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LIST OF CONTRIBUTORS xv
PREFACE xvii
PART I FUNDAMENTALS OF NEURAL PROSTHESES 11 The Historical Foundations of Bionics 3N. Donaldson and G.S. Brindley
1.1 Bionics Past and Future 3
1.2 History in 1973 5
1.2.1 Biomaterials 5
1.2.2 Nerve stimulation and recording 6
1.2.3 Transistors 8
1.2.4 Conclusion 9
1.3 Anaesthesia 9
1.4 Aseptic Surgery 10
1.5 Clinical Observation and Experiments 10
1.6 Hermetic Packages 13
1.6.1 Vacuum methods 14
1.6.2 Welding 15
1.6.3 Glass 15
1.6.4 Glass ceramics and solder glasses 16
1.6.5 Ceramics 18
1.6.6 Microcircuit technologies 19
1.6.7 Leak testing 20
1.7 Encapsulation (Electrical Insulation) 20
1.7.1 Insulation 20
1.7.2 Underwater insulation 21
1.7.3 Silicones 21
1.7.4 Primers 24
1.8 Early Implanted Devices 27
1.9 Afterword 29
References 35
2 Development of Stable Long-term Electrode Tissue Interfaces for Recording and Stimulation 38J. Schouenborg
2.1 Introduction 38
2.2 Tissue Responses in the Brain to an Implanted Foreign Body 39
2.2.1 Acute tissue responses 39
2.2.2 Chronic tissue responses 40
2.2.3 On the importance of physiological conditions 40
2.3 Brain Computer Interfaces (BCI) - State-of-the-Art 41
2.4 Biocompatibility of BCI - on the Importance of Mechanical Compliance 42
2.5 Novel Electrode Constructs and Implantation Procedures 45
2.5.1 Methods to implant ultraflexible electrodes 45
2.5.2 Surface configurations 46
2.5.3 Matrix embedded electrodes 47
2.5.4 Electrode arrays encorporating drugs 49
2.6 Concluding Remarks 50
Acknowledgements 51
References 51
3 Electrochemical Principles of Safe Charge Injection 55S.F. Cogan, D.J. Garrett, and R.A. Green
3.1 Introduction 55
3.2 Charge Injection Requirements 56
3.2.1 Stimulation levels for functional responses 56
3.2.2 Tissue damage thresholds 56
3.2.3 Charge injection processes 58
3.2.4 Capacitive charge injection 58
3.2.5 Faradaic charge injection 60
3.2.6 Stimulation waveforms 61
3.2.7 Voltage transient analysis 63
3.3 Electrode Materials 70
3.3.1 Non-noble metal electrodes 70
3.3.2 Noble metals 70
3.3.3 High surface area capacitor electrodes 70
3.3.4 Three-dimensional noble metal oxide films 71
3.4 Factors Influencing Electrode Reversibility 71
3.4.1 In vivo versus saline charge injection limits 71
3.4.2 Degradation mechanisms and irreversible reactions 72
3.5 Emerging Electrode Materials 73
3.5.1 Intrinsically conductive polymers 73
3.5.2 Carbon nanotubes and conductive diamond 76
3.6 Conclusion 80
References 80
4 Principles of Recording from and Electrical Stimulation of Neural Tissue 89J.B. Fallon and P.M. Carter
4.1 Introduction 89
4.2 Anatomy and Physiology of Neural Tissue 90
4.2.1 Active neurons 91
4.3 Physiological Principles of Recording from Neural Tissue 94
4.3.1 Theory of recording 94
4.3.2 Recording electrodes 95
4.3.3 Amplification 98
4.3.4 Imaging 100
4.4 Principles of Stimulation of Neural Tissue 101
4.4.1 Introduction 101
4.4.2 Principles of neural stimulator design 101
4.4.3 Modelling nerve stimulation 104
4.4.4 The activating function 106
4.4.5 Properties of nerves under electrical stimulation 107
4.5 Safety of Electrical Stimulation 110
4.5.1 Safe stimulation limits 110
4.5.2 Metabolic stress 112
4.5.3 Electrochemical stress 114
4.6 Conclusion 117
References 117
PART II DEVICE DESIGN AND DEVELOPMENT 121
5 Wireless Neurotechnology for Neural Prostheses 123A. Nurmikko, D. Borton, and M. Yin
5.1 Introduction 123
5.2 Rationale and Overview of Technical Challenges Associated with Wireless Neuroelectronic Interfaces 126
5.3 Wireless Brain Interfaces Require Specialized Microelectronics 129
5.3.1 Lessons learned from cabled neural interfaces 129
5.3.2 Special demands for compact wireless neural interfaces 130
5.4 Illustrative Microsystems for High Data Rate Wireless Brain Interfaces in Primates 133
5.5 Power Supply and Management for Wireless Neural Interfaces 140
5.6 Packaging and Challenges in Hermetic Sealing 143
5.7 Deployment of High Data Rate Wireless Recording in Freely Moving Large Animals 146
5.7.1 Sample Case A: Implant in freely moving minipigs in home cage 147
5.7.2 Sample Case B: Implant in freely moving non-human primate in home cage 148
5.7.3 Case C: External head mounted wireless neurosensory in freely moving non-human primates 149
5.8 Summary and Prospects for High Data Rate Brain Interfaces for Neural Prostheses 153
Acknowledgements 157
References 157
6 Preclinical testing of Neural Prostheses 162D. McCreery
6.1 Introduction 162
6.2 Biocompatibility Testing of Neural Implants 163
6.3 Testing for Mechanical and Electrical Integrity 165
6.4 In vitro Accelerated Testing and Accelerated Aging of Neural Implants 166
6.5 In vivo Testing of Neural Prostheses 171
6.6 Conclusion 181
References 182
PART III CLINICAL APPLICATIONS 187
7 Auditory and Visual Neural Prostheses 189R.K. Shepherd, P.M. Seligman, and M.N. Shivdasani
7.1 Introduction 189
7.2 Auditory Prostheses 190
7.2.1 The auditory system 190
7.2.2 Hearing loss 191
7.2.3 Cochlear implants 191
7.2.4 Central auditory prostheses 195
7.2.5 Combined electric and acoustic stimulation 198
7.2.6 Bilateral cochlear implants 198
7.2.7 Future directions 199
7.3 Visual Prostheses 199
7.3.1 The visual system 199
7.3.2 Vision loss 201
7.3.3 Retinal prostheses 201
7.3.4 Central visual prostheses 204
7.3.5 Perceptual effects of visual prostheses 204
7.3.6 Future directions 206
7.4 Sensory Prostheses and Brain Plasticity 206
7.5 Conclusions 207
Acknowledgements 207
References 207
8 Neurobionics: Treatments for Disorders of the Central Nervous System 213H. McDermott
8.1 Introduction 213
8.2 Psychiatric Conditions 215
8.2.1 Obsessive-compulsive disorder 215
8.2.2 Major depression 218
8.3 Movement Disorders 219
8.3.1 Essential Tremor 219
8.3.2 Parkinson's disease 219
8.3.3 Dystonia 220
8.3.4 Tourette's syndrome 221
8.4 Epilepsy 221
8.5 Pain 223
8.6 Future directions 223
Acknowledgements 227
References 227
9 Brain Computer Interfaces 231D.M. Brandman and L.R. Hochberg
9.1 Introduction 231
9.2 Motor Physiology 232
9.2.1 Neurons are the fundamental unit of the brain 232
9.2.2 Movement occurs through coordinated activity between multiple regions of the nervous system 233
9.2.3 Motor cortex: a first source for iBCI signals 234
9.2.4 The parietal cortex is implicated in spatial coordination 237
9.2.5 The premotor and supplementary motor cortices are engaged in movement goals 237
9.2.6 Functional brain organization is constantly changing 238
9.2.7 Section summary 238
9.3 The Clinical Population for Brain Computer Interfaces 239
9.3.1 Paralysis may result from damage to the motor system 239
9.3.2 Individuals with spinal cord injuries develop motor impairments that may impact hand function 240
9.3.3 Individuals with LIS develop motor impairment that impacts communication 241
9.4 BCI Modalities 242
9.4.1 Other neural activity-based signals for BCI devices 244
9.4.2 Electrodes placed in the cortex record action potentials from neurons 245
9.4.3 Raw voltage signals are processed into spikes 246
9.5 BCI Decoding and Applications 247
9.5.1 BCI decoders convert neural information into control of devices 248
9.5.2 BCI decoders allow for the control of prosthetic devices 249
9.6 Future Directions 252
9.6.1 Scientific and engineering directions for developing BCI technology 253
9.6.2 Clinical directions for development of BCI technology 254
9.7 Conclusion 255
References 255
PART IV COMMERCIAL AND ETHICAL CONSIDERATIONS 265
10 Taking a Device to Market: Regulatory and Commercial Issues 267J.L. Parker
10.1 Introduction 267
10.2 Basic Research 268
10.3 Preclinical Development 285
10.4 Clinical Trials and Approval to Sell 285
10.5 Building a Business not a Product 289
10.6 Conclusions 291
References 292
Webliography 292
11 Ethical Considerations in the Development of Neural Prostheses 294F.J. Lane, K.P. Nitsch, and Marcia Scherer
11.1 Introduction 294
11.2 Individuals with Disabilities and Technology Development 295
11.2.1 Assistive technology in the context of disability 295
11.2.2 International classification of functioning, disability and health 295
11.2.3 "Nothing About Us, Without Us" 297
11.2.4 Matching Person and Technology: applications to neural prosthesis development 299
11.2.5 Disability culture: the cochlear implant 301
11.3 Ethical Principles of Biomedical Research 301
11.3.1 Principles of biomedical ethics 302
11.3.2 Informed consent in clinical research trials 306
11.3.3 Information and informed consent 306
11.3.4 The process of obtaining informed consent 307
11.3.5 Decision-making 308
11.3.6 Influence of culture and country 308
11.3.7 What information is material? 308
11.3.8 Restoration versus enhancement and mental change 313
11.4 Conclusions 314
References 315
Appendix: Examples of Companies Developing and/or Marketing
Bionic Devices 319
Index 327
Nick Donaldson and Giles S. Brindley
Implanted Devices Group, Department of Medical Physics & Bioengineering, University College London, London, UK
In 1973, Donaldson and Davis published a paper called "Microelectronic devices for surgical implantation" in which they listed neuroprostheses in use and under development: pacemakers for the heart (fixed-rate, atrial-triggered and demand), incontinence devices, visual prostheses, dorsal column stimulators and electromyogram (EMG)) telemeters1. The field of bionics was then very young, the idea of surgically implanting an electronic device was new and very few people had worked on the technical difficulties entailed. Only pacemakers were then commercial products and there were no regulations in force. Now, 40 years later, there are many more types of device, both in clinical use and under development. A number of these devices will be described in Chapters 7-9 and include implants for addressing sensory loss (e.g. hearing, sight, balance), disorders of the brain and the mind (e.g. epilepsy, migraine, chronic pain, depression), as well as brain-machine interfaces. Manufacturing these devices and going through the process of regulation is now a multi-billion dollar industry.
The year 2013 may be remembered as the year in which GlaxoSmithKline (GSK) announced that they were to invest in the development of neurobionic devices, which they call Electroceuticals or Bioelectronic Medicines2 (Famm et al. 2013; Birmingham et al. 2014). The notion is that these will interact with the visceral nerves that innervate the internal organs to treat specific diseases. These diseases are not normally thought of as neurological (e.g. inflammation), but nevertheless there is some neural control. The announcement by GSK shows that the company thinks that implanted devices may become an alternative to some drug treatments. The motivations for their development no doubt include the rising costs of new drugs, better targeting of the causes of disease, and the realisation that implants might treat some of the increasingly prevalent diseases that threaten to overwhelm healthcare budgets (obesity, diabetes). They cite an example as the recent trial of a treatment for rheumatoid arthritis by stimulation of the vagus nerve (Koopman 2012). Some of the new implants will require surgical techniques new to human surgery, for example the splitting of spinal nerve roots in continuity into many fine strands. Only time will tell whether this vision is realistic, but it shows the huge rise in confidence that implanted bionic devices may be practicable and important in future healthcare.
The first electrical device implanted into a patient was the cardiac pacemaker of Elmqvist (1958), so the field is now nearly 60 years old (Figure 1.1). While Chapters 7-9 will review some of the types of implant with respect to their clinical function, Chapters 2-6 will review the field on which implant engineering is based, much of which has been built in this 60-year period. If we consider that the construction work in that period is the history of neurobionics, the purpose of this chapter is to look back to the pre-history, the foundation of the field, from the time before work began and probably before it was even conceived.
Figure 1.1 Elmqvist-Senning pacemaker of 1958. It is powered by two nickel-cadmium cells (arrowhead) which can be recharged by induction. The two transistors are on the right (arrows). The encapsulant is epoxy resin. An external valve oscillator was used for recharging at a frequency of 150 kHz. Scale bar = 1 inch.
We have worked in London during the historical period (see Box 1.6: MRC Neurological Prostheses Unit) and the story is slanted toward our view of the significant technology.
Donaldson and Davies (1973) suggested that neurological prostheses were the confluence of four streams of development: biomaterials (known from literature dating as far back as 1000 bc), electrical stimulation of nerves (Galvani 1791), electrophysiological recording (Matteucci 1842) and transistors (1948).
A textbook by Susrata from 1000 bc describes the use of catgut for sutures. In Europe, from the 16th to the mid-19th century, linen and silk were the normal materials for sutures and ligatures; for sutures, horse hair, catgut and cotton were tried occasionally, and for ligatures, strips of leather. But these seem to have been passing fashions, and most surgeons continued to use silk or linen. Whatever the material, it was not a biomaterial in the modern sense; it was not expected to remain in the body for years, but either to be removed by the surgeon within a week or two, or to be extruded through the skin as part of the healing process within a few months.
The first internal fixation of a fracture with a metal plate and screws was performed by Lane in 1895, but Lane's plate and screws were of ordinary steel, and would certainly corrode. Stainless steel (18-8 18% chromium, 8% nickel) was patented in 1912, but the original stainless steel corroded badly in sea-water. It was not until about 1926 that a modified stainless steel, 18-8-SMo, which had an additional 2-4% of molybdenum was developed, which resisted corrosion in sea-water and so could reasonably be expected to remain uncorroded in the body. This stainless steel was widely used in the internal fixation of fractures in the 1930s, and sometimes remained uncorroded for years (Haase 1937).
The variability remained mysterious, but it was made unimportant by the invention (1932) and introduction into bone surgery (1937) of Vitallium, an alloy of cobalt, chromium and molybdenum, which has never been reported as corroding in the body (Venable and Stuck (1938). The first widely successful artificial hip (though not absolutely the first artificial hip) was the cup arthroplasty (Smith-Peterson 1939). It used a Vitallium cup which was not bonded either to the head of the femur or to the acetabulum. Modern artificial hips have a ball bonded to the femur and a cup bonded to the pelvis. Problems of fixing the ball and cup to the bones and of wear at the articulating surfaces have been largely overcome. For artificial finger joints, it has been possible to avoid articulating surfaces by using adequately flexible silicones (Williams and Roaf 1973). Silicones were first used in medicine as coatings for syringe needles for reduced blood clotting (1946). In the same year, silicone rubbers were first used for surgical repairs and, in 1956, for the first hydrocephalus shunts (Colas and Curtis 2004). Thus by 1973 the field of biomaterials was established as a collaboration between surgeons, biologists and materials scientists, who had made progress by innovation with new materials, better designs and improved surgical techniques.
Less was known about implantable electrical materials: the first electrical implant in an animal was described by Louks (1933) and that was simply a coil, insulated with Collodion varnish, connected directly to electrodes; the experiments continued for 12 days. Clearly the idea that artificial materials can be implanted into the body was well established by 1973, but the specific difficulties of electrical devices were new.
It was established by Galvani in 1791 that nerves could be stimulated. The idea that nerves carried sensory messages to the brain and commands back to the muscles was stated in the 1st century ad by Galen, who argued for it against contrary opinions of some classical Greek authorities; he thought that the nerve signal was transmitted by fluid flow. However, when Leeuwenhoek looked at nerves in cross-section using his new microscope (1674), he was not convinced that there was any tubular structure to carry the fluid.
Newton wrote in 1678 about "a certain most subtle spirit which pervades and lies hid in all gross bodies, by the force and action of which . all sensation is excited and the members of animal bodies move at the command of the will, namely by the vibrations of this spirit, mutually propagated along the solid filaments of the nerves, from the outward organs of sense to the brain, and from the brain into the muscles." For the optic nerve, Newton repeated this opinion in his "Opticks" (Newton 1730): "Do not the rays of light in falling upon the bottom of the eye excite vibrations in the tunica retina? Which vibrations, being propagated along the solid fibres of the optic nerve, cause the sense of seeing?"
Since 1745, when the Leyden jar was invented, it was well known that electricity passing through human skin causes strong and often painful sensations. At least since 1738 (Swammerdam) it was known that if, in a preparation consisting of a frog's gastrocnemius muscle and sciatic nerve and little else, the nerve was pinched, contraction of the muscle followed immediately. Galvani (1791), using just such a preparation, showed that passing electricity from a frictional machine through the nerve had the same effect. He also did experiments using dissimilar metals, which he misinterpreted. Volta confirmed and extended Galvani's experiments, interpreted them correctly, and used them as the basis of his invention of the battery (1800), which quickly led to the discovery of the relation between electricity and magnetism, the work of Oersted,...
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