such a great friend. One day we will write that book on indoor tents.
My family, you have supported me through out my studies. Mum, thank you for proof reading my thesis, thank you for the dinners and shopping trips, the early morning phone calls. Mum, Dad and Sean your support through out my PhD. is heartfelt, thank you for believing in me, and for your wisdom and guidance through out all my life. Thank you goes to Jeff’s family as well, for their support and love. Jeff, my wonderful, fantastic, husband; you have supported me emotionally and financially. I promise this is it, no more study, well not for a very long time. You have kept me grounded, you have put up with my early morning starts of 5 am in the lab, the late night finishes, the Saturdays in the lab, and the odd Sunday, the running late for dinners, and the lack of a wife for the last two months. You have even been there to help me empty tubs of water, when our lab was flooding on a weekend. Words are not enough.
Finally, I need to thank Teflon tape, rubber bungs and God. My PhD. would not have function with out any of these.
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ABSTRACT
Thin carbon films, in the form of pyrolysed photoresist films (PPF), are being increasingly used for electrochemical devices. This research investigates the preparation and subsequent modification of PPF through both the electrochemical reduction of aryl diazonium salts and through the UV attachment of alkenes to the iodinated surface.
The pyrolysis of photoresist films produces PPF that is a smooth (rms < 0.5 nm), amorphous carbon film that can be used for further electrochemical studies. The pyrolysis method was investigated to see the affect of holding the pyrolysis at three different temperatures during the pyrolysis and the corresponding times for which they were held; the effect of gas flow on the PPF was also addressed. It was seen that the gas flow whilst not affecting the roughness of the surfaces, the electrochemical cleanliness towards ferricyanide was affected, whilst different temperatures during the pyrolysis and the length of time they held was also seen to have some affect on both the electrochemical performance as well.
The modification of PPF was carried out with aryl diazonium derivatives of oligo(ethylene glycols) (OEGs). The protein resistance of these modified surfaces were also investigated and compared to the equivalent gold modified surfaces, both the effect of the chain length of the OEG as well as the change in hydrophilicity of the distal end was investigated. For a comparison OEG thiol modified gold surfaces were used. A Fluorescein isothiocyanate labelled protein, bovine serum albumin, was used and two methods employed to study the protein resistance. These methods were the elution of adsorbed protein from surface and the measurement of the protein whilst on the surface using fluorescence microscopy.
The use of iodine plasma to modify the PPF produces a surface similar to that of both hydrosilysed silicon and hydrogenated diamond surfaces. The use of UV light at 514 nm to activate the surface and attach alkenes was employed. UV addition of alkenes to the surface allows patterning as was observed via the modification of the iodinated carbon film with undec-10-enyl-2,2,2-trifluoroethanethioate on areas exposed
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to light and the deprotection of the thiol which was then exposed to gold nano particles and surface patterning was investigated with SEM. This will allow the production of nanoarray sensors in the future.
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LIST OF PUBLICATIONS
C. Fairman, S.S.C. Yu, G. Liu, A.J. Downard, D.B. Hibbert, and J.J. Gooding, 2008, Exploration of Variables in the Fabrication of Pyrolysed Photoresist, Journal of Solid State Electrochemistry 12: 1357-1365.
C. Fairman, G. Liu, D.B. Hibbert, J.J. Gooding, 2011, Comparing the electrochemical performance of pyrolysed photoresist film electrodes to glassy carbon electrodes for sensing applications, ICONN 2010 proceedings, accepted.
J. S. Quinton, A. Deslandes, A. Barlow, J.G. Shapter, C. Fairman, J.J. Gooding, and D.B. Hibbert, 2008, RF Plasma Functionalized Carbon Surfaces for Supporting Sensor Architectures, Current Applied Physics 8: 376-379.
A. Deslandes, M. Jasieniak, M. Ionescu, J.G. Shapter, C. Fairman, J.J. Gooding, D.B. Hibbert, and J.S. Quinton, ToF-SIMS PCA characterisation of methane and hydrogen plasma modified HOPG, Surface and Interface Analysis, in press.
S. M. Khor, G. Liu, C. Fairman, S. G. Iyengar, J. J. Gooding, 2010, The Importance of Interfacial Design for the Sensitivity of A Label-Free Electrochemical Immuno-Biosensor for Small Organic Molecules, Biosensors and Bioelectronics, in press.
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TABLE OF CONTENTS
Title Page...... i Certificate of Originality ...... ii Copyright and DAI Statement ...... iii Acknowledgements ...... iv Abstract...... vi Publications...... viii Table of Contents ...... ix List of Abbreviations...... xvi
CHAPTER ONE – GENERAL INTRODUCTION
1.1 INTRODUCTION...... 2
1.2 BIOSENSORS ...... 3
1.2.1 TRANSDUCERS...... 4
1.2.1 CATALYTIC BIOSENSORS...... 5
1.2.2 AFFINITY SENSORS...... 8
1.3 FACTORS IMPORTANT FOR AFFINITY BIOSENSORS ...... 12
1.3.1 ELECTRODE SURFACE STRUCTURE...... 12
1.3.2 BIOSENSING INTERFACE ...... 14 1.3.2.1 Protein Resistance ...... 15 1.3.2.2 Binding of the Affinity Biosensor Interface...... 17
1.3 CARBON AS AN ELECTRODE MATERIAL ...... 19
1.3.1 CARBON PASTE ...... 19
1.3.2 HIGHLY ORDERED PYROLYTIC GRAPHITE ...... 19
1.3.3 DIAMOND-LIKE CARBON...... 22
1.3.4 HYDROGENATED AMORPHOUS CARBON...... 23
1.3.5 GLASSY CARBON ...... 24
1.3.5 THIN CARBON FILMS ...... 26
1.4 MODIFICATION OF CARBON ...... 28
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1.4.1 POLYMERS AND MEMBRANES ...... 28
1.4.2 HEATING AND OXIDATION OF CARBON SURFACES ...... 31
1.4.3 AMINES AND ARYLACETATES ...... 32
1.4.4 MODIFICATION OF CARBON SURFACES BY ARYL DIAZONIUM SALTS...... 35
1.4.5 HYDROSILYLATION, HYDROGENATION AND THE ATTACHMENT OF ALKENES...... 39
1.5 WHICH CARBON AND WHICH MODIFICATION METHODS TO USE?...... 42
1.6 REFERENCES ...... 43
CHAPTER TWO – EXPERIMENTAL METHOD
2.1 MATERIALS ...... 64
2.1.1 CHEMICALS AND REAGENTS ...... 64
2.1.2 PREPARATION OF BUFFERS AND STANDARD SOLUTIONS ...... 68
2.2 INSTRUMENTATION ...... 69
2.2.1 ANALYSIS ...... 69 2.2.1.1 Synthetic analysis ...... 69 2.2.1.1.1 NMR...... 69 2.2.1.2 Surface Analysis...... 70 2.2.1.2.1 Electrochemistry...... 70 2.2.1.2.1.1 Cyclic Voltammetry ...... 72 2.2.1.2.1.2 Osteryoung Square Wave Voltammetry...... 73 2.2.1.2.2 Contact Angle ...... 74 2.2.1.2.3 X-ray Photoelectron Spectroscopy...... 76 2.2.1.2.3 Scanning Electron Microscopy...... 76 2.2.1.2.4 Atomic Force Microscopy ...... 77 2.2.1.2.5 Fluorescence Micrpscopy ...... 78
2.2.2 SURFACE PREPARATION ...... 79 2.2.2.1 Spincoater ...... 79 2.2.2.2 Oven...... 79 2.2.2.3 Tube Furnace ...... 79 2.2.2.4 Plasma Chamber ...... 80
2.3 PREPARATION OF ELECTRODES AND ANALYSIS ...... 81
2.3.1 Preparation of Electrodes ...... 81
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2.3.1.1 General Procedure for PPF Preparation ...... 81 2.3.1.2 Glassy Carbon ...... 82
2.3.2 ANALYSIS OF SURFACES...... 82 2.3.2.1 Electrochemical measurements ...... 82
2.4 REFERENCES ...... 84
CHAPTER THREE - THE EXPLORATION OF VARIABLES IN THE
FABRICATION OF PYROLYSED PHOTORESIST
3.1 INTRODUCTION...... 87
3.2 EXPERIMENTAL METHOD ...... 90
3.2.1 PPF PREPARATION ...... 90 3.2.2 EXPERIMENTAL DESIGN ...... 92 3.2.3 PHYSICAL CHARACTERISATION OF FILMS...... 94 3.2.4 ELECTROCHEMICAL CHARACTERISATION...... 95 3.2.4.1 Glassy Carbon ...... 95 3.2.4.2 Electron Transfer Rates ...... 96 3.2.5 SYNTHESIS OF 4-CARBOXYPHENYL DIAZONIUM TETRAFLUOROBORATE...... 97 3.2.6 MODIFICATION OF ELECTRODES...... 98 3.6.2.1 Electrochemical Reduction of 4-Carboxyphenyl Diazonium Tetrafluoroborate...... 98 3.2.6.2 Attachment of Peptide to Surface ...... 98 3.2.6.3 Copper Accumulation ...... 99
3.3 RESULTS AND DISCUSSION ...... 100
3.3.1 CHOICE OF FACTOR VALUES...... 101 3.3.3 UNCERTAINTY IN PREPARATION AND MEASUREMENT ...... 106
3.3.4 PHYSICAL CHARACTERISTICS OF PPF SAMPLES...... 107 3.3.4.1 Resistivity ...... 107 3.3.4.2 Film Thickness ...... 108 3.3.4.3 Roughness ...... 109 3.3.5 ELECTROCHEMICAL CHARACTERISTICS OF PPF SAMPLES ...... 110 3.3.6 ELECTROCHEMICAL USABILITY AND FUNCTIONALITY...... 114 3.3.6.1 Complexation of Copper(II) with the Peptide Gly-Gly-His Bound to a Carbon Substrate...... 116
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3.3.6.2 Complexation of Copper (II) to Gly-Gly-His...... 118
3.4 CONCLUSION ...... 121
3.5 REFERENCES ...... 123
CHAPTER FOUR - PROTEIN RESISTANCE OF OLIGO(ETHYLENE GLYCOL)
ARYL DIAZONIUM DERIVATIVES
4.1 INTRODUCTION...... 128
4.1.1 ZWITTERIONIC SPECIES...... 129 4.1.2 POLYMERS ...... 130 4.1.3 OLIGO ETHYLENE GLYCOLS ...... 132
4.2 EXPERIMENTAL METHOD ...... 137
4.2.1 GENERAL SYNTHESIS OF ARYL DIAZONIUM DERIVATIVES OF ETHYLENE GLYCOL .... 137 4.2.1.1 Synthesis of 2-(2-(2-(4-nitro-phenoxy)-ethoxy)-ethoxy)-ethanol...... 138 4.2.1.2 Tri(ethoxy-(ethoxy(ethoxy))) aniline ...... 138 4.2.1.3 Synthesis of 4-(2-(2-(2-hydroxy-ethoxy)ethoxy)ethoxy) bezenediazonium
(OEG3OH)...... 139 4.2.1.4 Nitrobenzene Decanol ...... 140 4.2.1.5 4-(decyloxy)aniline...... 141 4.2.1.6 1-(decyloxy)-4-Aryl diazonium tetrafluoroborate (Decane derivative)...... 141 4.2.1.7 Monomethylether(ethoxy-(ethoxy(ethoxy))) Nitrobenzene ...... 142 4.2.1.8 Monomethylether(ethoxy-(ethoxy(ethoxy))) Aniline...... 143 4.2.1.9 Mono methylether(ethoxy-(ethoxy(ethoxy))) Aryl Diazonium Tetrafluoroborate
(OEG3OMe) ...... 143 4.2.1.10 Hexaethylene Glycol Nitrobenzene ...... 144 4.2.1.11 Hexaethylene Glycol Aniline...... 145
4.2.1.12 Hexaethylene Glycol Aryl Diazonium Tetrafluoroborate (OEG6OH) ...... 146 4.2.1.13 Monomethylether Hexaethylene Glycol Nitrobenzene...... 146 4.2.1.14 Monomethylether Hexaethylene Glycol Aniline...... 147 4.2.1.15 Monomethylether Hexaethylene Glycol Aryl Diazonium Tetrafluoroborate
(OEG6OMe) ...... 148 4.2.2 MODIFICATION OF SURFACES ...... 149 4.2.2.1 Preparation of Surfaces ...... 149
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4.2.2.1.1 Pyrolysed Photoresist Films...... 149 4.2.2.1.2 Gold ...... 150 4.2.2.2 Thiol attachment to gold surfaces ...... 150 4.2.2.3 Premade Aryl Diazonium Attachment...... 151 4.2.2.4 Acetonitrile In situ Formation of Aryl Diazonium Salts and Attachment ...... 152 4.2.2.5 Aqueous In situ Formation of Aryl Diazonium Salts and Attachment ...... 152 4.2.2.6 Electrochemistry of modified surfaces ...... 153 4.2.3 NON-SPECIFIC PROTEIN ADSORPTION MEASUREMENTS...... 153 4.2.3.1 Elution of Protein from the surface ...... 153 4.2.3.2 Measurement of Protein on the Surface...... 154 4.2.3.3 Non-Specific Protein Adsorption with Relationship to Time...... 156 4.2.4 CONTACT ANGLE ...... 157
4.3 RESULTS AND DISCUSSION ...... 158
4.3.1 ELECTROCHEMISTRY OF MODIFIED SURFACES ...... 160 4.3.1.1 Attachment of Oligo(Ethylene) Glycols...... 161 4.3.1.2 Electrochemical Passivation of Modified Surfaces...... 164 4.3.2 CONTACT ANGLES ...... 166
4.3.3 EFFECT OF MODIFICATION METHOD ON RESISTANCE TO NON-SPECIFIC PROTEIN
ADSORPTION ...... 168 4.3.4 EXPOSURE TIME AND EFFECT ON NON-SPECIFIC PROTEIN ADSORPTION...... 170 4.3.5 RESISTANCE TO NON-SPECIFIC PROTEIN ADSORPTION ON PPF SURFACES ...... 172 4.3.5.1 Elution of Fluorescently Labelled Protein from the Surface ...... 172 4.3.5.2 Fluorescent Microscopy...... 174
4.4 CONCLUSION ...... 180
4.5 REFERENCES ...... 181
CHAPTER FIVE – IODINATION OF PPF AND ALKENE MODIFICATION
5.1 INTRODUCTION...... 190
5.1.1 COMBINING STABILITY OF COVALENT BONDS AND MONOLAYERS...... 190 5.1.1.1 Alkenes and Alkynes on Silicon ...... 190 5.1.1.2 Alkenes on Diamond...... 192
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5.1.2 IODINATED SURFACES ...... 194
5.2 EXPERIMENTAL METHODS...... 195
5.2.1 PREPARATION OF PPF...... 195 5.2.2 IODINATION OF PPF ...... 195 5.2.3 ALKENE AND ALKYNE ADDITION TO AN IODINATED PPF SURFACE ...... 196 5.2.4 ANALYSIS OF THE IODINATED AND UV REACTED SURFACES ...... 198 5.2.4.1 Contact angle...... 198 5.2.4.2 Electrochemical characterisation...... 198 5.2.4.3 X-ray Photoelectron Spectroscopy ...... 198 5.2.4.4 Atomic Force Microscopy ...... 199 5.2.4.5 “Click” Chemistry...... 199 5.2.4.5 Patterning of Iodinated PPF...... 199 5.2.4.5.1 Synthesis of Gold nano particles ...... 199 5.2.4.5.2 Patterning of the Iodinated PPF Surface with S-undec-10-enyl-2,2,2- trifluoroethanethioate...... 200
5.2.4.5.3 Deprotection of C11-S-TFA Modified Surfaces...... 201 5.2.4.5.4 Attaching Gold Nanoparticles to the Modified Surface...... 201 5.2.4.5.5 SEM Imaging ...... 201
5.3 RESULTS AND DISCUSSION ...... 201
5.3.1 IODINATION OF PYROLYSED PHOTORESIST FILMS ...... 202 5.3.1.1 XPS of Iodinated Surface ...... 203 5.3.1.4 Roughness of PPF After Iodination...... 206 5.3.1.2 Electrochemical Behaviour of the Surface...... 208 5.3.1.3 Hydrophobicity of Iodinated PPF ...... 215
5.3.2 MODIFICATION OF IODINATED PPF BY U.V. ACTIVATION ...... 217 5.3.2.1 Reaction of Iodinated PPF withUndecylenic Acid at 254 nm ...... 218 5.3.2.1.1 Electrochemistry of Iodinated PPF Exposed to Undecylenic Acid at U.V. Wavelength 254 nm ...... 219 5.3.2.1.2 Contact Angle of Iodinated PPF Exposed to Undecylenic Acid at U.V. Wavelength 254 nm ...... 220 5.3.2.2 Reaction of Iodinated PPF with Undecylenic Acid at 514 nm ...... 222 5.3.2.2.1 Contact Angle of Iodinated PPF Exposed to Undecylenic Acid at U.V. Wavelength 514 nm ...... 223 5.3.2.2.2 Electrochemistry of Iodinated PPF Exposed to Undecylenic Acid at U.V. Wavelength 514 nm ...... 224 5.3.3 MODIFICATION OF IODINATED PPF WITH ALKYNES ...... 234
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5.3.3.1 Modification with Nonadiyne and Use of “Click” Chemistry...... 234 5.3.4 PATTERNING OF IODINATED PPF ...... 238
5.3.4.1 Modification with C11-S-TFA...... 239 5.3.4.2 Patterning with Trifluoroacetyl Thioldecene...... 241
5.4 CONCLUSION ...... 243
5.5 REFERENCES ...... 244
CHAPTER SIX – CONCLUSION AND FUTURE WORK
6.1 SUMMARY...... 251
6.2 FUTURE WORK...... 255
6.2.1 FURTHER INVESTIGATING THE EFFECTS OF PLASMA IODINATION AND ALKENE/ALKYNE
ADDITION ...... 255 6.2.1.1 Photolithograpy...... 256 6.2.2 BIOLOGICAL APPLICATIONS ...... 257 6.2.2.1 Affinity Sensors ...... 257 6.2.2.2.1 Development of a Mutlianalyte Sensor...... 259
6.3 CONCLUDING REMARKS...... 260
6.4 REFERENCES ...... 261
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LIST OF ABBREVIATIONS
AFM Atomic Force Microsopy BSA-FITC Bovine Ablimun Serum Fluoroscene Isothiocyante Conjugate CV Cyclic Voltammetry DNA Deoxyribonucleic acid EDC 1-Ethyl-3-(3-dimethylamino)propyl) carbodiimide E Electrode potential EDTA Ethylenediaminetetraacetic acid FAD Flavine Adenine Dinucleotide Phosphate GC Glassy Carbon GOx Glucose Oxidase Gly-Gly-His Glycine-Glycine-Histidine MES 2-(N-morpholino)-ethanesulfonic acid mol Mole NHS N-Hydroxysuccinimide NMR Nuclear Magnetic Resonance OEG Oligo(Ethylene Glycol) OSWV Osteryoung Square Wave Voltametry PPF Pyrolysed Photoresist Films PQQ Pyrroloquinolino quinone RMS Root Mean Square SAM Self Assembled Monolayer SEM Scanning Electron Microscopy TEM Transmission Electron Microscopy U.V. Ultra Violet XPS X-ray Photoelectron Spectroscopy
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Chapter One
General Introduction
1.1 INTRODUCTION
The desire for quick results, and easy to use systems, to real time analysis on the body and the environment are very important in today’s society.1 Many systems are already in place that allow us to carry out these tests, but they require trained professionals and time. One such example is the ability to detect heavy metals in a water system. Generally this requires samples to be taken and sent off to a laboratory to be analysed by an inductively coupled plasma mass spectrometer (ICPMS) which requires sample preparation and a qualified trained technician to run the samples.2 This is where a small hand held device that is portable and quick would be ideal.3-4 Samples could be taken and directly analysed at the site without tedious sample preparation. The device would also have to be specific for the target analyte and be resistant to interferences from other species in the sample. These same features are also applicable for many medical tests that require a blood sample to be taken and sent to a pathology laboratory. Typically in medical tests the samples take a couple of days to prepare before the appropriate test can be conducted and the results determined.5 For both of these examples the use of “biosensors” would be applicable.3-4, 6-7
The aims of this thesis are to investigate new carbon surfaces as well as modification for use in affinity biosensors. The following chapter will discuss the back ground to biosensors in particular affinity biosensors, what aspects are important to the sensitivity of the sensors.
Chapter 1 | 2
1.2 BIOSENSORS
The general basis of a “biosensor” is one that has the ability to detect an analyte with a biological recognition element immobilized directly onto a signal transducer.6-9
The biological recognition element includes species such as enzymes, peptides,10 DNA fragments,11-13 or antibodies.14 The analyte reacts with the biological recognition element that is specific to the target molecule. This reaction is then converted to a signal by the transducer that is either physical or physiochemical (Fig. 1.1).6 The most common types of transducer mechanisms used are in the form of optical, acoustic, or electrochemical.3, 6-7
Figure 1.1 Generalised construct of a biosensor.9
Chapter 1 | 3
1.2.1 TRANSDUCERS
The transducer converts the information produced by the analyte reacting with the biorecognition element into an electronic signal that can then be read out by the end user.5, 9, 15
Piezoelectric materials, such as quartz, are frequently used for acoustic wave transducer systems where the frequency of vibration, when an oscillating circuit is applied to the piezoelectric material, is dependent on the amount of substance absorbed onto the surface of the material.9, 16-17 The change in vibrational frequency, as the analyte reacts with the biorecognition element, can be measured. Small changes in the frequency (0.1 Hz) correspond to mass and viscosity changes (10-10 - 10-11 g), though there is no distinction between specific adsorption and non-specific adsorption.15-18
For optical transducers, the reaction of the analyte with the biorecognition element causes a change in the optical characteristics.5, 9, 16, 19 This response can be measured with fluorescence,20 absorbance or reflectance.21-22 For example, optical biosensors using porous silicon, the detection of the analyte is reliant on the change in the wavelength of reflected light at the interface which is caused by the change in refractive index.23-25 The drawback for optical sensors is that the media that the sensor is being measured in, needs to have low turbidity or better still to be transparent to the wavelength of light being employed for the signal generation.
Electrochemical transducers can be used to measure the signal produced in various ways.9, 15, 26 Potentiometric and amperometric are two ways that the signal can
Chapter 1 | 4
be measured from the transducer. These methods require the transducer to be an electrode. In potentiometric methods the ion concentration is measured.27-28 An amperometric transducer measures the currents produced from the change in oxidation state which occurs as the analyte binds with the biorecognition element.29-31
For the rest of this discussion the focus will be on amperometric electrochemical transducers. The use of amperometric electrochemical biosensors allows individual target molecules to be measured directly on the electrode surface using biorecognition species attached the electrode surface. There are two different classifications of biosensors depending on the biorecognition species used. The two classifications are catalytic biosensors, and affinity biosensors.
1.2.1 CATALYTIC BIOSENSORS
A catalytic biosensor relies on the reaction of the analyte with the biorecognition element causing the catalytic conversion of the analyte from a non-detectable species to a detectable species.8 The most common form of a catalytic biosensor is one using enzymes.1, 30, 32-36 The enzyme does not only act as the catalyst but also as the biorecognition element.
There are several ways for immobilising the enzyme on the transducer/electrode surface. In some cases the immobilisation of the enzyme on the surface is by the coating of the surface with the biorecognition element and the catalyst.37-38 The coating of the surface is secured in place with a dialysis membrane, allowing the transfer of species through the membrane but not the other way around.32 Immobilisation of the
Chapter 1 | 5
biorecognition element and catalyst can also occur by inclusion in a polymer. The polymer can be formed through either electrochemical or chemical means.39
Electrochemical redox reactions cause polymer formation and the incorporation of the biorecognition element.26
Not all reactions of the analyte with the biorecognition element are able to produce a signal that is directly detected by the transducer/electrode. A mediator that can be easily oxidised or reduced maybe required. The redox reaction in the mediator occurs from the reaction of the analyte with the biorecognition element. Once the biorecognition element reacts with the analyte, the mediator undergoes subsequent redox reactions that can then be detected by the transducer.9, 32, 40 As the analyte reacts with the enzyme, the enzyme is reduced. This then causes the subsequent reduction of the mediator and the enzyme is oxidised back to its original state. The transducer/electrode detects the change in oxidation state of the mediator.
Perhaps the most successful and well known of these systems is the glucose sensor used by diabetics.1 A glucose sensor consists of an electrode surface, a mediator and glucose oxidase (Fig. 1.2).37, 41 The glucose is oxidised in the blood sample by glucose oxidase that is adsorbed onto the transducer. The reduced glucose oxidase
(GOx) is then in turn re-oxidised by the mediator, which is then oxidised by the electrode and produces a current and thus a measurement of the amount of glucose present is given.37 The mediator used can be either oxygen, as in Nature where hydrogen peroxide is produced, or in commercial glucose sensors the mediator used is ferrocene or ferricyanide.6, 42 As the glucose is oxidised there are electrons produced which in turn cause the reduction of the mediator, ferrocene or ferricyanide.37-38, 41-42
Chapter 1 | 6
The current produced from the oxidation of the mediator by the electrode is then transferred to an electrical signal that can be readout by the end user.
Figure 1.2 The construct of a glucose sensor used by diabetics, where the glucose is adsorbed
onto an electrode surface and the electrical signal is produced by the oxidation of glucose and
subsequent oxidation of GOx.32
This type of sensor, although the biorecognition element is specific for the analyte, is prone to interference. Non-specific oxidation/reduction of unwanted redox active molecules can cause interference. In the case of the glucose sensor, ascorbic acid as well as uric acid and molecular oxygen can cause interference. As the glucose is oxidised by the glucose oxidase, molecular oxygen in the sample can in turn be oxidised instead of the mediator thus not all the glucose is detected.33 By “electrically wiring” into the enzyme this interference can be reduced. Willner and co-workers attached an electrochemical relay, pyrroloquinolino quinone (PQQ), to the aminoethyl flavine adenine dinucleotide phosphate (amino-FAD) in the glucose oxidase (Fig. 1.3).30, 33 By reconstituting the glucose oxidase around the amino-FAD attached to a surface bound
PQQ, the electrons produced via the oxidation of glucose can be transported to the electrode transducer. Similar work has been carried out by Gooding and co-workers
Chapter 1 | 7
where norbornylogous bridges and carbon nanotubes were inserted into glucose oxidase and attached to the electrode surface.43
Figure 1.3 “electrical wiring” of glucose oxidase. The glucose oxidase is reconstituted around
FAD that is bound to the gold surface with pyrroloquinolino quinone. As the glucose is
oxidised, FAD is in turn oxidised and the electrons are passed down the “electrical wire” to the
PQQ and then to the surface.33
These catalytic biosensors though are still not interference free and it is difficult to detect small molecules using this technique.
1.2.2 AFFINITY SENSORS
An affinity biosensor uses species that are specific to the analyte whereby the reaction of the analyte with the biorecognition element causes a signal without further reactions.9, 15-16, 44 The use of an affinity sensor provides a broader range of analytes due to a larger amount of biorecognition elements that can be used. As the name suggests the biorecognition element and analyte can act in a receptor-ligand like fashion.5, 9, 15-16 Affinity sensors can be used to detect various analytes. The
Chapter 1 | 8
biorecognition element can be either antibodies, nucleic acids, DNA, receptor proteins and biomimetic materials.3, 5, 9, 29, 45-46
The use of the peptide Glycine-Glycine-Histidine (Gly-Gly-His) to detect copper in water has previously been documented by Gooding and co-workers.10, 29, 47-49 When the peptide is attached to the surface and not coordinated to copper it produces no electrochemistry, but when the peptide complexes with free copper (II) it brings the copper (II) close enough to the surface of the electrode so that is able to be reduced and oxidised, thus the amount of copper (II) can be detected (Fig 1.4).10, 47 The use of the peptide sequence (Gly-Gly-His) instead of cysteine by itself gives better selectivity towards copper and shows little interference from other heavy metals.47, 49 The ability to attach the peptide to the surface using an alkanethiol species allows free movement of the peptide to be maintained.10 Free movement is achieved by the ability of the gold surface to rearrange on the surface to give a monolayer with lowest energy allowing the monolayer to rearrange to give the peptide enough space to bind to the copper.49-52
O O O O OH OH O NH HN O N N Cu2+ N NH N N + Cu2+ N O N O H H
S S
Figure 1.4 Gly-Gly-His copper sensor construct on a gold substrate, showing no
electrochemical behaviour without copper and once bound to copper electrochemical behaviour
is seen.10, 47
Chapter 1 | 9
The main type of affinity biosensors use antibodies or antigens, due to their affinity for specific proteins and analytes, which also allows for a wider range of analytes to be detected. These affinity biosensors are classified as immunosensors.3, 15,
53 Antibodies are proteins related to the immune system and are produced by B- lymphocytes in animals, in response to a foreign substance otherwise known as an antigen.3 The general structure of an antibody can be represented by the class of antibodies known as IgG or γ-globulin. Antibodies have a molecular weight between
150,000 and 160,000 Daltons. They are Y shaped, with each arm consisting of a light chain and a heavy chain held together with a disulphide bridge (Fig. 1.5).3, 54
Figure 1.5 Basic structure of an antibody showing the different fragments. The Fc fragment is
3, 5, 55 the crystalline fragment. The F(ab) and F(ab’)2 are the antibody binding fragments.
The main problem with immunosensors is the transduction of the binding event.
Many electrochemical immunosensors use competitive binding or co-enzymes that
Chapter 1 | 10
undergo an oxidation change converting the event into a transducable signal. An example of an electrochemical immunosensor has been explored by Liu et al..14, 43, 56
The use of biotin attached to the surface enables the measurement of antibiotin. Unlike other methods though, the use of labels or competitive binding is not needed. Biotin is attached to the redox active molecule ferrocene, which is attached to the surface using a molecular wire (Fig. 1.6).43 The ferrocene is able to be oxidised and reduced, thus producing an electrochemical signal. When the antibiotin binds to the biotin, as it is large in comparison to the sensor construct it not only engulfs the biotin but also the ferrocene. Once the ferrocene is covered with the antibiotin it is no longer able to be oxidised or reduced due to the inability of counter ions to access the ferrocene. Thus a decrease in the electrochemical signal is observed.43
Figure 1.6 Antibiotin immunosensor. As the antibiotin binds to the surface bound biotin, it
blocks access of electrons to the ferrocene thus reducing the electrochemical signal produced.
The concentration of biotin can be correlated to the amount of signal reduction.43, 56
Chapter 1 | 11
The difference between affinity biosensors and catalytic biosensors is the ability to detect small molecules, with specific biorecognition species, and little interference.
1.3 FACTORS IMPORTANT FOR AFFINITY BIOSENSORS
The sensitivity, stability and selectivity of an affinity biosensor are important.
The transducer and its structure, and the biosensing interface can influence these factors. Selectivity relies on the ability of the surface to only bind the target analyte and that species alone.6-7 Sensitivity of the affinity biosensor not only relies on the ability of the biorecognition element to bind to the analyte but also on the ease to which the analyte can bind to the biorecognition element.57 The thermodynamics of the analyte binding with the biorecognition element can also be affected making the biosensor slower in response.58 The stability of the sensor requires the binding of the biorecognition element to be robust as well as the recognition element itself.9, 15, 59-60
1.3.1 ELECTRODE SURFACE STRUCTURE
The surface structure of the electrode is important and has the ability to affect the sensitivity of the affinity biosensor. The environment that the biorecognition element is in will affect the thermodynamics between it and the analyte. It is important that all the biorecognition elements on the surface are in the same environment to ensure similar thermodynamics between each and the analyte.3, 35, 58, 61-62 The loss of movement of the biorecognition element in some cases can affect both the binding kinetics and reaction thermodynamics.35, 57-58, 63-64
Chapter 1 | 12
The surface roughness of the electrode now becomes important to the sensitivity of the affinity biosensor.35, 57, 62 If the surface is rough, the biorecognition elements are not all available to react with the analyte.61 This in comparison to those on a smooth surface where all species are able to react thus allowing more recognition sites and increasing the amount of change that can be recorded and hence the sensitivity (Fig.
1.7). Having an affinity biosensor with a smoother surface will increase the sensitivity.57, 65-66 The ability to control the surface topography is required for both preparation of the surface and for the subsequent modification with the biorecognition element.57
Figure 1.7 a) The affect of a rough surface on the environment of the biorecognition element.
Not all biorecognition elements are able to be accessed by the analyte. b) The affect of a
smooth surface on the environment of the biorecognition element, allowing access to all
biorecognition elements and increasing sensitivity.
Eggers et al. have also investigated the effect of the distance of the redox probe from the electrode surface and its depth into the diffusion layer. It was shown that the distance the redox probe is into the diffusion layer could affect the electron transfer rate,
Chapter 1 | 13
the further it is into the diffusion layer the slower the electron transfer and the lower the formal potential.67-69 If an affinity biosensor similar to the one used by Gooding and co- workers is to be assembled the surface roughness is important as this will affect the sensitivity of the electrochemical signal produced.
The electrode surface that is to be investigated for the use of an affinity biosensor needs to have a surface with near atomic smoothness, this will allow for greater sensor sensitivity. By having a surface with near atomic smoothness will allow for the biorecognition element as well as the redox probe to be in the same environment over the entire electrode surface producing greater sensitivity in the affinity biosensor.
1.3.2 BIOSENSING INTERFACE
As affinity biosensors are to be used in complicated matrixes, the biorecognition layer needs to be bound to the surface to give a reagent less solid-state device. The method used to bind the biorecognition element to the surface needs to be stable towards oxidation in solution. It also needs to be stable for storage. Since many affinity biosensors will be used for biological samples, the interface also needs to resist adsorption of unwanted proteins and allow for fast thermodynamics between the analyte and the biorecognition element. The use of a diluent between the biorecognition elements allows space for freedom of movement for the binding of the biorecognition element and the analyte, thus giving rise to faster thermodynamics.35, 57-58, 63-64
Chapter 1 | 14
1.3.2.1 PROTEIN RESISTANCE
The exposure of the affinity biosensor surface to biological matrixes such as blood, requires the surface to only allow the binding of the wanted analyte to the biorecognition element. The use of a specific biorecognition element for the analyte will partly allow this, but the surface may be prone to non-specific protein adsorption.
There are several ways of combating this problem, and they all involve the diluting of the biorecognition element with a protein resistant diluent.70-75 The use of poly(ethylene glycols) to form a polymer on the surface with the biorecognition element is one such method.76-77 The molecular weight of the polymer can have an effect on the protein resistance.
The use of shorter single chains of poly(ethylene glycol) in the form of oligo(ethylene glycols) (OEG’s), allow for a more controlled formation of the protein resistant diluent.72, 78-82 Grunze and co-workers observed that for alkanethiol OEG’s on gold the length of the chain was an important factor as to the ability of the surface to resist non-specific protein adsorption.82 By changing the chain length from three OEG units (Fig. 1.8 b) to six OEG units (Fig. 1.8b) the amount of protein adsorbed onto the surface was decreased. The hydrophilicity of the distal end was also important. When the distal end was changed from a methoxy (Fig. 1.8c) to a hydroxy (Fig. 1.8a) the amount of non-specifically adsorbed protein was also shown to decrease.82-83
Chapter 1 | 15
HS O OH a O O
HS O O O b O O O OH
c HS O O O O
Figure 1.8 a) Alkanethiol OEG with three OEG units and a hydroxy distal end. b) Alkanethiol
OEG with six OEG units and a hydroxy distal end. c) Alkanethiol OEG with three OEG units
and a methoxy distal end.81, 84
The final common method for the reduction in non-specific protein adsorption is to use zwitterionic species on the surface (Fig 1.9a and 1.9b) or to make the surface zwitterionic like (Fig. 1.9c).71, 80, 85-89 By using a diluent that has both positively and negatively charged species on the surface the amount of non-specific protein adsorption has been observed to decrease.86, 88 The biosensor surface can also be modified to be zwitterionic like. This requires the use of two different diluents, one positively charged and the other negatively charged. This gives the surface an overall neutral charge at an appropriate pH and has been shown to also decrease the amount of protein adsorption.71,
86-87
a b c
+ + + +
- - - - - +
------
+ + + + + + + +
Figure 1.9 a) The modification of a surface with a zwitterionic species that has a negative
distal end and a positive centre. b) The modification of a surface with a zwitterionic species
that has a positive distal end and a negative centre. c) A modified surface with both positive
and negative species giving the surface a zwitterionic like character.
Chapter 1 | 16
By using a diluent that is able to resist non-specific protein the specificity of a affinity biosensor as well as the sensitivity would be increased. By reducing non- specific protein adsorption on the affinity biosensor it would allow the target molecule access to the biorecognition element. The use of zwitterionic surfaces though requires the pH of the matrix being tested to be at the right level so that both elements are positively charged and negatively charged at the same time. It is the hope that affinity biosensors in the future will be used with little to no sample preparation, using oligo(ethylene glycols) are the diluent to reduce non-specific protein adsorption requires no adjustment of the pH and thus will be further investigated.
1.3.2.2 BINDING OF THE AFFINITY BIOSENSOR INTERFACE
The two most common surfaces for electrochemical biosensor transducers are gold and carbon, though the use of silicon surfaces and other metals is an emerging field.90-91 Both gold and carbon surfaces are able to be modified. Gold can be modified with thiols to form a sulphur-carbon bond,59 and carbon can be modified in several ways including polymer layers,26 aryl diazonium salts,92-93 and even alkenes.94 All of these modification methods will be discussed below. The ideal surface for an electrochemical biosensor is one that has reliable electrochemistry; this requires a stable surface.95
The modification of gold is generally carried out by the use of alkanethiols which spontaneously absorb onto the surface of gold to form a gold-thiolate bond.96
The use of an alkanethiol modified gold surface allows the formation of a well understood monolayer, which can then be used for various electrochemical methods
Chapter 1 | 17
including that of electrochemical biosensors.45, 59, 97 It has been shown that longer alkanethiol chains form a more ordered monolayer with the alkyl chains positioned at an angle of 30° than layers formed of shorter chain lengths.98
There are several issues with using thiols for the modification of gold. Firstly they are able rearrange on the surface to give a monolayer with lowest energy.51-52 The gold-thiol bond is also prone to oxidation as it is highly polar, and has a narrow potential window of +0.8 V and -1.4 V.50, 99-100 Packing density, chain length and distal end group can affect the stability of the gold-thiol. Shorter chain lengths can reduce this potential window to -0.4 V to +0.6 V. The monolayers are also liable to desorb at elevated temperatures.96 Alkanethiol modified gold surfaces are also unstable to sulfonates and sulfinates, and are oxidised with UV light.101-102 These instability issues can be overcome for storage by sealing in silver foil to protect it from light. The stability issues still come into play in the modification process as for some sensors there are multiple steps each with its own liquid environment.95, 103 These stability issues in the use of gold for electrochemical biosensors give rise to the search for another viable surface to be used.
The use of carbon, as previously mentioned, is another highly used surface for electrochemical biosensors. There are many carbon surfaces including carbon paste, highly ordered pyrolytic graphite (HOPG), diamond like films, glassy carbon and thin carbon films. Is there a carbon surface that provides better stability and good electrochemical properties?
Chapter 1 | 18
1.3 CARBON AS AN ELECTRODE MATERIAL
1.3.1 CARBON PASTE
Carbon paste electrodes are as their name indicates made of carbon mixed with a liquid that has low water solubility and low volatility.104-105 These are cheap, easy to construct electrodes. They react well electrochemically, but are extremely rough and not stable over long periods of time.105 The media in which the carbon is mixed can affect the ability of the electrode to perform. This can be seen in work by Lindquist,105 where several different carbon paste electrodes were made and their performance was tested. On glassy carbon electrode the reduction of hydroquinone is irreversible.
Lindquist showed that a carbon paste electrode made from 1-bromonaphthalene produced irreversible voltammograms with hydroquinone.105 Carbon paste electrodes made with either paraffin oil, silicone fluid or decahydronapthalene all gave good reversible peaks for hydroquinone.
These electrodes though do not provide a smooth enough surface for an affinity biosensors. The biorecognition element is also only loosely bound, which makes long exposure time of the sensor in media difficult.
1.3.2 HIGHLY ORDERED PYROLYTIC GRAPHITE
Highly ordered pyrolytic graphite (HOPG) can be atomically smooth, but due to its structure of edge and basal planes the electrochemical response towards many redox active complexes can be affected.106-107 Basal plane HOPG is generally used for STM
Chapter 1 | 19
imaging as it is atomically flat carbon with few or no defects.108 HOPG is produced by using high temperature decomposition of gaseous hydrocarbons and then applying pressure at high temperatures. The common gaseous hydrocarbons used are acetylene or methane gas.109-110 The higher the temperature used during formation, the more ordered and parallel the graphitic layers become.111 The use of pressure during the annealing process removes “ripples” in the basal plane and removes impurities in the graphite sheet, thus forming a near ideal graphite.112 HOPG is made of edge and basal planes. The basal plane is atomically smooth with variances due to step edges. The edge planes are rough,113 and functionalised with oxygen. During polishing of the edge planes unsatisfied valances are formed due to bonds breaking and they are able to react with oxygen and water to form oxygen containing functional groups.
It has been seen that edge and basal planes behave differently with regards to electron transfer. Both inner sphere and outer sphere redox systems, such as ferricyanide and ruthenium hexamine respectively, behave the same way on basal plane
HOPG. Slow electron transfer rates of ruthenium hexamine and ferricyanide on basal planes, indicate that it is not surface impurities that hinder the process but the surface itself.114 It has been seen that electron transfer on the basal plane can be improved by both electrochemical and laser activation of the surface. These processes increase the edge defects of the surface.106, 108, 115-116 The surface of basal plane HOPG is low in oxygen and the cleaning of these impurities from this surface does not dramatically increase the surface kinetics. However, increasing the amount of oxygen on edge planes has been shown to slow the electron transfer rate due to the linking of the graphite sheets.117
Chapter 1 | 20
HOPG is a semimetal in nature, from Raman spectroscopy the 1360/1582 cm-1 peak ratio (D/G) can indicate how ordered the carbon structure is. Basal plane HOPG is highly ordered with a ratio of D to G band value close to zero (0.0005), whilst edge plane HOPG is highly disordered (1.1). The capacitance of basal order HOPG is low and linked with the semimetal nature of the material. Edge plane HOPG shows high reactivity towards electron transfer and adsorption in comparison to basal plane HOPG that has low electron transfer rates and minimum adsorption although the bulk structure is the same Fig 1.10.106
Figure 1.10 Bulk configuration of HOPG showing edge and basal planes.106, 108, 115
The use of HOPG as an surface for mass produced electrodes is undesirable due to the difficulty of mass production and cost. This fact combined with both slow electron transport for basal planes and rough surfaces for edge planes makes another carbon alternative sought after.
Chapter 1 | 21
1.3.3 DIAMOND-LIKE CARBON
The use of diamond as a carbon electrode substrate is a new development.
Diamond like carbon film is made from the deposition in plasma of methane and hydrogen gas mix, which forms diamond like films with polycrystalline structure or microcrystals where the carbons are linked in a tetrahedral construct with sp3 hybridisation.118
Diamond by itself though is non-conducting and needs to be doped during the formation process with boron to provide conductance through the substrate. From here boron doped diamond like films (BDD) can be used for electrochemistry by further modification with alkenes after the surface has been modified. BDD provides a wide working potential window and a low background.119 The BDD diamond is comprised of diamond like micro crystalline structures. Hence the structure is not the pure sp3 structure but can contain sp2 as well due to the inclusion of boron.120-121
Diamond surfaces have been used to further investigate non-specific protein resistance of oligo(ethylene glycols) for use in biosensors. The modification of the diamond surface was carried out with alkenes via activation of the surface with UV light, as will be discussed later in chapter 1 section 1.4.5. The modified surfaces produced were able to reduce non-specific protein adsorption similar to that of oligo(ethylene glycol) thiol modified gold surfaces.72, 122 The diamond surfaces were also modified with amine terminated alkenes which were used to further modify the surface with sulfosuccinimidyl-6'-(biotinamido)-6-hexamidohexanoate (NHS-SS-
Biotin). This allowed the diamond to be modified with biotin, by exposing the surface
Chapter 1 | 22
to fluorescently labelled avidin, the binding of the avidin to biotin modified surfaces and oligo(ethylene glycol) modified surfaces was measured using fluorescent microscopy.72, 94, 122 Diamond surfaces have also been used to bind DNA to the surface.90-91
Further study into the use of this surface as a biosensor substrate is still required.
Although BDD is electrochemically conducting the surface roughness though, is not near atomically smooth which is wanted for an affinity biosensor. Is there a smoother electrochemically conducting carbon surface that can be used?
1.3.4 HYDROGENATED AMORPHOUS CARBON
Amorphous carbon is a mixture of both sp2 and sp3 carbon, and it is highly disordered. Hydrogenated amorphous carbon (a-C:H) films can be formed using either microwave plasma chemical vapour deposition (MW-PCVD) or plasma enhanced chemical vapour deposition (PE-CVD) of acetylene and hydrogen gas. The structure of the a-C:H can vary on the flow rate of hydrogen into the CVD chamber. As the ratio of hydrogen to acetylene is increased the amount of sp3 configured carbon also increases in comparison to sp2 configured carbon.123 The surfaces produced are similar to diamond like films as both are non-polar and similar to basal plane HOPG.124 The surfaces produced are stable in air, and are slower to oxidise than that of polished glassy carbon.125 Roughening of the surface occurs during formation of a-C:H and root mean square (rms) values range from 5 nm to 120 nm.123 The roughness depends on the acetylene to hydrogen ratio; ratios of 15:150 and 15:270 (acetylene to hydrogen respectively) give surfaces with low rms values due to the formation of more sp3 bonds
Chapter 1 | 23
and the structure is more dense. Ratios on either side of this have higher rms values for low acetylene to hydrogen ratios more sp2 bonds are formed and at higher ratios there is polymeric carbon due to excess hydrogen.123
Similarly to diamond films and BDD, a-C:H films can be modified through the use of alkenes and UV light. Hamers and co-workers have also functionalised a-C:H films with alkenes and further modified with s-DNA. The modified surfaces were then hybridised with DNA.126
For the improvement of sensitivity of affinity biosensors surface roughness needs to be minimised, as discussed earlier a-C:H have a wide range of surface roughness (rms of 5 nm to 120 nm)123, this makes a-C:H not smooth enough for the use of an affinity sensor if surface sensitivity is to be improved.
1.3.5 GLASSY CARBON
Glassy carbon (GC) is commonly used as an electrode material in electrochemical sensors as it has a wide potential window127-129 and is a very stable material under a wide range of conditions.130 GC is a good electrode material for most redox reactions and can be modified by the reduction of various compounds, as will be discussed later. The behaviour towards outer sphere redox species131 produces good electrochemistry, though the behaviour of inner sphere redox species can vary depending on the preparation methods used.132
Chapter 1 | 24
GC is made from the high heat treatment of phenolic resins in which intermolecular cross linking of the hydroxyl groups on the phenolic groups and methylene groups, with the release of water. This gives the resulting glassy carbon domains of graphite in an amorphous phase consisting of entangled aromatic ribbons that are crossed linked with sp3 bonding (Fig. 1.11).133-135
Figure 1.11 Generalised structural model of GC showing graphitic ribbon stacks.134
The elimination of water occurs between the temperatures of 350 °C and 500 °C forming the aromatic ribbons, though they are not perfect and are randomly orientated.134 At 500 °C to 1500 °C hydrogen is released and the ribbons stack closer together and cross linking occurs.134, 136 At higher than 1500 °C graphitisation occurs at these temperatures the aromatic ribbons start to flatten and the boundaries between the ribbons become more localised.136-137 However true graphitisation cannot occur as the aromatic ribbons are too long and would need to break in order for this to occur.
GC has been used for several biosensors as shown (section 1.2.2) previously the work by Liu et al.43, 56 shows the use of glassy carbon in the construct of an affinity
Chapter 1 | 25
biosensor through the modification technique of the electrochemical reduction of aryl diazonium salts (this will be discussed later in chapter 1 section 1.4.4).14, 56 The affinity biosensor worked through the use of biotin attached to ferrocene which in turn is bound to the GC electrode surface. The biosensor gives and electrochemical signal due to the electrochemical reduction and oxidation of ferrocene. As anitbiotin binds to the biotin it blocks the access of electrons to the ferrocene, thus the signal is reduced depending on the amount of antibiotin in the sample. Glassy carbon has also been modified with oligo(ethylene glycols) and oligo(monomethyl ethers) to investigate non-specific protein adsorption. Both Maeda et al.138 and Downard and co-workers139 have shown that the use of these molecules on the surface has the ability to reduce non-specific protein adsorption in comparison to bare surfaces.138-139
The drawback with glassy carbon is that the surface of the final material is rough on the molecular level. This roughness has implications for modern trends in sensing where molecular level control over the modification of an electrode surface is important. Therefore, if the advantages of GC are to be exploited over as wide a range of potential applications as possible there is a need for smoother surfaces to allow molecular level control of the surface modification, for high resolution patterning, and for AFM investigation into the layers formed by various surface modification techniques.
1.3.5 THIN CARBON FILMS
An alternative to GC is thin carbon films.140-142 Previous studies by McCreery and co-workers143-145 and the Kinoshita group146-149 have shown that thin carbon films
Chapter 1 | 26
can be formed by the pyrolysis of photoresist films. The thin carbon films produced give smoother carbon surfaces than are achievable with conventional methods of fabricating GC (with a rms value less than 0.5 nm compared with 4.5 - 44 nm for
GC).143-147 In common with surfaces of GC, films formed from this process are mainly amorphous with graphitic regions. This can be seen by the presence of the relative D and G bands in the Raman spectra around 1360 cm-1 and 1600 cm-1. These two bands can give an idea as to how much disorder is present in the structure.145
For the formation of thin carbon films a thin film of photoresist is laid down on a substrate and then pyrolysed in a tube furnace in a reducing atmosphere to give a conducting carbon film.143 The attractiveness of pyrolysed photoresist films (PPF) is that it not only provides a much smoother surface but also has similar electrochemistry to that of GC. Furthermore it is compatible with bulk manufacture of a range of conducting patterned carbon structures.144, 146-147 PPF has also been shown to have low oxygen content (the atomic percent ratios from x-ray photoelectron spectroscopy the ratios of oxygen to carbon are approximately 0.05) for films pyrolysed at temperatures greater than 700 ºC and they are slow to be oxidised in ambient atmospheres. The low
O/C ratio is important if these materials are to be used as micro electrodes and micro batteries as the O/C ratio influences the electron transfer rate of some redox probes.140,
144
The use of PPF as an electrode surface for affinity biosensors will be discussed later in chapter 3 section 3.3.6.2.
Chapter 1 | 27
1.4 MODIFICATION OF CARBON
Carbon surfaces, as previously mentioned, can be modified in several ways;
1. Through the use of polymers on the surface.
2. Through the production of radicals on the surface, via heat and vacuum.
3. Making the surface reactive with carboxylic acids and amines, the
surface can be subsequently modified.
4. Using electrochemical modification to produce stable covalently bound
layers.
5. Recent progress into the use of alkenes has been shown to modify
diamond-like surfaces.
1.4.1 POLYMERS AND MEMBRANES
Polymer layers on the surface of carbon use the ability to combine the conducting properties of certain polymers and the ease of incorporating not only recognition elements, but several wanted functionalities such as protein resistance and specification.150-151 Polymers can be used as a membrane either over the recognition element, or in the form of a sandwich arrangement with a polymer membrane on either side of the recognition element, or with the polymer itself being the recognition element as illustrated in Fig. 1.12.26, 152
Chapter 1 | 28
a b c
Figure 1.12 Modification of carbon surfaces with polymer membranes. a) The biorecognition element is sandwiched between to polymer layers. The first is conducting; the second can act as
a membrane allowing only certain species through. b) The polymer layer is a membrane over
the biorecognition element. c) The biorecognition element is incorporated into the polymer.26
The polymers can be formed in several ways, including via electrochemical polymerisation, and chemical polymerisation. Polypyrrole is used as a polymer for biosensing as it is electrochemically conducting, and can be produced from the electrochemical oxidation of pyrrole in aqueous sulphuric acid, reacting through the α,
α'-carbons and some reaction of the β-carbons causing cross linking of the chain. By forming the polymer in a biological media, enzymes can be incorporated into the polymer.153 Several other polymers that are able to be electrochemically formed can also be incorporated with enzymes via the same method.26 This method has the advantage of being able to control the biological loading of the polymer through the concentration of the media. Modifying the pyrrole monomer with a recognition element is another way to incorporate them into the polymer.154-155 As the polymerisation of the
Chapter 1 | 29
pyrrole can still occur and in a similar manner to the enzymes the recognition element is thus incorporated into the polymer.
The use of Nafion, a sulfonated tetrafluoroethylene based fluoropolymer- copolymer, can be used for selectivity. Nafion polymer on the electrode surfaces repels ascorbic acid as it is negatively charged.156-157 The electrodes with a layer of Nafion on top of the electrode showed better resistance to ascorbic acid than electrodes with a mixture of Nafion and GOx.156
The use of membranes can work in a similar manner. The recognition elements are physisorbed onto the surface and a membrane, generally a dialysis membrane or a non-conducting polymer, is then placed over the modified surface.32, 158 The membrane has two purposes, firstly as a method to stabilise the modified surface in solution, and secondly as a way to reduce interferences via size or charge exclusion. This method can be seen in a lactose sensor where the two enzymes galactosidase and glucose oxidase are trapped behind a dialysis membrane that has a low molecular cut off weight at 3.5 ×
103.39, 158
These methods both allow the inclusion of recognition elements and help to reduce interference by competing substances, though neither allow sensitive detection due to mass transfer through either the polymer or membrane.
Chapter 1 | 30
1.4.2 HEATING AND OXIDATION OF CARBON SURFACES
The oxidation of carbon surfaces produces carboxylic acids, quinonic, ketonic or hydroxylic groups on the surface (Fig. 1.13). These groups can then be reacted to further modify the surface. This oxidation can occur through treatment of the surface with either hot, strong acids, or by heating the substrate to around 400 °C and exposing it to oxygen.159 This can be seen in the work by Paxinos et al.160 where the GC was anodically oxidised using nitric acid, sulphuric acid and potassium dichromate and passing a charge through the surface of 2 C cm-2. Cobalt diaminosarcophgine was then attached covalently to the GC surface once the oxidised surface was activated with N- cyclohexyl-N'-[2-(N-methylmorpholino)-ethyl]-carbodiimide-p-toluene sulfonate.160
The oxidation of the surface is carried out under harsh conditions and also increases the surface roughness.161-163
Carboxylic acid Phenol o-quinone Lactone HO O Carbonyl OH O O O O O O O
p-quinone
O
Figure 1.13 Carboxylic acids, quinonic, ketonic or hydroxylic groups on the surface of
oxidised carbon.164
Chapter 1 | 31
Amine groups can be introduced to the surface by the use of ammonia. Amine termination of the surface can be accomplished using either plasma or ammonia or a combination of the two; Firstly by the exposure of the carbon surface with ammonia plasma.165 Secondly, amines can also be introduced onto the surface by polishing GC electrodes in the presence of ammonia.128 Thirdly, using a mixture of plasma exposure and ammonia exposure the carbon can be modified by exposing the carbon surface to argon radio frequency plasma and subsequent exposure to ammonia vapour.166-168 The amine terminated surface can then be reacted with N-hydroxysuccinimide esters. This was shown by Saveant and co-workers through the attachment of a ferrocene N- hydroxysuccinimide ester to an amine terminated surface as well as attaching biotin to the surface.166, 169
The surface preparation required to terminate the carbon surfaces with amines or to oxidise the surface requires harsh conditions, which roughen the surface. Little work has also been carried out on the use of these two methods for making mixed monolayers on the surface, which is a requirement for affinity biosensors.
1.4.3 AMINES AND ARYLACETATES
Primary and secondary amines can be electrochemically oxidised in either ethanol or acetonitrile to produce a radical that binds to the surface of carbon (Fig
1.14).170 A monolayer is believed to be formed by the oxidation of primary amines, whilst secondary amines produce low coverage, implying that the stereochemistry of the alkyl amine being attached are important.170 Bein and co-workers investigated alkyl chains of different lengths and it was observed that those with longer chain length
Chapter 1 | 32
(amino hexanol, decylamine and octadecylamine) did not produce the same amount of coverage as those with shorter chain lengths (butylamine).171 It was noted that the reproducibility of the attachment of the amines was affected by the GC electrode history including its electrochemical performance. The structure of the carbon can also affect the attachment and reproducibility, as it has been shown that the oxidation of amines onto the surface does not occur for basal planes.171
R R CH2 CH2 R R H N 2 H N CH CH2 R - 2 + -e -H H2N HN CH2 HN
Figure 1.14 Oxidation of primary amines onto carbon surfaces.171
The reaction of the amines onto the surface was found to form nitrogen-carbon bonds. The formation of the nitrogen-carbon bond was found to be covalently formed as opposed to the amines being only physisorbed onto the surface. Pinson and co- workers 170 have shown that the bond formed is stable after thermal treatment (110° for
1 hr) under vacuum. However it was shown by Deinhammer et al.172 that after 100 cyclic scans (in 0.1 M HClO4 between 0.2 and 0.8 V vs. Ag|AgCl in saturated LiClO4) a butylamine derived carbon surface gave a 10 % reduction of the N:C ratio. The use of heat as well as time, can be used to modify carbon surfaces with alkyl amines. By refluxing the carbon surface in either neat alkyl amines or concentrated solutions of alkyl amines in terahydrofuran under N2 for 15 hrs to 5 days a monolayer forms, though this is a very harsh method.173 By leaving the surface in the alkyl amine solution
Chapter 1 | 33
without heating the reaction was noted to go slower than the electrochemically assisted modification. Similar electrochemical methods can be used for alcohols. It is believed that a surface radical is produced which then reacts with the alcohols forming an ether bond.
The modification of carbon surfaces using arylacetates is carried out according to Kolbe reaction, through the oxidation of carboxylates.93, 174 This method allows the modification of the basal plane as well as the edge plane of graphite and carbon surfaces. The carboxylate is oxidised releasing CO2 and forming a radical which then reacts with the surface (Fig. 1.15).175-176
R CO2 - R -e -CO2 R
Figure 1.15 Oxidation of arylacetates via the Kolbe reaction.177-178
Several studies have shown that there is the possibility of the formation of multilayers.174, 176 As the arylcarboxylates are oxidised onto the surface a peak in cyclic voltammetry is shown. Upon further scanning this peak is observed to decrease and a secondary peak is observed. If however the potential is held just before the oxidation peak, the removal of the arylcarboxylate is observed.174, 176
The use of amines and arylcarboxylates to modify the surface provides a polar bond and is not as stable as a carbon-carbon bond. The arylcarboxylate is unstable for
Chapter 1 | 34
the use of electrochemical sensors, and also can form multilayers. Can a carbon surface be modified with a covalent bond that is non-polar and thus less prone to oxidation?
1.4.4 MODIFICATION OF CARBON SURFACES BY ARYL DIAZONIUM SALTS
The use of aryl diazonium salts to modify carbon surfaces was first performed by Saveant and Pinson.93, 179 Aryl diazonium salts can be used on both gold and glassy carbon surface to form stable, covalently bound layers on an electrode surface.180-181
The electrochemical reduction of aryl diazonium salts produces a radical, which is then strongly bound to the surface (Fig. 1.16).92 This reduction produces covalently bound aryl groups on the surface through a carbon-carbon bond. The layers produced are stable and have a wider potential range than that of a thiol derived gold surface. Aryl diazonium salts can also be reduced on both GC as well as HOPG, edge and basal planes, though edge planes are more reactive.92
R R
R + e- N - N2 N
Figure 1.16 Reduction of aryl diazonium salts to the surface.92-93, 182
As the aryl diazonium salts are reduced through cyclic voltammetry, the peak for the reduction of the aryl diazonium salt onto the surface becomes passivated and shifts negatively as the surface continues to react towards the radicals. This loss of the
Chapter 1 | 35
reduction peak of the aryl diazonium salt is due to the electron transfer rate becoming slower as the modified layer becomes thicker, as thicker surface modification layers hinder the electron transfer through the layer.92 The saturation of GC is quicker than that seen on HOPG. This again is due to the greater reactivity of edge planes than basal planes, as HOPG in this experiment was mainly basal planes and GC, as it is amorphous, is made of both edge and basal planes. The potential window of aryl diazoniums on carbon is far greater than that of thiolates on gold, -2.6 V to 5.6 V in comparison to +0.8 V to -1.4 V when measured in an aqueous envirnoment.50, 59 The formation of the layer however is not as well defined as that of the gold-thiol monolayer and produces multilayers not monolayers.183-184 On carbon it has been seen that at least three layers of aryl diazoniums are formed on the surface.184 Both monolayers and multilayers have been observed through the reduction of aryl diazonium salts onto the carbon surface. Multilayers can occur as the radical produced reacts with the aryl rings in the ortho positions, either in solution or once they are attached to the surface (Fig.
1.17).184
R R R
R R R R R N + e- N
- N2
Figure 1.17 Formation of multilayers through diazonium salt reduction.184-186
It has been noted that the scan rate can control the number of these layers. The use of steric hindrance to control the formation of monolayers or multilayers has been
Chapter 1 | 36
investigated by Pinson and co-workers187-188 by using different aryl diazonium salts where either the para position was blocked, one of the meta positions or both the meta positions or the ortho position or a combination of the three (Fig 1.18). It was seen that those in the ortho position 2,6-dimethylbenzene diazonium (Fig 1.18a) and 2- ethylbenzene diazoniums (Fig 1.18b) showed no surface modification. Blocking of the two meta positions with a bulky butyl group limited the modification layer to a monolayer (Fig 1.18d).187-188 Aryl diazoniums modified at either the two meta positions with methyl groups (Fig 1.18c) or the ortho and para positions also with methyl groups showed multilayers (Fig 1.18e).
ab c
N2 N2 N2
d e
N2 N2
Figure 1.18 Aryl diazonium salts used to investigate steric hindrance and modification of
carbon surfaces.187-188 a) 2,6-dimethylbenzene diazoniums. b) 2-ethylbenzene diazonium. c)
3,5-dimethylbenzene diazonium. d) 3,5-dibutylbenzene diazonium. e) 2,4-dimethylbenzene
diazonium.
The layers derived by the reduction of aryl diazonium salts are highly stable to both air and heat as it was seen that the layers are still present after heating to 700 K.
The electrochemical reduction of aryl diazonium salts can be performed in one of two
Chapter 1 | 37
ways, firstly via “pre-making” the aryl diazonium salt and carrying out electrochemical reduction. Secondly with an in situ method by forming the aryl diazonium salt in solution from the aniline derivative and immediately reducing the compound to the surface.189-190 It was shown by Liu et al. that the surface produced by in situ generation of aryl diazonium salts is the same as that produced by “pre-made” aryl diazonium salts.191 It has also been seen that they can form stable layers through spontaneous formation on the surface.192-194 By simply immersing the surface into the aryl diazonium solution with an open-circuit potential, spontaneous reduction is carried out and a covalent bond is formed on the surface.176 It is yet to be understood how these spontaneously formed layers are attached. However, this spontaneous reaction does allow the patterning of the carbon surface through micro contact printing.192-193
Like the gold-alkanethiol layers it is possible to use mixed layers with aryl diazonium salts. This has been shown in a number of studies.56, 180, 193, 195 Using mixed layers gives a modified surface the ability to have a multi functional aspect, and different aspects of the surface can have differing functions, such as detecting different analytes with the same electrode. Mixed layers also have the ability to combine a biorecognition element with a diluent that not only spaces out the biorecognition element but provides resistance to non-specific protein adsorption.43, 180, 195
Aryl diazonium derived carbon surfaces have been shown to be applicable to many electrochemical sensor techniques. It has been shown that through the use of a phenyl acetate aryl diazonium derived surface the concentration of dopamine in high ascorbic acid concentrations can be measured.196 The measurement of dopamine in the presence of ascorbic acid is difficult as generally the response is small and both
Chapter 1 | 38
compounds oxidise at nearly the same potential, and dopamine can oxidise in the presence of ascorbic acid.197 Once the carbon surface is modified with phenyl acetate aryl diazonium salt dopamine is distinguishable from ascorbic acid.196
The use of aryl diazonium salts allows for the surface of the electrode to be modified with a stable, covalently bound layer. The electrochemical reduction of aryl diazonium salts provide a more stable layer over those formed from the reduction of amines and arylacetates, this is provided by the carbon-carbon bond. The stability of this modification layer and the ability to partially control the number of layers formed through differing functionalities at the ortho and para positions makes this surface modification technique useful in the construct of an affinity biosensor.
1.4.5 HYDROSILYLATION, HYDROGENATION AND THE ATTACHMENT OF
ALKENES
Although we have the ability to produce sensitive biosensors on smooth carbon surfaces, we still have to use aryl diazonium salts to attach the particular sensor parts to the surface.43 The use of aryl diazonium salts has the ability to produce multilayers instead of monolayers on the surface, which has the problem of again placing the biorecognition element and redox mediator in different environments on the sensor.
If there was a way to form controlled monolayers like the gold-thiolate derived layers, with the added stability of the aryl diazonium salts it would greatly increase the capacity of an affinity sensor. Add to these attributes the ability to pattern the surface
Chapter 1 | 39
then the possible uses of the sensor can be greatly expanded to cover multianalyte- sensors.
Silicon has the ability to be hydrogenated via the exposure to hydrofluoric acid, this means that the surface instead of being covered in oxide is covered in hydrogen.
This surface can then be exposed to alkenes and either with heat or UV activation be modified with a stable, covalently bound monolayer as was first shown by Linford et al..90, 198-200 The layer formed has a monolayer surface coverage, which can then be further modified. This can be seen in the work of Böcking et al, where they showed that a formed monolayer of alkenes can then be modified by the attachment of oligo(ethylene glycol) which reduces the amount of protein adsorbed onto the surface.78,
201-202 Hamers and co-workers have also shown that hydrolysed silicon can be used for subsequent modification with DNA strands.90
Through the use of hydrogenated diamond surfaces stable, covalently bound monolayers can be formed through the reactions of alkenes with the surface. Hamers and co-workers have shown that through the exposure of alkenes to a hydrogenated diamond surface with UV excitation at the wavelength 254 nm that the diamond surface can be modified with a monolayer.94 Hamers and co-workers203-204 investigated the process through which alkenes are covalently attached to the surface and suggested that it was not the activation of the alkene but of the surface causing ejection of a photoelectron (Fig. 1.19). The method of alkene addition to diamond surfaces is similar to that of alkene addition to silicon surfaces.205-206 It was also noted that the modification depended on the alkene used and that alkenes that have a high electron affinity are more likely to react with the surface.203 The hydrogenated amorphous
Chapter 1 | 40
carbon can also be further modified with alkenes in the similar manner to that of diamond surfaces.
Figure 1.19 Alkene addition to the surface of hydrogenated diamond surfaces. Hamers and co-
workers suggest that instead of the alkene being activated with UV light, the surfaces is
activated. UV light activates the surface causing ejection of an electron from the surface to the
alkene, this causes rearrangement of the alkene and the loss of an hydrogen of the surface
leaving an activated site for the attachment of the alkene.203-204, 207
The use of alkenes to modify hydrosilylated surfaces and diamonds surfaces would work well for an affinity biosensor as they provide a well defined stable monolayer. This thesis though is focusing on the use of carbon as and electrode surface, which rules out the use of hydrosilylated silicon for an affinity biosensor construct. It was also previously noted that diamond surfaces are not nearly smooth enough if the sensor sensitivity is to be enhanced. To be able to use alkenes on PPF as a monolayer would require the PPF to be hydrogenated or activated in a similar fashion allowing UV attachment of alkenes, this will be investigated further in chapter 5.
Chapter 1 | 41
1.5 WHICH CARBON AND WHICH MODIFICATION METHODS TO
USE?
It is the hope of this project to improve on both the electrode surface and the methods of modifying the surfaces, whilst at the same time improving the sensor construct. The use of thin carbon films or PPF will provide a near atomically smooth surface, by modifying this surface with aryl diazonium oligo(ethylene glycols) will reduce the non-specific protein adsorption. By combining these to factors it will allow the biorecognition elements to be in the same environment without hindrance from unwanted proteins. The use of iodinated PPF will allow the formation of stable monolayers on the electrode surface. These elements combined hope to produce a more sensitive affinity biosensor.
Chapter three investigates the preparation of thin carbon film electrodes and their usability for biosensors. The effect of varying the heating parameters during the pyrolysis procedure and the effect of gas flow are investigated. This chapter hopes to understand the affects of the heating profile on the pyrolysis of spin-coated photoresist to produce almost atomically smooth, electrochemically conducting carbon surfaces.
The application of these surfaces towards biosensors is also shown through the modification with 4-carboxyphenyl diazonium salt, and the attachment of the peptide
Gly-Gly-His to measure the concentration of copper.
Chapter four reports the use of new oligo(ethylene glycol) aryl diazonium salts to further investigate the reduction of protein adsorption on the thin carbon film surface.
Through the investigation of the chain length of oligo(ethylene glycol) aryl diazonium
Chapter 1 | 42
salts and the affect of the distal end on non-specific protein adsorption. By comparison to those formed on gold surfaces provides a comparison to their effectiveness.
In chapter five, iodination of the carbon surface and alkene attachment through
UV activation is used to improve surface modification, whilst retaining the surface attributes of smoothness, and electrical conductivity. By producing stable, covalently bound monolayers on the almost atomically smooth PPF surface, the two surface modification techniques of the monolayer formation from gold-thiol modification and the stability from electrochemical reduction of aryl diazonium salts have been combined. This will give the potential for a more sensitive ad stable affinity sensor than those formed previously with gold-thiol surface modification or through aryl diazonium reduction on carbon. The ability to pattern the surfaces to increase functionality is shown.
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207. Colavita, P. E.; Sun, B.; Tse, K.-Y.; Hamers, R. J., Photochemical Gafting of n-Alkenes
onto Carbon Surfaces: the Role of Photoelectron Ejection. J. Am. Chem. Soc. 2007, 129
(44), 13554-13565.
Chapter 1 | 62
Chapter Two
Experimental Methods
Chapter 2 | 63
The focus of this work is on the preparation of smooth thin carbon films and subsequent modification. This chapter describes the various instrumentation used for this project. The procedures and chemicals used are also described. Further specific experimental are described in the relevant chapters. The instrumentation used in this research is mainly electrochemical and is described in this chapter. Other experimental techniques used such as X-ray photoelectron spectroscopy (XPS), atomic force microscopy (AFM), contact angle and scanning electron microscope (SEM) are also described.
2.1 MATERIALS
2.1.1 CHEMICALS AND REAGENTS
All chemicals used were reagent grade or higher and were used as received unless otherwise stated. All aqueous buffers and solutions were prepared using Milli-Q water (18 MΩ cm; Millipore, North Ryde, Sydney).
Chemical Formula Grade Supplier
Acetone CH3COCH3 - Ajax
Acetonitrile CH3CN - Ajax
Cambridge Isotope Acetonitrile-d CD3CN 99.8% Laboratories Inc.
Ammonia solution NH3 28% Ajax
4-Aminobenzoic acid C7H7NO2 99% Sigma
Chapter 2 | 64
Chemical Formula Grade Supplier
Ascorbic acid C6H8O6 - Unilab
Celite - 501 Fluka
Cambridge Isotope Chloroform-d CDCl3 D 98.8% Laboratories Inc.
Copper (II) sulfate CuSO4•5H2O - Ajax
1-Decanol C10H22O - Sigma
N-(-3- dimethylaminopropyl)-Nʼ- C8H17N3•HCl - Sigma ethylcarbodiimide hydrochloride (EDC) Disodium hydrogen Sigma- Na2HPO4 phosphate Aldrich 98% Dipotassium hydrogen K2HPO4 Sigma- ACS phosphate Aldrich reagent
Dichloromethane CH2Cl2 - Ajax
Ethanol CH3OH - Ajax
Ethylenediaminetetraacetic (HO2C2H2)2NC2H4N(CH2CO2H)2 99% Aldrich acid EDTA
Ethyl acetate CH3CO2C2H5 - Ajax
4-Fluoro-1-nitrobenzene C6H2FNO2 99% Aldrich
Forming gas 5% H2 in 95% N2 - Air liquide
Gold chloride HAuCl4•3H2O 99.9% Aldrich
Hexa(ethylene glycol) C18H38O7 Aldrich
Hexa(ethylene Sigma- glycol)mono-11- C23H48O7S 95% Aldrich mercaptoundecyl ether
Chapter 2 | 65
Chemical Formula Grade Supplier Hexaamine ruthenium(III) Ru(NH3)6Cl3 98% Aldrich chloride N Hydroxysuccinimide C4H5NO3 98% Aldrich (NHS) Hydrochloric acid HCl 32% Ajax
Hydrogen peroxide H2O2 30% Aldrich
Hydrogen gas H2 - Air liquidé
Iodine I2 Sublimed Fluka
Isopropanol (CH3)2CHOH - Ajax
2-(N-morpholino)
ethanesulfonic C6H13NO4S 99.5% Sigma acid (MES)
Magnesium sulphate MgSO4•3H2O - Ajax
Methyl iodide CH3I - Sigma
Methanol CH3OH - Ajax
2-Mercaptoethanol C2H6OS - Sigma
Mowiol 4-88 - - polysciences
Nitric acid HNO3 70% Ajax
Nitrosonium NOBF4 - Aldrich tetrafluoroborate
Nonadiyne C9H12 98% Sigma Ammonium iron(II) (NH4)2SO4·FeSO4·6H2O - Ajax sulphate 10 % Palladium on carbon Pd - Lancaster AZ electronic Positive photoresist AZ - - materials 4620, (Japan). Potassium dihydrogen KH2PO4 >99% Aldrich phosphate
Chapter 2 | 66
Chemical Formula Grade Supplier
Potassium chloride KCl - Sigma
3-inch <100> n-type silicon Micro wafer (500-550 μm thick Materials and - - and 2.0-9.0 Ω cm Research resistivity) Consumables
Silica Grade 9385, 230-400 - Merck
Sodium chloride NaCl - Ajax
Sodium citrate C6H5Na3O7•2H2O ACS Sigma
70% in Sodium hydride NaH Aldrich oil
Sodium hydroxide NaOH - Ajax
Sodium tetrafluoroborate NaBF4 98% Aldrich
Sodium nitrite NaNO2 97% APS
Sodium sulphate Na2SO4 - Ajax
Sulphuric acid H2SO4 - Ajax
Tetrabutylammonium (CH3CH2CH2CH2)4N(BF4) 99% Aldrich tetrafluoroborate Tetrabutyl ammonium (C4H9)4N(BF4) 98% Aldrich hydrogen sulphate Tri(ethylene glycol) C7H16O4 95% Aldrich monomethylether
Tri(ethylene glycol) O(C2H4O)2C2H4OH - Aldrich Triton X - - Sigma Triethylene glycol mono- Sigma- HS(CH2)11(OCH2CH2)3OH 95% 11-mercaptoundecyl ether Aldrich
Table 2.1 A list of chemicals and reagents used.
Chapter 2 | 67
2.1.2 PREPARATION OF BUFFERS AND STANDARD SOLUTIONS
A range of buffer solutions was prepared for this work. The pH of the buffer solutions was measured using a Futura pH electrode connected to a pH meter (both from Beckman Instruments, Fullerton, CA, USA). The pH meter was calibrated using standard pH 4.0 (± 0.05) and pH 7.0 (± 0.05) buffer solutions (Asia Pacific Specialty,
Sydney, Australia). Buffer solutions used were 50 mM phosphate buffer (pH 7.0) with
1.0 M KCl, 100 mM MES (pH 6.8), 50 mM ammonium acetate (pH 7.0) with 50 mM
NaCl and phosphate buffered saline (PBS).
Peptide modification was carried out in 100 mM MES buffer (pH 6.8).
Electrochemical measurements of peptide-modified electrodes were carried out using 50 mM ammonium acetate buffer (pH 7.0) with 50 mM NaCl. The accumulation of copper was carried out in stock copper sulphate solutions made with 50 mM ammonium acetate buffer (pH 7.0).
For the exposure of modified PPF and gold surfaces to BSA-FITC, a solution of
BSA-FITC in PBS was used. PBS was prepared from sodium chloride (8 g, 0.14 mol), potassium chloride (0.2 g, 2.7 mmol), disodium hydrogen phosphate (1.44 g, 0.010 mol) and potassium dihydrogen phosphate (0.24 g, 1.8 mmol) in Milli-Q water (1 L) at pH
7.4.
Electrochemical measurements to investigate the affect of iodination and modification with alkenes and aryl diazonium salts were carried out in phosphate buffer
Chapter 2 | 68
with 1.0 M KCl. Potassium dihydrogen phosphate (1.7 g, 9.8 mmol), dipotassium hydrogen phosphate (2.2 g, 16.2 mmol) and potassium chloride (3.7 g, 50 mmol).
Solutions of the redox species, 10 mM hexamine ruthenium(III) chloride, 10 mM
Potassium ferricyanide, and 10 mM ascorbic acid, were all made with 50 mM phosphate buffer (pH 7.0) and 1.0 M KCl unless otherwise stated.
2.2 INSTRUMENTATION
2.2.1 ANALYSIS
2.2.1.1 CHARACTERISATION OF SYNTHETIC COMPOUNDS
2.2.1.1.1 NMR
1H NMR spectra were obtained on a Bruker DPX300F (300 MHz) spectrometer.
Data is reported as follows: chemical shifts (δ) are measured in parts per million (PPM) down field from TMS; multiplicity: observed coupling constants (J) in Hertz (Hz).
Multiplicities are reported as singlet (s), broad singlet (bs), doublet (d), broad doublet
(bd), triplet (t), broad triplet (bt), quartet (q), doublet of doublets (dd), doublet of doublet of doublets (ddd), doublet of triplets (dt), doublet of doublet of triplets (ddt), pentet (p), heptet (h), multiplet (m), and double multiplet (dm).
13C NMR spectra were obtained on a Bruker DPX300F (75.6 MHz) spectrometer. C13 chemical shifts (δ) were reported in parts per million (PPM) down field from TMS.
Chapter 2 | 69
2.2.1.2 SURFACE ANALYSIS
2.2.1.2.1 ELECTROCHEMISTRY
The main experimental technique used in this body of work has been voltammetric measurements. This is the application of a potential to an electrochemical cell and the monitoring of the output current, as can be observed in cyclic voltammetry.
In voltammetry, a three electrode cell system is used. The cell is then connected to a potentiostat, which controls the input waveform and acts as a current measuring device.
The three electrodes used are a working electrode, counter electrode, and reference electrode. The potential applied to the working electrode is measured relative to the reference electrode. An electrochemical current of a species can be measured upon applying a potential that can cause its oxidation or reduction.
Electrochemical measurements were predominantly performed with an Autolab
PGSTAT 12 potentiostat (Eco Chemie, Netherlands) interfaced to a personal computer.
Data acquisition was performed using GPES and Nova software. Cyclic voltammetry and Osteryoung square wave voltammetry experiments were carried out with a conventional three electrode system, comprising a bare or modified working electrode, a platinum flag counter electrode and a Ag|AgCl 3.0 M NaCl reference electrode (from
Bioanalytical Systems Inc., Lafayette, IN, USA). All potentials are reported versus this reference at 25°C unless otherwise stated.
Chapter 2 | 70
a
b
Figure 2.1 a) Autolab potentiostat used for electrochemical measurements. b)
Electrodes used from right to left PPF, GC, reference and counter.
Redox species that either are in solution or attached to the surface can be detected from the current flowing between the working electrode and counter electrode.
The working electrodes were either Pyrolysed photoresist films (PPF), as prepared per the general procedure discussed in section 2.3.1.1 or as described per chapter, glassy carbon (GC) electrodes (Bioanalytical Systems Inc., Lafayette, USA), and gold foil.
Chapter 2 | 71
2.2.1.2.1.1 Cyclic Voltammetry
Cyclic voltammetry (CV) is a potential sweep technique.1-2 The potential is swept back and forth between two potential limits (E1 and E2) at a set sweep rate, otherwise known as the scan rate (Vs-1), and is the rate of change of potential with time
(Fig. 2.1). The current is measured as the potential is swept continuously between E1 and E2. The use of multiple scans can give an indication to the stability of the redox species.3 The variation of current with scan rate can give an indication as to whether the redox species is surface bound or in solution.1-2
a
b
Figure 2.1 a) Potential-time profile for cyclic voltammetry. b) Representation of a current (I)
vs potential (E) plot for cyclic voltammetry.
Chapter 2 | 72
2.2.1.2.1.2 Osteryoung Square Wave Voltammetry
Osteryoung square wave voltammetry (OSWV) is a sensitive technique, combining large amplitude square wave modulation with a staircase waveform (Fig.
2.2a).4-6 Higher sensitivity is achieved by removing the background currents. The current is sampled at the end of each pulse; the forward current sampled at t1 and the reverse current at t2. The net current is the difference between the two (Fig 2.2b) and removes the response due to the charging current.6 The redox species is continuously reduced and oxidised. The conditions for OSWV were a pulse amplitude of 0.025 V, a step of 0.004 V and frequency of 25 Hz.
a
b
Figure 2.2 a) Diagram of the square wave potential waveform where Esw is the pulse
amplitude, ΔE is the step height and τ is the square wave period. b) Representative ΔI vs E plot
for OSWV.
Chapter 2 | 73
2.2.1.2.2 CONTACT ANGLE
All contact angles were measured on a ramé-hart standard contact angle goniometer and data acquisition collected on a personal computer. The angles were processed with dropimage.
The contact angle can be measured by producing a drop of liquid on a solid surface. For these studies only milli-Q is used. The angle formed between the liquid/solid interface and the solid/air interface and the surface of the interface is the contact angle (Fig 2.3).7 The contact angle is measured using the Young equation
(equation 1.1) and results from the interface/surface tensions between the water and solid surface surrounded by air.
Figure 2.3 Contact angle of a water droplet on a solid surface. γ1 is the solid/water interface
free energy, γ2 is the solid surface free energy and γ12 is the water surface free energy.
γ 2 = γ12 +γ1 cosθ equation 1.1
A water drop with a large contact angle is hydrophobic (Fig 2.4a), and a drop with a small contact angle is hydrophilic (Fig 2.4b). By measuring the advancing and
Chapter 2 | 74
receding angles information about the surface topology, i.e. surface modification heterogeneity, effect of surface treatments and cleanliness, can be gained. The advancing angle can be measured by adding volume to the drop without increasing the surface area of the drop (Fig. 2.4c) and the receding angle is the reverse where volume is removed without changing the surface area (Fig 2.4d). The difference between the two gives the hysteresis.7
a b