5. Cochlear Implants
Third Edition
Susan B. Waltzman, PhD
Marica F. Vilcek Professor of Otolaryngology
Department of Otolaryngology-Head and Neck Surgery
Co-Director, NYU Cochlear Implant Center
New York University School of Medicine
NYU Langone Medical Center
New York, New York
J. Thomas Roland Jr., MD
Professor of Otolaryngology and Neurosurgery
Mendik Foundation Professor and Chairman
Department of Otolaryngology-Head and Neck Surgery
Co-Director, NYU Cochlear Implant Center
New York University School of Medicine
NYU Langone Medical Center
New York, New York
Thieme
New York • Stuttgart • Delhi • Rio
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7. Contents
Preface .. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . vii
Contributors .. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . viii
Acknowledgments. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . xii
1 History of the Cochlear Implant... . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 1
Marc D. Eisen
2 Genetics of Hearing Loss and Predictors of Cochlear Implant Outcome ..............
Robert W. Eppsteiner, Richard K. Gurgel, and Richardj.H. Smith
3 Consequences of Deafness and Electrical Stimulation on the Peripheral and Central
10
Auditory System.. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 19
james B. Fallon, David K. Ryuga, and Robert K. Shepherd
4 Auditory Neuroplasticity .. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 38
Robert C. Froemke, Selena E. Heman-Ackah, and Susan B. Waltzman
5 Mimicking Normal Auditory Functions with Cochlear Implant Sound Processing: Past,
Present, and Future .. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 47
Ward R. Drennan, Mario A. Svirsky, Matthew B. Fitzgerald, andjay T. Rubinstein
6 Expanding Criteria for the Evaluation of Cochlear Implant Candidates.. . . . . . . . . . . . . . 61
Susan Arndt, Roland Laszig, Antje Aschendorff. and Rainer Beck
7 Principles of Cochlear Implant Imaging .. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 74
Andrewj. Fishman and Selena E. Heman-Ackah
8 Intraoperative Monitoring During Cochlear Implantation ... . . . . . . . . . . . . . . . . . . . . . . 100
Mauro K. Cosetti
9 The History of Cochlear Implant Electrode Design... . . . . . . . . . . . . . . . . . . . . . . . . . . . . 108
Maja Svrakic andj. Thomas RolandJr.
10 Cochlear Implant Surgical Technique ... . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 118
Peter S. Roland andj. Thomas RolandJr.
11 New Horizons in Surgical Technique .. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 128
Theodore R. McRackan, Robert F. Labadie, j. Thomas RolandJr., and David S. Haynes
12 A Global View of Device Reliability... . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 132
Rolf-Dieter Battmer
13 Revision Cochlear Implantation .. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 141
David R. Friedmann, j. Thomas RolandJr., and Susan B. Waltzman
14 Advancements in Cochlear Implant Programming............................... 148
William H. Shapiro
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8. vi
15 Auditory and Linguistic Outcomes in Pediatric Cochlear Implantation .. . . . . . . . . . . . . . 158
Gerard M. O'Donoghue and David B. Pisani
16 Auditory Outcomes in the Adult Population
Oliver F. Adunka, Margaret T. Dillon, and Craig A. Buchman
167
17 Therapeutic Approaches Following Cochlear Implantation .. . . . . . . . . . . . . . . . . . . . . . . 182
Warren Estabrooks, K. Todd Houston, and Karen Maclver-Lux
18 Acoustic and Electric Speech Processing .. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 194
Bruce}. Gantz, Sarah E. Mowry, Rick F. Nelson, Sean 0. McMenomey, Chris}. james, and Bernard Fraysse
19 Music Perception .. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 203
Alexis Roy and Charles}. Limb
20 Auditory Brainstem Implants .. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 212
Shoun D. Rodgers, john G. Golfinos, and}. Thomas RolandJr.
21 Applying Cochlear Implant Technology to Tinnitus and Vestibular Interventions... . . . . 221
justin S. Golub, james 0. Phillips, andjay T. Rubinstein
22 The Impact of Cochlear Implantation on the Recipient's Health-Related Quality of Life... . 235
Selena E. Heman-Ackah
23 Future Technology .. . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . . 248
Susan B. Waltzman and}. Thomas RolandJr.
Index...................................................................... 249
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9. Preface
This fully updated third edition of Cochlear Implants repre
sents the superb efforts of many individuals who have
contributed significantly to the field. We have built on the
previous edition by adding new chapters relating to genet
ics, neuroplasticity, expanding criteria for implantation, the
application of implant technology to tinnitus and vestibular
issues, music perception, intraoperative monitoring, device
reliability and reimplantation, and the use of quality-of-life
and outcome measures-areas that occupy the forefront of
cochlear implantation. Other chapters have been revised to
reflect current research and clinical applications and pro
vide the most recent information related to the clinical and
translational sciences that continue to advance this exciting
technology and its implementation. Patient outcomes, can
didacy criteria, technical design, surgical technique, and
programming and processing concepts are constantly pro
gressing, and increasing numbers of individuals are gaining
significant benefit. Our goal was to create a book that will
provide both experienced and new and budding otolaryngol
ogists-head and neck surgeons, neurotologists, audiologists,
neuroscientists, neurophysiologists, speech pathologists, tea
chers of the deaf, psychologists, and others interested in
cochlear implants with an extraordinary resource for years
to come. Thanks to the contributors and their hard work,
dedication, and attention to detail, we feel that this goal has
been exceeded, and we are most grateful to all involved.
vii
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10. viii
Contributors
Oliver F. Adunka, MD, FACS
Associate Professor
OtologyfNeurotology/Skull Base Surgery
Department of Otolaryngology-Head and Neck Surgery
University of North Carolina at Chapel Hill
Chapel Hill, North Carolina
Susan Arndt, MD
Department of Otorhinolaryngology
Implant Center Freiburg
University of Freiburg
Freiburg, Germany
Antje Aschendorff, MD
Associate Professor
Department of Otorhinolaryngology
Head of Implant Center Freiburg
University of Freiburg
Freiburg, Germany
Rolf-Dieter Battmer, PhD
Professor and Director
Center for Clinical Technology Research
Trauma Hospital
Berlin, Germany
Rainer Beck, MD
Department of Otorhinolaryngology
Implant Center Freiburg
University of Freiburg
Freiburg, Germany
Craig A. Buchman, MD, FACS
Professor and Vice Chairman for Clinical Affairs
Chief OtologyfNeurotology/Skull Base Surgery
Department of Otolaryngology-Head and Neck Surgery
University of North Carolina at Chapel Hill
Chapel Hill, North Carolina
Maura K. Cosetti, MD
Assistant Professor and Co-Director of Otology/Neurotology
Departments of Otolaryngology-Head and Neck Surgery
and Neurosurgery
Louisiana State University Health Sciences Center
Shreveport, Louisiana
Margaret T. Dillon, AuD, CCC-A, F-AAA
Assistant Professor
Department of Otolaryngology-Head and Neck Surgery
University of North Carolina at Chapel Hill
Chapel Hill, North Carolina
Ward R. Drennan, PhD
Virginia Merrill Bloedel Hearing Research Center
Department of Otolaryngology-Head and Neck Surgery
University of Washington
Seattle, Washington
Marc D. Eisen, MD, PhD
Adjunct Clinical Assistant Professor
Department of Otorhinolaryngology-Head and Neck
Surgery
University of Pennsylvania
Philadelphia, Pennsylvania
Robert W. Eppsteiner, MD
Otolaryngology Resident T32 Research Fellow
Department of Otolaryngology-Head and Neck Surgery
University of Iowa Hospitals and Clinics
Iowa City, Iowa
Warren Estabrooks, M.Ed., Dip.Ed.Deaf, LSLS Cert. AVT
President and CEO
WE Listen International Inc.
Toronto, Ontario, Canada
james B. Fallon, PhD
Bionics Institute
Melbourne, Australia
and
Department of Medical Bionics
University of Melbourne
Melbourne, Australia
AndrewJ. Fishman, MD
Director of Neurotology & Cranial Base Surgery
Director, Cochlear Implant Program
Cadence Neuroscience Institute
Winfield, Illinois
and
International Visiting Professor of Otolaryngology-Head &
Neck Surgery
NATO Military Hospital, Bydgoszcz, Poland
Professor of Pediatric Otolaryngology
Children's Hospital of Bydgoszcz
Bydgoszcz, Poland
Matthew B. Fitzgerald, PhD, CCC-A
Department of Otolaryngology-Head and Neck Surgery
New York University School of Medicine
NYU Langone Medical Center
New York. New York
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11. Professor Bernard Fraysse
Chairman of the ENT Department
H6pital Purpan
Toulouse, France
David R. Friedmann, MD
Department of Otolaryngology-Head and Neck Surgery
New York University School of Medicine
NYU Langone Medical Center
New York, New York
Robert C. Froemke, PhD
Assistant Professor of Neuroscience and Otolaryngology
Department of Otolaryngology-Head and Neck Surgery
New York University School of Medicine
NYU Langone Medical Center
New York, New York
Bruce j. Gantz, MD, FACS
Professor and Head, Department of Otolaryngology-Head
and Neck Surgery
Brian F. McCabe Distinguished Chair in Otolaryngology
Head and Neck Surgery
Professor, Department of Neurosurgery
University of Iowa Carver College of Medicine
Iowa City, Iowa
john G. Golfinos, MD
Chairman, Department of Neurosurgery
Associate Professor of Neurosurgery and Otolaryngology
New York University School of Medicine
NYU Langone Medical Center
New York, New York
justin S. Golub, MD
OtologyfNeurotologyfLateral Skull Base Surgery Fellow
Department of Otolaryngology-Head and Neck Surgery
University of Cincinnati
Cincinnati Children's Hospital Medical Center
Cincinnati, Ohio
Richard K. Gurgel, MD
Assistant Professor
Division of Otolaryngology-Head and Neck Surgery
University of Utah
Salt Lake City, Utah
David S. Haynes, MD, FACS
Otology Group of Vanderbilt
Vanderbilt University Medical Center
Nashville, Tennessee
Selena E. Heman-Ackah, MD, MBA
Otology, Neurotology and Skull Base Surgery
Medical Director of Otology, Neurotology, and Audiology
Division of Otolaryngology-Head and Neck Surgery
Department of Surgery
Beth Israel Deaconess Medical Center
Harvard Medical School
Boston, Massachusetts
K. Todd Houston, PhD, CCC-SLP, LSLS Cert. AVT
School of Speech-Language Pathology and Audiology
University of Akron
Akron, Ohio
Chris j. james, PhD
CHU Toulouse-Purpan
and
Cochlear France SAS
Toulouse, France
Robert F. Labadie, MD, PhD
Professor and Director of Research
Department of Otolaryngology-Head and Neck Surgery
Professor, Department of Biomedical Engineering
Vanderbilt University
Nashville, Tennessee
Roland Laszig, MD
Head, Department of Otorhinolaryngology
Implant Center Freiburg
University of Freiburg
Freiburg, Germany
Charlesj. Limb, MD
Associate Professor
Department of Otolaryngology-Head and Neck Surgery
johns Hopkins Hospital
johns Hopkins University School of Medicine
Peabody Conservatory of Music
Baltimore, Maryland
Karen Maclver-Lux, MA, Aud(C), LSLS Cert. AVT
Director
Maclver-Lux Auditory Learning Services
King City, Ontario, Canada
Sean 0. McMenomey, MD
Professor of Otolaryngology and Neurosurgery
Department of Otolaryngology-Head and Neck Surgery
New York University School of Medicine
NYU Langone Medical Center
New York, New York
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12. X
Theodore R. McRackan, MD
Department of Otolaryngology-Head and Neck Surgery
Vanderbilt University
Nashville, Tennessee
Sarah E. Mowry, MD
Department of Otolaryngology
Georgia Regents University
Augusta, Georgia
Rick F. Nelson, MD, PhD
Department of Otolaryngology-Head and Neck Surgery
University of Iowa Hospitals and Clinics
Iowa City, Iowa
Gerard M. O'Donoghue, MD
Consultant Neuro-Otologist
Nottingham University Hospitals NHS Trust
Queens Medical Centre
Honorary Professor of Otology and Neurotology
University of Nottingham
Co-founder, Nottingham Hearing Biomedical
Research Unit
Nottingham, United Kingdom
james 0. Phillips, PhD
Research Associate Professor
Department of Otolaryngology-Head and Neck Surgery
University of Washington
Seattle, Washington
David B. Pisoni, PhD
Distinguished Professor of Psychological and
Brain Sciences
Chancellor's Professor of Cognitive Science
Department of Psychological and Brain Sciences
Indiana University
Bloomington, Indiana
Shaun D. Rodgers, MD
Department of Neurosurgery
New York University School of Medicine
NYU Langone Medical Center
New York, New York
]. Thomas RolandJr., MD
Professor of Otolaryngology and Neurosurgery
Mendik Foundation Professor and Chairman
Department of Otolaryngology-Head and Neck Surgery
Co-Director, NYU Cochlear Implant Center
New York University School of Medicine
NYU Langone Medical Center
New York, New York
Peter S. Roland, MD
Professor and Chairman
Department of Otolaryngology-Head & Neck Surgery
Professor of Neurological Surgery
University of Texas Southwestern Medical Center
Dallas, Texas
Alexis Roy, MSc
Harvard Medical School
Boston, Massachusetts
jay T. Rubinstein, MD, PhD
Virginia Merrill Bloedel Professor and Director
Virginia Merrill Bloedel Hearing Research Center
Professor of Otolaryngology and Bioengineering
University of Washington
Seattle, Washington
David K. Ryugo, PhD
Curran Foundation Professor
Garvan Institute of Medical Research
Darlinghurst, New South Wales
and
Conjoint Professor
School of Medical Sciences
University of New South Wales
Kensington, New South Wales
Australia
William H. Shapiro, AuD, CCC-A
Clinical Associate Professor
Supervising Audiologist
NYU Cochlear Implant Center
New York University School of Medicine
New York, New York
Robert K. Shepherd, PhD
Bionics Institute
Melbourne, Australia
and
Department of Medical Bionics
University of Melbourne
Melbourne, Australia
RichardJ.H. Smith, MD
Sterba Hearing Research Professor
Director, Molecular Otolaryngology and Renal Research
Laboratories
Vice Chair, Department of Otolaryngology
Professor of Otolaryngology, Molecular Physiology & Bio
physics, Pediatrics and Internal Medicine (Division of
Nephrology)
University of Iowa Hospitals and Clinics
Iowa City, Iowa
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13. Mario A. Svirsky, PhD
Noel L. Cohen Professor of Hearing Science and Vice
Chairman of Research
Department of Otolaryngology-Head and Neck Surgery
New York University School of Medicine
NYU Langone Medical Center
New York, New York
Maja Svrakic, MD
Department of Otolaryngology-Head and Neck Surgery
New York University School of Medicine
NYU Langone Medical Center
New York, New York
Susan B. Waltzman, PhD
Marica F. Vilcek Professor of Otolaryngology
Department of Otolaryngology-Head and Neck Surgery
Co-Director, NYU Cochlear Implant Center
New York University School of Medicine
NYU Langone Medical Center
New York, New York
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14. xii
Acknowledgments
We thank all the contributors to this third edition. In
addition, we are indebted to J. Owen Zurhellen, Timothy
Hiscock, and Chris Malone at Thieme Publishers for their
commitment, guidance, and patience during the writing of
this book; we could not have done it without their profes
sionalism and support.
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15. 1 History of the Cochlear Implant
Marc D. Eisen
• Introduction
The cochlear implant has created a paradigm shift in the treat
ment of sensorineural hearing loss. The impact that the implant
has had is far greater than one would expect considering the
brief time over which its development occurred. In less than
four decades, the cochlear implant progressed from the first
attempts to elicit hearing via direct electrical stimulation of the
auditory nerve to a commercially available device that has
restoredvarying degrees of hearing to tens of thousands ofdeaf
patients. Several themes that can be discerned in the implant's
history are widely applicable to the development of other neu
ral prostheses. For one, the implant's development was truly an
interdisciplinary effort. Significant contributions came from
professionals in fields as diverse as engineering, otology, audiol
ogy, auditory neurophysiology, psychoacoustics, and industry.
The interaction among these players was not always harmoni
ous, but the strife yielded synthesis and progress.
Another theme is the courage of a few clinicians to risk their
reputations and eschew scientific dogma in the hope of helping
the patients that sought their care. A third theme is the willing
ness of patients to take substantial risks in serving as research
subjects, sometimes without any promise of individual gain.
This chapter cannot mention each and every contribution that
was made to the implant's early development, but rather cites
selected events and characters that, with the aid of the "retro
spectroscope," exemplify these themes and demonstrate the
progression of events leading toward a device that enables the
patient who has lost all hearing to regain the ability to converse
on the telephone and enables the deaf child to develop near
normal speech production and understanding.
The implant's development occurred in several phases. The
first phase of pioneering and experimentation began in 1957
and continued throughout the 1960s. The second phase, which
entailed feasibility studies, occurred in the 1970s. These studies
were conducted to determine whether the implant safely stim
ulated the auditory pathway and elicited useful hearing. A third
phase entailed the subsequent development of a commercially
viable multielectrode cochlear prosthesis.
• Precursors
Several discoveries made during the first half of the twentieth
century were not directly related to electrical stimulation of the
cochlear nerve, but were influential on the early development
of the cochlear implant and therefore warrant mention. These
include Homer Dudley's work on the synthesis of speech and
his "vocoder," Glenn Wever and his discovery of the cochlear
microphonic, and S.S. Stevens and coworkers' description of
electrophonic hearing.
The Vocoder
Homer Dudley was a researcher at the Bell Telephone Laborato
ries in New York. He described and demonstrated in 1939 a
real-time voice synthesizer that produced intelligible speech
using circuitry designed to extract the fundamental frequency
of speech, the intensity of its spectral components, and its over
all power. The spectral components were extracted with a
series of ten band-pass filters covering the frequency range of
speech.l He named the synthesizer the "vocoder," a compressed
version of "coding the voice." The operating principles of the
vocoder for condensing speech into its principal components
formed the basis of early speech processing schemes for multi
channel cochlear implants.
The Cochlear Microphonic
In 1930, Wever and Bray2 recorded and described the electrical
potentials in the cochlea that faithfully reproduced the sound
stimulus. This phenomenon became known as the "Wever-Bray
effect." The source of these measured potentials was initially
incorrectly assumed to represent auditory nerve discharges.
This theory ofthe origin ofthese potentials would be equivalent
to the "telephone" theory of hearing, referring to the analogue
representation of the voice carried along the "cable" of the
auditory nerve as it would along the wires of a telephone line.
In truth, what Wever and Bray were recording was not a
response of the cochlear nerve, but the cochlear microphonic
produced by the outer hair cells in the cochlea. Regardless of
the ultimate dismissal of the telephone theory of hearing, it
inspired several of the earliest pioneers of the cochlear implant.
Electrophonic Hearing
S.S. Stevens and his colleagues classically described in the 1930s
the mechanism by which the cochlear elements respond to elec
trical stimulation to produce hearing.3 This mechanism was
coined "electrophonic hearing." We now know that electrophonic
hearing results from the mechanical oscillation of the basilar
membrane in response to voltage changes. The primary tenet of
their description was the requirement that the cochlea be intact.
Prior to 1957, efforts to stimulate hearing electrically were per
formed on subjects with at least partially functioning cochleas.
These subjects' responses could be accounted for by electrophonic
hearing rather than by direct nerve stimulation. Furthermore, the
developers of the earliest cochlear implant efforts had the burden
of proving that the implants were directly stimulating the
cochlear nerve rather than eliciting electrophonic hearing.
• Pioneers: 1957-1973
Andre Djourno and Charles Eyries
Although numerous attempts to treat deafness with electricity
have been reported over the past several centuries,4 the first
reported direct stimulation of the cochlear nerve for the purpose
of generating hearing appeared as recently as 1957 with the
work of Andre Djourno and Charles Eyries. Despite the revolu
tionary impact that the cochlear implant has had on all auditory
disciplines, these beginnings in Paris received little attention.
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16. 2
. .
Andre Djourno (1904-1996) received degrees in both science
and medicine, yet he devoted his career to science. His early
endeavors were studying the electrophysiology of frog periph
eral nerve.5·6 He then ventured into more medical applications
of electricity. Several of Djourno's earlier innovations reflected
his inventiveness: a device to measure the pulse continuously,?
high-frequency electrical stimulation to remove metal frag
ments from bones,8 and the use of electroencephalography
(EEG) to study narcolepsy.9 Perhaps the most prescient devel
opment from this period was artificial respiration utilizing
direct phrenic nerve stimulation.10 Although this innovation
did not reach widespread clinical implementation, it demon
strated Djourno's interest in neural prostheses.
Djourno focused the next phase of his career on fabricating
and testing implantable induction coils to be used for "telesti
mulation," or stimulation through inductive coupling without
wires. Djourno assembled these induction coils himself and
called them "microbobinages," as the coils wound with wire
resembled small spools of thread (� Fig. 1.1).
Fig. 1 .1 Example of implantable induction coils ("microbobinages")
assembled by Djourno in his laboratory. Induction coils like the ones
shown here were used in various applications, including the stimulation
of the auditory pathway. The hand holding the coils provides perspective
on the implant's size. (Courtesy of the john Q. Adams Center.)
Both the active coil and the ground electrode were implanted
under the skin of an animal, and stimulation was trans
cutaneous (rather than percutaneous). The implantable coils
were first used to stimulate the sciatic nerve and thus trigger a
jump behavior in rabbits. Djourno studied numerous aspects of
telestimulation, including electrode biocompatibility (he
described using one of the first bioresistant resins, araldite, for
example, to coat the electrodes).11 He addressed the effect of
stimulus frequency on muscle contraction, and he found that
with higher frequency stimuli, muscles would not contract,
whereas with lower frequency stimuli muscle contraction was
painful. Djourno found the "right" stimulus frequency between
400 and 500 Hz. Since this frequency was within the speech
range, he began to use the analogue signal of his own voice as
the telestimulating stimulus.12 Triggering a nerve with his voice
may well have contributed to the idea of stimulating the
cochlear nerve to restore hearing.
Djourno also addressed the safety of repetitive stimulation
on tissue, demonstrating that the sciatic nerve from an
implanted rabbit, when examined histologically and grossly,
showed no changes after 2 years of repetitive stimulation.B
Throughout this time Djourno revealed little interest in hear
ing. He recognized, however, the potential of using the micro
bobinages to stimulate the auditory system, as he noted in a
1954 publication the possibility of "treating deafness" as a
potential application.12
Charles Eyries (1908-1996) completed his training in oto
laryngology in Paris in the early 1940s. Clinically, Eyries earned
early recognition for his description of a procedure to treat
ozena, or atrophic rhinitis, by placing implants underneath the
nasal mucosa to decrease the caliber of the nasal passages.14
This procedure became known in the French literature as the
"Eyries operation." Eyries was named chief of otorhinolaryngo
logy and head and neck surgery at I.:Institut Prophylactique in
1953, which has since been renamed I.:Institut Arthur Vernes.
Although primarily a clinician, he had research interests in
neuroanatomy and embryology of the facial nerve, and he
wrote about surgical facial nerve repairs.15 Eyries had shown
little interest in hearing at this point in his career and had never
worked with Djourno, although he knew of Djourno because
both he and Djourno had laboratories in the medical school
associated with the hospital.
As the local expert on facial nerve repairs, Eyries was
asked in February 1957 to provide a consultation for an
unfortunate patient, a 57-year-old man who suffered from
large bilateral cholesteatomas. A right-sided temporal bone
resection was performed 5 days prior to the consultation
and an extensive left temporal bone resection was per
formed several years earlier. Both procedures involved abla
tion of the labyrinth and facial nerve sectioning. As a result,
the patient was left with bilateral deafness and bilateral
facial nerve paralysis. Eyries was consulted to consider a
facial nerve graft for reanimation.16
On examination, Eyries found that the caliber of the
patient's remaining nerve was too small to support a local
nerve transfer. Eyries therefore embarked on a search for
appropriate graft material. He went to the medical school
seeking cadaverous material, where he met Djourno, who
offered to help and suggested stimulating hearing at the
same time. Although Eyries was primarily interested in
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17. his patient's facial reanimation, he agreed to implant
an electrode into the patient at the time of surgery.
Eyries's justification for agreeing to the implantation was
that the cavity was already exposed and the patient had
nothing to lose in having the extra procedure.16 From
Djourno's standpoint, the patient was deaf and begging
to escape from the silence that haunted him, and he was
fascinated by the opportunity to telestimulate the auditory
system.17
The procedure took place on February 25, 1 957. Eyries
performed the right-sided facial nerve graft using fetal sci
atic nerve as the graft material, which purportedly proved
to be successful. At the time of surgery, the proximal
cochlear nerve stump was found to be significantly shred
ded. Djourno and Eyries chose to seat the active electrode
into the remaining stump and place the induction coil into
the temporalis muscle. A postoperative lateral skull film con
firmed its placement (� Fig. 1 .2).
Some testing was done intraoperatively. The stimulus
waveforms included bursts of a 1 00-Hz impulse signal
administered 15 to 20 times per minute, low-frequency
alternating current, and the analogue signal of words
spoken into a microphone. The patient described detecting
auditory sensations. Several qualitative observations were
made: the patient's discrimination of intensity was good;
frequency discrimination was poor; no speech recognition
was evident. The patient underwent an extensive post
operative rehabilitation with the implant under the guid
ance of the speech therapist. Over the ensuing months more
complex stimuli were administered, and the patient was
able to differentiate between higher frequency (described as
"silk ripping") and lower frequency (described as "burlap
tearing") stimulation. He appreciated environmental noises
Fig. 1 .2 Lateral skull film of Djourno and Eyries's first implant following
surgery. The coil has been embedded in the temporalis muscle,
whereas the electrodes were placed near the remaining stump of the
cochlear nerve. (Courtesy of the john Q. Adams Center.)
and several words, but could not understand speech.
The publication that resulted from this work is the seminal
citation for direct cochlear nerve stimulation.18
Several months later, during testing, the electrode suddenly
ceased to function. Djourno and Eyries went to the operating
room to investigate. They found that a solder joint connecting
the wires to the ground electrode embedded into the tempora
lis muscle had broken, and the implant was replaced. The sec
ond implant, however, suffered the same fate. Eyries held
Djourno responsible for the broken electrodes and refused to
perform a third implantation.19 The falling out between the two
men over this problem was the end of Eyries's involvement in
the project. After this event, he and Djourno rarely conversed
for the rest of their lives.
This was not quite the end of the story for Djourno,
however. He went on to address several aspects of hearing
applicable to electrical stimulation. For one, he examined
the oscillographic representation of spoken words in an
effort to give deaf patients a visual representation of speech
that they could use for biofeedback when learning to
speak.2o After the first implant effort, a colleague
approached Djourno to enter into a business venture to
develop the implant. The colleague proposed that in
exchange for an exclusive arrangement on the project, he
would provide Djourno with the financial and engineering
support of industry_17 Djourno was always an academic ide
alist, and he did not believe in profiting from his discoveries.
Furthermore, he detested industry and would have no part
in granting exclusivity. As a matter of principle, Djourno
chose to do another implant with a different oto
laryngologist, Roger Maspetiol_l7 This second patient, deaf
ened from streptomycin ototoxicity, was implanted with an
electrode near the promontory, rather than within the tem
poral bone. The patient showed little enthusiasm for her
device, and she was lost to follow-up only a few months
after it was implanted. Djourno subsequently lost funding
for further implant work.21 This signaled the end of Djour
no's participation in developing an auditory prosthesis.
The legacy of the Djourno and Eyries's work was sustained
despite the abrupt departure of the two men. Claude-Henri
Chouard, who was a student in Eyries's laboratory working on
the facial nerve, resumed work on the cochlear implant several
years later. Chouard was instrumental in developing one of the
first functional multichannel implants, and he credits Charles
Eyries as his major source of inspiration.22
Although Djourno and Eyries's implantation on February
25, 1957 is typically credited as the first cochlear implant, a
closer evaluation of the patient's anatomy raises the ques
tion of whether the cochlear nerve or the auditory brain
stem were stimulated by the implanted electrodes, as
wallerian degeneration may have destroyed the cochlear
ganglion cells.23 Whether Djourno and Eyries stimulated the
cochlear nerve or the cochlear nucleus should not over
shadow the significance of their work. Electrical methods to
treat deafness had been described by numerous practition
ers for almost two centuries prior to 1 957, beginning with
the classic work of Alessandro Volta in the late 18th cen
tury.4 These previous efforts, however, either were aimed at
treating deafness with therapeutic electrical stimulation or
were examples of electrophonic hearing.
3
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• Early Developments in the
Western Hemisphere
Dissemination of the work of Djourno and Eyries was at first
slow in the Western Hemisphere. This is likely attributable
to the fact that their publication appeared only in the
French-language medical literature. Additionally, of the pair,
the more likely to present his work among clinicians was
Eyries, as he was an otolaryngologist. Eyries demonstrated
little enthusiasm for the project, however, and his interest
was short-lived. Djourno was a physiologist rather than a
clinician, making interaction between him and American
otolaryngologists less likely despite his continued interest.
Word of their work reached William F. House in California
serendipitously sometime around 1959, when a patient of
his handed him a summary in English of the Djourno and
Eyries work.24 The summary was optimistic regarding elec
trical stimulation to replace hearing, and House was
inspired.
los Angeles
William F. House was a dentist-turned-otologist who began
working with his brother Howard P. House at the Otologic
Medical Group in Los Angeles upon completion of his residency
in 1956. Early in his career he had already made significant con
tributions to otology and neurotology, including the facial
recess approach. He was working at the time on the middle
fossa approach to the internal auditory canal in collaboration
with john Doyle, a neurosurgeon who also practiced at St.
Vincent's Hospital in Los Angeles.2s House and Doyle first
sought to record the cochlear nerve response to sound when
the nerve was exposed during the middle fossa approach for
vestibular neurectomy as a treatment for Meniere's disease.
Specifically, they sought to record the nerve output associated
with tinnitus.26 They relied on Doyle's brother, james Doyle. an
electrical engineer, to address the technical challenge of record
ing such signals intraoperatively. The nerve output was
recorded, but no tinnitus was observed. Successful recordings
of sound-induced potentials from the cochlear nerve, however,
inspired stimulating the nerve with similar waveforms in order
to restore hearing.
House and Doyle first attempted electrical stimulation to
elicit hearing during stapes surgery by placing a needle elec
trode on the promontory or into the open oval window. An ear
speculum inserted into the external auditory canal served as a
ground lead. With square wave stimuli, patients reported hear
ing the stimulus without discomfort, dizziness. or facial nerve
stimulation. These responses were sufficient to encourage
House and Doyle to implant a patient with a hard-wire device.
The first willing subject was a 40-year-old man with severe oto
sclerosis and deafness. Promontory stimulation of the right ear
on january 5, 1961 revealed consistent responses. On january 9,
therefore. a gold-wire electrode was inserted under local anes
thesia through a postauricular approach into the round win
dow. The wire was brought out through the postauricular
skin.27 The patient reported hearing the electrical stimuli, but
he had poor loudness tolerance. Several weeks later the wire
was removed.
A second patient was also implanted in january 1961. The
woman had deafness, tinnitus, and vertigo associated with con
genital syphilis, and she was brought to the operating room for
a vestibular neurectomy through the middle fossa approach.
During the procedure, a single gold-wire electrode was placed
through the middle fossa approach into scala tympani at the
basal part of the cochlea. The wire was brought out through a
skin incision. The patient described hearing the square wave
stimulation upon waking from anesthesia. Over the ensuing
days, the current intensity required to elicit a response
increased. For fear of infection or edema, the wire was removed.
With the first patient's encouraging responses, and with the
hope of producing discrimination of higher frequencies, House
and Doyle decided to reimplant him with a five-wire electrode
array inserted through the mastoid facial recess and round win
dow. The electrode array was attached to a more permanent
electrode induction system seated in the skull. Over a several
week testing period, the patient's intensity requirement
increased and his postauricular skin began to swell. This device
was also removed for risk of infection. Worries of bio
compatibility of materials ensued.
The theoretical basis for the multiple-electrode design was
to spread high-frequency stimuli among spatially separated
electrodes. By stimulating different subpopulations of audi
tory nerve fibers at rates slower than their refractory period,
they thought, summation among the subpopulations would
purportedly yield an overall high-frequency response along
the whole nerve. This implant design and its theoretical
basis became the foundation for an early cochlear implant
patent application submitted by james Doyle and Earle Bal
lantyne in 1 961 . The patent was not granted until 1969.28
Despite being founded on what has since been shown to be
an erroneous theory of electrical stimulation, the patent was
ironically prescient in its statement that a 1 6-channel unit
would be necessary for implant patients to be able to con
verse on the telephone.
Word of the two implanted patients reached the lay press.
The brief articles were overly optimistic in their descriptions
of an "artificial ear," going so far as to announce that "surgical
implantation of a transistorized device designed to restore
hearing of deaf persons is scheduled within 30 days."29 These
reports prompted readers who were deaf to call House and
Doyle seeking a cure for their deafness, and aroused the interest
of investors seeking to cash in on emerging medical technology.
House recognized the danger in such publicity, and publicizing
the implant work became an issue of considerable conflict
between the Doyles and House. Disagreement over how
aggressive to proceed with the implant, given the initial bio
incompatibility problems, opened an irreparable rift between
House and the Doyles that brought an end to their collabora
tion. House had a very busy otologic practice, and implant
development took a low priority for several years to follow. The
Doyles, on the other hand, continued to experiment, implanting
numerous subjects. They collaborated with the Los Angeles
otolaryngologist Frederick Turnbull, whose office was used for
most of the testing. They reported their results in locaJ3° and
nationaJ31 forums, reporting optimistically that electrical stimu
lation could yield speech perception, but not offering system
atic testing or analysis. The Doyles ceased their investigations
in 1968 due to a lack of research funding.26
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19. Stanford University
F. Blair Simmons had worked as a research associate in the
laboratory of S.S. Stevens at Harvard as a medical student and
then with Robert Galambos at the Walter Reed Institute prior to
his residency in otolaryngology at Stanford University in
Stanford, California. Simmons was an assistant professor in
Stanford's Division of Otolaryngology in 1962 for less than a
month before he was presented with an unexpected opportu
nity to stimulate the cochlear nerve intraoperatively. The
patient was an 18-year-old man who had developed a recur
rence of a cerebellar ependymoma that manifested itself as mild
hearing loss. Exploratory craniotomy under local anesthesia
was planned, and the cochlear nerve would be exposed during
the procedure. Prior to surgery, Simmons discussed stimulating
the patient's cochlear nerve electrically. The patient agreed
to the intraoperative testing and to a preoperative auditory
training session. During the awake craniotomy, the patient
was asked to describe what he heard when a bipolar electrode
was used to stimulate the exposed cochlear nerve with 100-
microsecond square wave pulses. The patient described
auditory sensations and was able to discriminate stimulation
frequencies up to 1 kHz.32
Simmons's first implanted device was then placed 2 years
later, in 1964. This second subject was a 60-year-old man who
had been unilaterally deaf for several years, and whose better
hearing ear then became deaf. He also suffered from retinitis
pigmentosum and had associated severe sight disability.
Despite being made fully aware that implantation would likely
fail and very likely yield no useful hearing, the subject agreed
to undergo the implantation. Local anesthesia was used, and
the promontory exposed through a postauricular transmeatal
approach and elevation of a tympanomeatal flap. A 2-mm coch
leostomy and then subsequent 0.1 -mm drill hole into the
modiolus were performed. A partial mastoidectomy was also
performed and the middle ear entered anterior to the facial
nerve by removing the incus. A six-electrode array was placed
through the mastoid opening into the epitympanum and then
through both the cochleostomy and the modiolar opening to a
depth of 3 to 4 mm. The electrodes were attached to a plug that
was then secured to the mastoid cortex. Psychoacoustic testing
was carried out both at Stanford and at Bell Laboratories in New
jersey.33 Unfortunately, the subject's combination of disabilities
made psychophysical testing very challenging. Based on these
unfavorable experiences, Simmons became pessimistic about
the future of implantation. He estimated the likelihood that
electrical stimulation of the auditory nerve could ever provide
a clinically useful means of communication to be "considerably
less than 5%."34 Human implantation at Stanford was postponed
until further animal testing could prove its utility.
House Resumes His Work
With the advancements in pacemakers and ventriculoperito
neal shunts in the late 1960s, House's interest in cochlear
implantation was reawakened with more confidence in the
safety and efficacy of indwelling devices (.,. Fig. 1.3). House was
working with a talented engineer named jack Urban, a collabo
ration best known for several influential developments in neu
rotologic instruments. House and Urban aggressively pursued
History of the Cochlear Implant
Fig. 1 .3 William F. House (left) and Robin Michelson (right)
collaborating in the early 1 970s. (Courtesy of the john Q. Adams
Center.)
implanting their single-channel device in human patients. As
much as any other parameter, the durability and safety of
the device was on House's mind with this group of patients. Of
several patients implanted in 1969, one required having his
implant removed due to tissue rejection, and another was lost
to follow-up. However, a third patient, Charles Graser, became a
long-term experimental subject. In Graser, House found stimu
lation levels and results that remained stable over the course of
years. This gave credence to the safety of electrical stimulation.
Charles Graser was deaf for 10 years because of ototoxicity.
Postimplantation, he worked intensely as a research subject,
and continued to do so enthusiastically for many years.
Many of the observations and modifications that House and
Urban reported in the 1960s were based on the testing of only
subject-Graser. For instance, one of the surprising findings
from the work with Graser was that a 1 6,000-Hz carrier fre
quency signal helped him appreciate higher frequencies, and
amplitude-modulating the carrier with the acoustic signal
generally sounded the best. This signal processor strategy
became standard on the House/3M cochlear implant. Reporting
of these early results was primarily by testimonial experiences
of the individual subjects rather than systematic study. Another
important outcome of these early studies was abandoning the
multiple electrode systems for the single-wire electrode.Js
San Francisco
Robin Michelson (.,. Fig. 1 .3) was an otolaryngologist in private
practice in the 1960s in Redwood City, California. He was
the grandson of the Nobel Prize-winning physicist Albert
Michelson. Robin Michelson's inspiration for cochlear implanta
tion came from seeing a patient, T.l. Moseley, who had severe
tinnitus and otosclerosis. Michelson had sought to monitor
the cochlear microphonic during a stapedectomy as a means of
immediate feedback, since he performed the procedure under
local anesthesia. Moseley, an engineer, agreed to build him a
high-gain amplifier with an earpiece that Michelson could use
in the operating room. Michelson placed an electrode against
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20. 6
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the round window. Feedback from the amplifier elicited the
sensation of sound for the patient that Michelson was subse
quently able to pitch match.36
Michelson, like House, originally subscribed to the telephone
theory of hearing-that the cochlea presented the auditory
nerve with the analogue electrical signal of the auditory stimu
lus, and that all that was required to restore hearing was to
stimulate the auditory nerve with a similar signal. In an attempt
to demonstrate that electrical stimulation of the auditory nerve
elicited auditory responses, he implanted an electrode into
the cat cochlea and measured the cochlear microphonic in the
opposite ear. He found that electrical stimulation suppressed
the contralateral cochlear microphonic similarly to acoustic
stimuli. He concluded, therefore, that electrical stimulation was
carried along auditory pathways.37 Although Michelson was
likely demonstrating electrophonic hearing rather than direct
auditory nerve electrical stimulation, this result inspired him to
implant a human volunteer with hearing loss.
Michelson's first implant was a single-channel device
implanted into a congenitally deaf woman. Testing after
implantation revealed that she obtained auditory sensations
from stimulation, and that pitch perception was possible for
stimulus frequencies less than about 600 Hz. More interesting
to Michelson, however, was that the subject could differentiate
a square-wave stimulus from a sine-wave stimulus.36 Michelson
interpreted this to indicate that the fine structure of the
electrical stimulus could be conveyed along auditory pathways.
The gold-wire electrode hardened several days after the
operation, broke from the rest of the implant, and needed to be
removed. Several additional patients received fully implantable
single-channel devices, and this preliminary work was
presented to the American Academy of Ophthalmology and
Otolaryngology in October 1970; a follow-up study was pre
sented at the 1971 meeting of the American Otological Society.
The patients had pitch perception based on stimulus frequency
and could recognize speech stimuli but had no word under
standing. All implanted patients lost whatever residual hearing
they had prior to implantation.38
It was around this time that Francis Sooy visited Michelson in
Redwood City and saw his work in progress with implantation.
Sooy was the chairman of the nascent Department of Oto
laryngology at the University of California at San Francisco, and
this interaction with Michelson confirmed his belief in the
potential of cochlear implantation. He persuaded Michelson to
join the faculty at UCSF and bring his implant investigations
to the University. Sooy also believed that the successful devel
opment of the cochlear implant required a university-based
scientific foundation. After recruiting Michelson, Sooy then
recruited Michael Merzenich from the University of Wisconsin.
Merzenich was a young neurophysiologist whose interest was
mapping the inferior colliculus. He joined the UCSF faculty and
began working on recordings from the inferior colliculus for
several months before meeting with Michelson about the
cochlear implant. Merzenich was initially quite skeptical about
the merits of the implants and showed little interest in joining
the development effort. After seeing a few patients on a docu
mentary film created by the otolaryngology resident C. Robert
Pettit, however, Merzenich became convinced of its potentiaJ.39
The collaboration between Michelson, a clinical pioneer, and
Merzenich, a talented basic scientist with a solid foundation in
neurophysiology, was masterminded by Sooy and was an indis
pensable element in the development of the UCSF cochlear
implant program.
One of the first studies Merzenich performed was recording
the response properties of single units in the cat inferior colli
culus in response to both sound stimulation from one ear and
electrical stimulation from the other ear in implanted cats. He
showed that the inferior colliculus neurons responded similarly
to electrical and sound stimuli, but that the tuning curves for
electrical stimulation were very flat and showed little tuning.
Additionally, the responses from animals with ototoxin-induced
hair cell destruction showed the same responses to electrical
stimuli as untreated cochlea. This was the first definitive dem
onstration that auditory sensation with implants arose from
direct stimulation of the auditory nerve rather than electro
phonic effects. Responses in the cat were then compared to
psychoacoustic measures in the human implanted subjects
using the same electrical stimuli in both groups. The conclu
sions from this work were that with single-electrode devices,
periodicity pitch up to about 600 Hz is possible, but no place
coding of frequency is possible. Thus in order to convey com
plex sounds such as speech, multiple-electrode arrays would be
necessary.40 This work was presented to the American Otologi
cal Society at the 1973 annual meeting in St. Louis, and it
marked the beginning of the race toward the development of a
multichannel cochlear implant.
• Controversies and Doubts
The year 1973 represents a crossroads in the cochlear implant's
development. Until this time, cochlear implantation would have
been considered, at best, an idea with potential to help some
deaf people sometime in the future, and at worst as a danger
ous experimental procedure promising nothing better than
vibrotactile information. Simmons had downplayed the poten
tial of implants and abandoned human implantation. The only
clinicians performing human implants, House and Michelson,
were surgeons far from the mainstream and whose funding
was from private sources. In order for the implant development
to proceed, implants would need to be granted legitimacy as a
valid research pursuit with National Institutes of Health (NIH)
funding and demonstrate broad-based clinical application. This
section highlights events in the 1970s that accomplished both.
National Institutes of Health
The NIH itself was partly responsible for giving scientific legiti
macy to the cochlear implant. In 1970 the Neural Prosthesis
Program was established within the National Institute of Neu
rological Diseases aimed at promoting extramural research on
neural prostheses primarily by capitalizing on the contract
mechanism of the NIH.41 Initially the program did not focus on
an auditory prothesis, but rather on developing a visual pros
thesis for the blind, and the first contracts focused on this goal.
In addition to awarding contracts, the Neural Prosthesis Pro
gram under the guidance of F. Terry Hambrecht initiated and
maintained the annual Neural Prosthesis Workshop. The work
shop brought together a multidisciplinary group of contractors
and consultants to the NIH campus to discuss research findings,
delineate important problems, and develop strategies for the
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21. development of neural prostheses. At the third workshop in
january 1973, auditory prostheses first commanded a signifi
cant part of the agenda. Participants included Michelson,
Merzenich, and Simmons. Both Merzenich and Simmons also
obtained extramural NIH funding for their implant-related
research by this time.41
Early Cochlear Implant Meetings
Several meetings over the next several years pitted the implant
pioneers against the otology/hearing science establishment.
These symposia began to bring cochlear implantation into the
limelight, often resulting in considerable controversy. Between
1971 and 1973, significant work removed doubts that the audi
tory nerve could be stimulated directly with the implant. Con
cerns that the prominent oro-scientists expressed toward the
implant therefore shifted and coalesced during meetings in
1973 and 1974 of the Otological Society, the First International
Conference on Electrical Stimulation in San Francisco, and the
Third Workshop of the Neural Prosthesis Program. These con
cerns and their rationales are as follows:
• Concern: The remaining nerve fiber population in deafness is
not sufficient to support tonotopic stimulation ofthe nerve.
This was based on the finding of Hal Schuknecht and
coworkers that only a minority of temporal bones examined
demonstrated more than two thirds of the normal population
ofcochlear ganglion cells.42 Additionally, Nelson Y.S. Kiang, a
neurophysiologist at the Massachusetts Institute of
Technology who had defined how single auditory nerve units
respond to sound in cat, led a vehement opposition to human
cochlear implantation. His point ofview was that cochlear
implants with the current design could never produce speech
understanding or "useful hearing" because electrical stimuli
could not convey the complex auditory stimuli that the
cochlea provided.43 Implanting humans with devices that
offered little more than improved lip reading, he thought,
could not be considered prudent.
• Concern: Electrical stimulation could convey sounds out ofthe
speechfrequency range. Cochlear damage in deafness is
typically in its basal half, where high-frequency stimuli are
transduced. The electrodes described at the time extended
only into the proximal basal part of the cochlea. Therefore, if
the place principle were utilized, electrical stimulation would
yield only sound frequencies higher than the speech range.44
• Concern: The dynamic range of loudness with electrical
stimulation would be too narrow to convey useful sound
information. Although loudness grows with sound intensity
in the cochlea over a range of nearly 100 dB, the intensity
range with electrical stimulation is only about 6 dB, which
would severely limit loudness discrimination. The dynamic
range of the firing of cochlear nerve fibers of the cat in
response to both electrical and acoustic stimulation revealed
a similar finding-that the dynamic range in response to
sound is 20 to 40 dB, and to electrical stimuli 4 dB.43
• Concern: lntracochlear manipulation that would occur with
cochlear implantation would result in significant damage to the
cochlea; anything that disturbs scala media would cause
degeneration ofthe remaining sensoryfibers. This concern
arose from studies of Schuknecht showing that one aspect of
cochlear pathology was auditory nerve fiber degeneration.45
Why, then, perform an invasive procedure like the cochlear
implant when an externally worn device such as a
vibrotactile stimulator could be used to the same end?
The above concerns did not dissuade the core group of implant
developers from proceeding onward, yet a strong aura of doubt
surrounded the cochlear implant. At the forefront of cochlear
implant support, however, was Francis Sooy, who was responsi
ble for assembling the implant devotees in October 1974 with
the support of the NIH in order to evaluate the progress and
define the research goals for the implant, and to establish
guidelines for patient selection and implantation protocols. Two
important decisions were made at this meeting. First, criteria
for implantation were delimited: full informed consent that the
procedure is experimental; no useful hearing in either ear; only
those patients able and willing to participate in psychophysical
testing; otherwise healthy patients; and, finally, adults only.
Second, a consensus decision was made to stop implanting all
single-channel devices until an objective evaluation of the
patients already implanted could be performed.46 The NIH took
the lead in this objective evaluation with a call for applications
for a formal objective evaluation of the single-channel recipi
ents. The future of implant development rested on this objec
tive evaluation, as a finding that the implant had limited utility
may have curtailed allocation of further resources from
the Neural Prosthesis Program. The contract to perform the
objective assessment was awarded in june 1975 to a team at
the University of Pittsburgh led by Robert Bilger.
The Bilger Report
Thirteen adult single-channel implant subjects, 1 1 implanted
by House and two by Michelson, were flown to Pittsburgh for a
week-long testing session to take part in the study. The subjects
underwent extensive audiological, psychoacoustic, and vestibu
lar testing. Several of the results were not surprising: Subjects
could not understand speech with the implant alone, but the
implant helped the patients' lipreading scores. Also not surpris
ing was the finding that the subjects' quality of life was aided
by the implant. A surprising finding, however, was that the
subjects' speech production was significantly aided by their
implants. The investigators concluded from the study that
single-channel implants helped deaf patients. While this
conclusion may not seem profound, it was the first objective,
scientific assessment of implant performance, concluding that
the subjects received benefit from the implant with minimal
risk.47 From this, the cochlear prosthesis gained the legitimacy
needed to justify funded research efforts toward a multichannel
device. Furthermore, while the world waited for the multi
channel implant, the single-channel device was viable.
• Development of a
Multichannel Device
With the Bilger study confirming the utility of a single-channel
device, House moved forward with refinement of his implant.
He and jack Urban joined forces with the 3M Company. The
House/3M single channel device (.,.. Fig. 1 .4) was implanted into
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Fig. 1 .4 An early version of the House/3 M single-channel device.
Shown is the implanted receiver/stimulator and wire electrodes.
(Courtesy of the john Q. Adams Center.)
several thousand patients by the early 1980s, and in 1984 the
Food and Drug Administration (FDA) granted approval for the
device. Other centers, however, concentrated their efforts on
researching and developing a multichannel device. At the
forefront of this competition were Merzenich, Michelson,
Robert Schindler, and colleagues at UCSF (� Fig. 1.5), and
Graham Clark at the University of Melbourne in Australia.
Clark, a clinically trained otolaryngologist, began investigat
ing the cochlear implant as a graduate student in the 1960s.
Fig. 1 .5 Early eight-channel electrode and epoxy-coated receiver
designed by Robin Michelson and assembled by Mel Bartz. The
intracochlear portion of the electrode array was formed from Silastic to
fill scala tympani. (Courtesy of Stephen Rebscher, University of
California at San Francisco.)
He realized as early as his graduate thesis in 1969 that the
single-channel device had limited utility,48 and he sought to use
a systematic scientific approach to developing a multielectrode
device. The approach had several fronts: developing speech
processing strategies, optimizing the electrode array, and devel
oping a safe, reliable implantable receiver-stimulator. The
efforts toward what would become the Cochlear Corporation's
Nucleus multichannel implant was primarily an Australian ven
ture, as funding came from Australian national telethons and
government-associated engineering firms, and partly through
government grants.49 Clark and his colleagues reported several
important findings, two of which were that inserting the elec
trode array in an anterograde direction through a single cochle
ostomy at the round window niche into scala tympani was less
traumatic to the cochlear structures than either retrograde
insertion or multiple cochleostomies,so.sJ and dissolution
of platinum electrodes with biphasic pulsatile stimuli was
minimal, implying safe long-term stimulation.s2 Clark first
implanted a human subject in 1978, and by 1981 he showed
that subjects were able to understand some open-set speech
with their implants and without the aid of lipreading.s3 The
FDA approval for the Nucleus multichannel implant (Cochlear,
Melbourne, Australia) was granted for adult patients in 1985
and children as young as 2 years in 1990.
As several technical challenges were overcome in the 1980s,
multichannel cochlear implants became a safe option for pro
foundly deaf adults and children. Patients with the implant
were expected to have a quality-of-life improvement and some
open-set speech recognition. Another development was
required, however, to dramatically improve the speech
recognition provided by the implant, and this was the develop
ment of high-rate interleaved stimulation. Multiple electrode
stimulation relies on the place principle of coding auditory
stimuli along the cochlea. For separate electrodes to be effective
in eliciting different frequency responses, the spatial extent of
their stimuli must be different. Several studies in the late 1970s
and early 1980s demonstrated that significant interference
(known as "interaction") resulted from simultaneous stimula
tion of multiple electrodes.s4.ss It was found that electrode
interaction could be minimized by stimulating the electrodes in
a staggered, nonsimultaneous pattern.54 Another discovery was
that nonsimultaneous stimulation at pulse rates greater than
1 kHz was especially effective at improving an implant subject's
speech understanding. A collaboration between UCSF and the
Research Triangle Institute (Research Triangle, NC) resulted in
the implementation and testing of a speech processing scheme
that utilized this concept. The concept was patented and
became known as continuous interleaved sampling (CIS). The
implementation of CIS provided a tremendous improvement in
implant recipients' performance with speech recognition.56
Since that time there have been numerous noteworthy tech
nological developments in both device design and coding, and
the future promises even greater advances to further enhance
performance in the implanted hearing-impaired population.
• Conclusion
The development of the cochlear implant began in 1957 with
the first attempts to restore hearing with direct electrical
stimulation of the auditory nerve. In the years that followed,
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23. the primary proponents of implants were a few otologists try
ing to help their patients with single-channel devices, despite
considerable opposition from leaders in the field. If it were not
for these pioneers. cochlear implants may well have been
delayed by many years. Following the Bilger study, cochlear
implant research gained mainstream support, and efforts
toward a marketable multichannel device were underway.
Improvements are ongoing and offer a bright future to the hear
ing-impaired population.
• References
[ 1 ] Dudley H. Remaking speech. ] Acoust Soc Am 1939; 1 1 ; 169-177
(2] Wever EG, Bray CW. The nature of the acoustic response: the relation
between sound frequency of impulses in the auditory nerve. j Exp Psycho!
1 930; 13: 373-387
(3] Stevens SS. On hearing by electrical stimulation. j Acoust Soc Am 1937; 8:
191-195
(4] Shah SB, Chung JH, jackler RK. Lodestones, quackery, and science: electrical
stimulation ofthe earbefore cochlear implants. Amj Otol 1997; 18: 665-670
[5] Djourno A. Strohl A. Modifications du courant de peau de grenouille pendant
!'excitation electrique. CR Soc Bioi (Paris) 1 937; 125: 625
(6] Djourno A. Variation de l'excitabilite du sciatique de grenouille suivant l'ecart
des electrodes. CR Soc Bioi (Paris) 1946; 140: 1 83
(7] Djourno A. Sur Ia mesure instantanee de Ia frequence du pauls. Paris
Med (Paris) 1938; 37: 83
(8] Djourno A. Masmonteil, Roucayrol jC. Une application de Ia haute frequence
a !'extraction de protheses metalliques. Soc Electrother Radial. 1948; 29:
637-638
(9] Djoumo A, Delayj, Verdeaux G Un cas de narcolepsie avecetude eiectroence
phalographique. Congres d'Electro-encephalographie de Langue fran�aise,
Paris 1949
[10] Djourno A. La respiration eiectrophrenique. Presse Med 1952; 60: 1532-
1533
[ 1 1 ] Djourno A. Excitation eiectrique localisee a distance. C R Acad Sciences. 1953;
236: 2337-2338
(12] Djourno A. Kayser D. La methode des excitations induites a distance. ] Radial
1 954; 36: 1 1 7-118
(13] Djourno A, Kayser D, Guyon L Sur Ia tolerance par le nerf d'appareils eiectri
ques d'excitation indus a demeure. CR Soc Bioi (Paris) 1955; 149: 1 882-1883
[14] Eyries C. Traitement de l'ozene par un nouveau precede de prothese chirurgi
cale. Ann Otolaryng. 1946; 13: 581-586
[ 15] Olivier G. Eyries C. Reperes chirurgicaux et aspects du nerf facial extra
petreux. Med trap. 1953; 13: 720-723
(16] Eyries C. Experience personelle. Cahiers d'Oto-Rhino-Laryngologie. 1979; 14:
679-681
[ 17] Djourno A. Interview with Phillip Seitz. january 12. 1 994. john Q, Adams
Center Archives
[18] Djourno A, Eyries C, Vallancien B. De !'excitation eiectrique du nerf cochleaire
chez l'homme. par induction a distance, a !'aide d'un micro-bobinage indus
a demeure. CR Soc Bioi (Paris) 1957; 1 5 1 : 423-425
[19] Eyries C. Interview with Phillip Seitz, january 10, 1994. john Q, Adams Center
Archives
(20] Djourno A. Analyse oscillographique instantanee de Ia voix par!ee. CR Soc
Bioi (Paris) 1959; 153: 197-198
(21 ] Djourno A. A propos de prothese sensorielle totale. Bull Acad Nat! Med 1977;
161 : 282-283
[22] Chouard CH. Entendre sans Oreilles. Paris: Robert Laffont. 1973
(23] Eisen MD. Djourno, Eyries, and the first implanted electrical neural stimula
tor to restorehearing. Otol Neurotol 2003; 24: 500-506
[24] House WF A personal perspective on cochlear implants. In: Schindler RA,
Merzenich MM. eds. Cochlear Implants. New York: Raven Press 198513-
1 98516
(25] House WF. Cochlear Implants: My Perspective. Newport Beach, CA: AllHear,
1 995
(26] DoylejB. Interview with Philip Seitz, August 22, 1993. john Q, Adams Center
Archives
[27] House WF. Cochlear implants: beginnings (1957-1961 ). Ann Otol Rhinal Lar
yngol 1976; 85: 3-6
(28] Doyle JB, Ballantyne EW, inventors Artificial sense organ, U.S. Patent
3,449,768,june 17, 1969
[29] Anonymous . California electronics firm readies "artificial ear" implant. Space
Age News. 1961 ; 3: 1
(30] Doyle JB, Doyle JH, Turnbull FM, Abbey j, House L Electrical stimulation in
eighth nerve deafness. Bull Los Angel Neuro Soc 1963; 28: 148-150
(31 ] Doyle JH, Doyle JB, Turnbull FM. Electrical stimulation of the eighth cranial
nerve. Arch Otolaryngol 1 964; 80: 388-391
(32] Simmons FB. Mongeon Cj. Lewis WR. Huntington DA. Electrical stimulation
of acoustical nerve and inferior colliculus; results in man. Arch Otolaryngol
1 964; 79: 559-568
(33] Simmons FB, Epley jM, Lummis RC et al. Auditory nerve: electrical stimula
tion in man. Science 1965; 148: 104-106
(34] Simmons FB. Electrical stimulation of the auditory nerve in man. Arch Otolar
yngol 1966; 84: 2-54
(35] House WF, Urban j. Long term results of electrode implantation and elec
tronic stimulation of the cochlea in man. Ann Otol Rhinal Laryngol 1 973; 82:
504-51 7
(36] Michelson R P. Interview with Phillip Seitz, November 7 , 1995. john Q. Adams
CenterArchives
(37] Michelson RP. The crossed cochlea effect. Trans Am Acad Ophthal Otolaryngol
1 968
(38] Michelson RP. Electrical stimulation of the human cochlea. A preliminary
report. Arch Otolaryngol 1971 ; 93: 31 7-323
(39] Merzenich MM Interview with Marc Eisen, March 26. 2004
(40] Merzenich MM. Michelson RP, Pettit CR. Schindler RA, Reid M. Neural encod
ing of sound sensation evoked by electrical stimulation of the acoustic nerve.
Ann Otol Rhinal Laryngol 1973; 82: 486-503
[41 ] Hannaway C. Contributions of the National Institutes of Health to the Devel
opment of Cochlear Prostheses. Bethesda, MD: National Institutes of Health,
1 996
[42] Kerr A. Schuknecht HF. The spiral ganglion in profound deafness. Acta Otolar
yngol 1968; 65: 586-598
(43] Kiang NYS, Moxon EC. Physiological considerations in artificial stimulation of
the inner ear. Ann Otol Rhinal Laryngol 1 972; 8 1 : 714-730
(44] Lawrence M, johnsson L-G. The role of the organ of Corti in auditory nerve
stimulation. Ann Otol Rhinal Laryngol 1973; 82: 464-472
(45] Schuknecht HF. Lesions ofthe organ of Corti. Trans Am Acad Ophthalmol Oto
laryngol 1 953; 57: 366-383
(46] Merzenich MM. Sooy FAReport on a workshop on cochlear implants, Univer
sity ofCalifornia at San Francisco, October 23-25 1 974
(47] Bilger RC. Evaluation of subjects presently fitted with implanted auditory
prostheses. Ann Otol Rhinal Laryngol 1977; 86 Suppl 38: 1-176
(48] Clark G. Middle Ear and Neural Mechanisms in Hearing and in the Manage
ment of Deafness [Doctor of Philosophy Thesis]. Sydney: University ofSydney,
1 969
(49] Clark G. Sounds from Silence. Adelaide: Allen & Unwin, 2000
[50] Clark GM, Hallworth Rj. Zdanius K. A cochlear implant electrode. J Laryngol
Otol 1 975; 89: 787-792
(51 ] Clark GM. An evaluation of per-scalar cochlear electrode implantation tech
niques. An histopathological study in cats. j Laryngol Otol 1977; 91: 185-199
(52] Black FO. Wall C, O'LearyDP, Bilger RC. WolfRV. Galvanic disruption of vesti
bulospinal postural control by cochlear implant devices. ] Otolaryngol 1978;
7: 519-527
[53] Clark GM, Tong YC, Martin LF. A multiple-channel cochlear implant: an evalu
ation using open-set CID sentences. Laryngoscope 1981 ; 91 : 628-634
[54] Eddington OK, Dobelle WH, Brackmann DE, Mladejovsky MG. ParkinjL Audi
tory prostheses research with multiple channel intracochlear stimulation in
man. Ann Otol Rhinal Laryngol 1978; 87: 1-39
[55] White M. Design Considerations of a Prosthesis for the Profoundly Deaf.
Berkeley, CA: University of California. Berkeley, 1978
(56] Wilson BS, Finley CC, Lawson DT, Wolford RD. Eddington OK, Rabinowitz
WM. Better speech recognition with cochlear implants. Nature 1991; 352:
236-238
9
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24. 1 0
I I
2 Genetics of Hearing Loss and Predictors of Cochlear
Implant Outcome
Robert W. Eppsteiner, Richard K. Gurgel, and Richard}.H. Smith
• Introduction
Cochlear implantation is the standard treatment for hearing
restoration in patients with bilateral, profound sensorineural
hearing loss (SNHL). Although cochlear implant candidates all
share the diagnosis of SNHL, the divergent causes of hearing
loss create a heterogeneous patient population. This heteroge
neity in etiology likely contributes to the spectrum of cochlear
implant performance. If we better understood the causation
of SNHL in deaf patients, we would likely better predict their
hearing outcome after implantation.
Deafness results from the interplay of environmental and
genetic factors affecting the auditory pathway. With the
advent of new technologies for genomic enrichment and
high-throughput sequencing, the field of genetics has begun a
renaissance. Sequencing the entire human genome, which took
over a decade for the Human Genome Project, can now be done
in a matter ofdays. This new accessibility ofgenetic information
is revolutionizing both the molecular study of disease and its
management. Among the changes is a paradigm shift in the
evaluation of the deaf/hard-of-hearing person, especially if the
family history suggests that the hearing loss is inherited.
The cornerstone of the evaluation of hearing loss remains
the medical history and physical examination, comple
mented by a thorough audiological assessment, but the next
test that should be ordered is a comprehensive genetic
assessment. This algorithm underscores the importance of
a person's unique genetic traits in the medical decision
making process.1 This chapter reviews the genetic basis of
hearing loss, novel technologies used for comprehensive
genetic testing, and the impact of genetics on cochlear
implant (CI) performance.
• Genetic Basis of Hearing Loss
In developed nations, hearing loss is diagnosed in approxi
mately 1 of every 500 newborns, making it the most
common congenital sensory defect.2 It is three times more
prevalent than both Down syndrome and cystic fibrosis.3.4
The causes of congenital SNHL may be environmental (for
example, congenital cytomegalovirus and antibiotic-induced
ototoxicity) or genetic.3 In 70% of cases, hearing loss is
nonsyndromic (NSHL), implying that hearing loss is the only
recognized phenotypic abnormality. In the remaining 30% of
cases, however. other physical findings, such as heterochro
mia iridis or preauricular pits, co-segregate with the auditory
deficit. Collectively, these types of hearing loss are called
syndromic (SHL).
Most forms of SHL can be recognized from birth, but there
are two important exceptions, notable because they are both
recessive and relatively common. Usher syndrome, of which
there are three types, presents with congenital hearing loss
and later-onset retinitis pigmentosa, and Pendred syndrome,
which can present with congenital or postlingual hearing
loss and later-onset goiter, both appear as NSHL at birth,
and thus we refer to these types of SHL as the NSHL mimics.
Without genetic testing the NSHL mimics cannot be distin
guished from true NSHL. The scope of the challenge lies in
the fact that NSHL is extremely heterogeneous. Over 67
NSHL-causing genes have been identified; however, the total
number is likely double based on data assigning genomic
positions to 130 NSHL loci (a locus is a genomic position
that harbors a NSHL-causing gene).s
Most congenital NSHL (80%) is autosomal recessive
(ARNSHL), and, quite unexpectedly, mutations in one gene
account for 50% of congenital severe-to-profound ARNSHL in
many different world populations.3 G]B2, encodes a protein
called Connexin 26, which makes hexameric gap junctions
to link cells as a functional syncytium. The relative contribu
tions made by other genes to severe-to-profound ARNSHL,
and to other degrees of congenital hearing loss, have not
been determined primarily because until recently the exper
imental design was prohibitively complex, expensive, and
labor intensive.
Of the 67 genes implicated in NSHL, 38 cause ARNSHL and 25
cause autosomal dominant NSHL. There are two X-linked
causes of NSHL and, in addition, mitochondrial- and microRNA
associated NSHL occurs.6·7 These genes encode a wide variety of
proteins that are expressed in the cochlea and auditory neural
pathway and have a diverse spectrum of functions. Structural
proteins include actins (ACTG1 ), actin-associated proteins
(TRIOBP, RDX) and myosins (MY07A, MY01 5A, MY06, MY01A,
MYH9, MYH14); cellular junction/adhesion proteins include
otoancorin (OTOA), claudin-14 (CLDN14), and the gap junctions
(GJB2, GJB6); extracellular linkage molecules include cadherin
23 (CDH23) and protocadherin 15 (PCDH15); and transporters
and channels include pendrin (SLC26A4) and potassium
channels (KCNQ4) ("" Table 2.1 ).
• Advanced Sequencing
Technology for Genetic Testing
for Deafness
In 1977, Frederick Sanger, the only two-time Nobel laureate in
chemistry, developed Sanger sequencing, the gold standard for
genetic testing.8 Sanger sequencing utilizes chain-terminating
dideoxynucleotide inhibitors to determine nucleotide sequence,
and until recently was the only method used for full-gene
sequencing. Over the past few years, however, several advanced
genomic technologies that parallelize the sequencing process
(therefore they are often collectively called massively parallel
sequencing [MPS] technologies) have been developed. These
technologies produce millions of sequences at once that are bio
informatically aligned to the parent human genome and
queried for nucleotide differences. For an in-depth review of
these technologies as applied to hearing loss, the reader is
referred to Shearer et al.9
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25. . .
.
. .
Table 2.1 List ofGenes Included on the OtoSCOPE Platform with Corresponding Protein Name, Function, and Cochlear Implant Performance
Information'
Gene Protein Function Cl Perfonnance Reference
Membranous labY!ith Genes
CDH23 cadherin-related 23 structural (cell adhesion) + 1 8,1 9
CLDN14 Claudin 1 4 structural (tight junction) unknown
COLJ JA2 collagen, type XI, alpha 2 structural (extracellular matrix) unknown
ESPN espin structural (cytoskeleton of hair bundle) unknown
GJB2 gap junction protein, beta 2 ion homeostasis + 22,28-33
GJB6 gap junction protein, beta 6 ion homeostasis + 62
ILDR1 lg-like domain-containing receptor 1 unknown unknown
LOXHD1 lipoxygenase homology domain-containing 1 stereociliary protein +
MY03A myosin lilA motor protein (hair bundle) unknown
MY06 myosin VI motor protein (hair bundle) unknown
MY07A myosin VIlA motor protein (hair bundle) +
MYOJSA myosin XVA motor protein (hair bundle) unknown
OTOA otoancorin structural (extracellular matrix) unknown
OTOF otoferlin synaptic transmission (exocytosis at auditory +
ribbon synapse)
PTPRQ protein-tyrosine phosphatase receptor structural (hair cell shaft connectors) unknown
RDX radixin structural (cytoskeleton of hair bundle) unknown
SLC26A5 solute carrier family 26, member 5 motor protein (OHC} unknown
STRC stereocilin structural (extracellular matrix) unknown
TECTA tectorin alpha structural (extracellular matrix) unknown
TMC1 transmembrane channel-like 1 unknown + 63
TMIE transmembrane inner ear unknown unknown
TRIOBP TRIO and F-actin binding protein structural (cytoskeleton of hair bundle) unknown
USH1C Usher syndrome 1C homolog structural (scaffolding protein hair bundle) unknown
WHRN whirlin structural (scaffolding protein hair bundle) unknown
MYH14 myosin, heavy chain 1 4, nonmuscle unknown unknown
POU4F3 pou class 4 homeobox 3 transcription factor unknown
T}P2 tight junction protein 2 structural (tight junction) unknown
POU3F4 pou-domain class 3 transcription factor 4 transcription factor + 64,65,66
SLC26A4 solute carrier family 26, member 4 ion homeostasis + 36-40
AUGJ actin, gamma 1 structural (cytoskeleton of hair bundle) unknown
COCH coagulation factor C homologue, cochlin structural (extracellular matrix) +
CRYM crystallin, mu ion homeostasis unknown
DFNAS deafness, autosomal dominant 5 unknown unknown
SERPINB6 SERPINB6 protease inhibitor (hair cells) unknown
Spiral Ganglion Genes
ESRRB estrogen-related receptor beta transcription factor unknown
CCDCSO coiled-coil domain containing 50 structural (cytoskeleton of hair bundle) unknown
G/PC3 GAIP (-terminus interacting protein 3 proposed role in signal acquisition and unknown
propagation in cochlear hair cells
GJB3 gap junction protein, beta 3 ion homeostasis unknown
PCDH15 protocadherin-related 1 5 structural (cell adhesion i n hair bundle) unknown
PJVK pejvakin auditory pathway signaling (hair cell and unknown
neuronal)
TMPRSS3 transmembrane protease, serine 3 unknown variable
KCNQ4 potassium voltage-gated channel ion homeostasis unknown
MYH9 myosin, heavy chain 9, nonmuscle motor protein (hair cell) +
WFS1 Wolfram syndrome 1 (wolframin) ion homeostasis unknown
1 1
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26. 1 2
Table 2.1 continued
I Gene Protein Function Cl Perfonnance Reference
I Minimal Data Genes
GPSM2 g-protein signaling modulator 2 G-protein coupled receptor signaling pathway unknown -
GRXCR1 glutaredoxin cysteine-rich 1 unknown unknown -
HGF hepatocyte growth factor mitogen, motogen, and neurotrophic factor unknown -
LHFPLS lipoma HMGIC fusion partner-like 5 may function in hair bundle morphogenesis unknown -
LRTOMT leucine-rich transmembrane OMT auditory receptor cell development unknown -
MARVELD2 MARVEL domain containing 2 epithelial barrier formation unknown -
TPRN taperin unknown unknown -
PRPS1 phosphoribosylpyrophosphate synthetase 1 nervous system development and nucleotide unknown -
synthesis
GRHL2 grainyhead-like 2 transcription factor unknown -
MY01A myosin lA movement of organelles along actin unknown -
filaments
SLC1 7A3 solute carrier family 1 7. member 3 ionic and neurotransmitter transmembrane unknown -
transport
DIAPH1 diaphanous homologue 1 structural (cytoskeleton of hair bundle) unknown -
DSPP dentin sialophosphoprotein biomineral tissue development unknown -
EYA4 eyes absent homologue 4 transcription factor unknown -
CLRN1 clarin 1 may modulate neurotransmission at hair unknown -
cell-spiral ganglion cell synapse
GPR98 g-protein-coupled receptor 98 may have role in the development of the unknown -
central nervous system
USH1G SANS (aka Usher syndrome type-1 G protein) structural (hair cell bundles) unknown -
USH2A usherin 2A structural (cell adhesion) unknown -
MSRB3 methionine-R-sulfoxide reductase B3 protein repair unknown -
DIABLO diablo homologue, mitochondrial promotes apoptosis by activating unknown -
caspases
CEACAM16 carcinoembryonic antigen-related cell adhesion possible structural protein (between unknown -
molecule 1 6 tectorial membrane and stereocilia)
EYA 1 EVA1 protein unknown unknown II -
FOX/1 forkhead box protein 11 transcription factor unknown II -
KCNJ10 adenosine triphosphate (ATP)-sensitive inward ion homeostasis unknown
11- Irectifier potassium channel 1 0
Abbreviations: + represents good cochlear implant performance.
0Genes have been divided based on their location ofprimary expression. Genes listed as expressed in the spiral ganglion in certain cases may also be expressed in
the membranous labyrinth but are listed as spiral ganglion expressed genes.
Multigene Panels Using Microarrays
One of the first advanced genomic strategies applied to heredi
tary hearing loss was the single nucleotide extension microar
ray (HHL APEX).10 These mutation detection arrays incorporate
bound primers to which genomic DNA is hybridized. Fluores
cent nucleotides are added, and their binding to overhanging
primer bases is detected by imaging. HHL APEX does not inter
rogate entire genes but rather only 198 bases in eight genes
where pathogenic variants have been described.
Another microarray-based platform is OtoCHIP. It offers an
important advantage in that it uses resequencing microarrays
to screen specific genes for any nucleotide changes. Biotinylated
genomic DNA is hybridized to its complementary probe on the
array, which is imaged repeatedly to determine the nucleotide
at each genomic position. The current version of OtoCHIP inter
rogates 19 genes (70,000 bases).11
Multigene Panels Using Targeted
Genomic Enrichment
An alternative to array-based hybridization is solution-based
hybridization, one example of which is targeted genomic
enrichment (TGE). In TGE, sheared genomic DNA is hybrid
ized to biotin-tagged probes (also known as baits) that
are complementary to specific sequences of interest.
Hybridization occurs in solution (solid-phase hybridization
is also possible), and then the genomic DNA-bait complexes
are captured using streptavidin beads. Noncapture genomic
DNA is washed away, leaving a library enriched for a
specific region of interest. There are currently two
comprehensive panels for hearing loss that employ TGE:
OtoSCOPE and a panel designed by Otogenetics Corporation
(Atlanta, GA).12·13
http://medical.dentalebooks.com
27. Personalized Genomic Medicine
In addition to the targeted deafness panels described above, it is
possible to sequence a person's entire exome (coding genetic
sequence) or even a person's entire genome using next-genera
tion sequencing. It is no longer far-fetched to consider clinicians
having access to a patient's entire genomic sequence to aid in
disease diagnosis and treatment. For a variety of technical and
bioinformatic reasons, however, it is currently more efficient to
use multigene panels than more comprehensive alternatives.
• Role of Genetic Testing in
Patient Management
The role of genetic testing in the management of the deaf/
hard-of-hearing patient is rapidly evolving. With platforms
. . . . . ..
like OtoSCOPE, all known genetic causes of NSHL can be
screened simultaneously, moving the role for genetic testing
in patient management to the forefront.
Genetic Testing for Cochlear Implant
Candidates
Currently, when a child or adult with severe-to-profound
deafness presents for a CI evaluation, genetic testing is not
part of the standard evaluation. We propose an evaluation
paradigm in which genetic testing is part of the preoperative
evaluation for all CI candidates with suspected NSHL
(11> Fig. 2.1 ). Preoperative genetic testing can decrease the
number of screening tests ordered, change surgical manage
ment, and improve patient selection for implantation,
thereby decreasing healthcare costs.
-
Genetic Testing Paradigm for
Cochlear Implant Candidates
� �
..(
Apparent Genetic
Hearlng Loss
•
Medical History
Family History
Physical Exam
Audiogram, ABA, ASSR
t t
1.(
Apparent Non-Syndromlc
) II.( Syndromlc Hearing Loss
)Hearing Loss
• •
(Comprehensive Genetic Testing
with Multlgene Panel
( Phenotype-Based
Individual Gene Testing
J
• •
'
Genetic Counaellng
( Pathogenic Mutation In
J
No Pathogenic Mutation ln
0
J
Appropriate Testing:
Known Hearing Loss Gene Known Hearing Loss Gene Ophthalmology referral, EKG,
Temporal Bone Imaging, etc.
• •
t
( )..(
Non-Syndromlc
J
(Non-syndromlc Hearing
J
R-ch-Baeed Testing
Hearing Loss Loss Mimic
' '
(( Genetic CounHIIng
)) Genetic CounHIIng
Appropriate Testing:
Ophthalmology referral, EKG,
Temporal Bone Imaging, etc.
-
Fig. 2.1 Proposed genetic testing paradigm for Clcandidates. In cases where inherited deafness does not have syndromic features we recommend
comprehensive genetic testing. This will determine if individuals have true nonsyndromic hearing loss or hearing loss caused by a nonsyndromic
hearing loss mimic gene such as in Usher or Pendred syndrome. When a mutation in a nonsyndromic mimic gene is identified, referral for appropriate
further clinical evaluation should be pursued. Individuals for whom a genetic diagnosis is not reached are excellent candidates for research-based
testing and novel gene discovery. Abbreviations: ABR, auditory brainstem response; ASSR: auditory steady-state response; EKG, electrocardiogram.
1 3
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28. 1 4
I I
Genetic Screening in Cochlear
Implant Candidates with
Usher Syndrome
Usher syndrome, an autosomal recessive type of SNL that falls
under the rubric of NSHL mimics, is the leading genetic cause
of deafness and blindness and illustrates the utility of genetic
testing prior to cochlear implantation. Second to mutations in
G]B2, mutations in the Usher syndrome genes are the most com
mon cause of hearing loss in the congenitally deaf Cl population
(20% of cases).14 Because the deafness is congenital but the visual
impairment is delayed, without genetic testing it can be very
difficult to differentiate the Usher syndrome neonate from a neo
nate with another form of congenital severe-to-profound hearing
loss.1s But differentiation is important for many reasons. First,
when the diagnosis of Usher syndrome is made early, precau
tions such as wearing ultraviolet ray (UV)-canceling sunglasses
can be taken to delay the onset of vision loss. Second, in patients
with Usher syndrome, simultaneous bilateral implants are advo
cated, because sound localization is improved.16 Because patients
with USH1 eventually develop blindness, early bilateral cochlear
implantation ensures that hearing outcomes are optimized before
vision is lostP Third, preoperative genetic testing provides valu
able prognostic information, as Usher syndrome patients have
excellent hearing outcomes after cochlear implantation.18·19
Improved Patient Selection
for Cochlear Implantation with
Genetic Testing
It is estimated that 3 to 7% of CJ recipients do not benefit from
implantation; however, these patients cannot be identified
prior to implantation.20·21 Because most CJ recipients with
NSHL have very similar audioprofiles, audiological testing
cannot be used to prognosticate CI outcomes. It is possible,
however, that CI performance may be related to the genetic
cause of hearing loss. For example, studies of CJ performance
in persons with G]B2-related deafness have shown that
outcomes are typically excellent, whereas implantation in
persons with DDP1/TIMM8a-related deafness are not advisa
ble.22,23 The availability of multigene deafness panels like
OtoSCOPE make comprehensive studies of this relationship
possible. Preliminary data suggest that if the hearing loss is
secondary to a gene expressed in the membranous labyrinth
(G]B2, CDH23, MY07A), the CI outcome is likely to be a good; in
contrast, if the hearing loss is due to a gene expressed in the
spiral ganglion (DDP1/TIMM8a), CJ performance may be poor
(see below).
Decreased Need for Screening Tests
The evaluation of a deaf/hard-of-hearing patient with appar
ent NSHL is not standardized. After an audiogram, temporal
bone imaging is often reflexively ordered, often with one or
more screening tests including electrocardiogram, renal
ultrasound, urinalysis, and ophthalmological evaluation.24
Occasionally genetic testing, typically for G]B2 only, is consid
ered. This type of evaluation paradigm is not evidence-based
and neither is it logical or cost-effective. As an alternative,
we propose that after an audiogram, every patient with
suspected NSHL should have comprehensive genetic testing.
If a diagnosis is established, a large number of exploratory
screening tests can be avoided and a directed evaluation can
be completed. If SHL is suspected, appropriate screening tests
can be ordered as required (.,. Fig. 2.1 ).
• Impact of Genetic Mutation on
Cochlear Implant Performance
Despite more than 60 reports studying genetic mutation and CI
outcome, there are few firmly established genotype-phenotype
CI performance correlations (Table 2.1 ). Intuitively, the site
of pathology along the auditory pathway should be a useful
framework for predicting the impact of a genetic lesion on Cl
performance. For example, mutations in genes expressed in
the membranous labyrinth should portend a good CI outcome
because the implant would bypass the lesion and directly stim
ulate spiral ganglion neurons. In contrast, mutations in spiral
ganglion-expressed genes should portend poorer performance
because of dysfunction at the site of electrical stimulation.
Prior studies suggest that these suppositions are correct
(.,. Fig. 2.2).25,26
Membranous Labyrinth
Expressed Genes
The vast majority of established genotype-phenotype correla
tions have been published for genes that encode membranous
labyrinth proteins including G]B2, SLC26A4, OTOF, LOXHD1,
KCNQ1, MYH9, CDH23, MY07A, TMC1, COCH, POU3F4, and the
mitochondrial expressed genes. As a CJ bypasses the membra
nous labyrinth, persons with these genetic types of hearing loss
should be among the group of good CI performers, and indeed
this is almost always the case.
GJB2
G]B2 is the best studied hearing loss gene and has firmly estab
lished genotype-phenotype correlations. The encoded protein,
connexin 26, is expressed in the supporting cells, spiral limbus
and spiral ligament of the membranous labyrinth, and may be
important in K+ ion recycling in the supporting cells and stria
vascularis.27 There are over 25 reports (including over 420
individuals) of G]B2 genotype-phenotype CJ performance corre
lations, with the general consensus being that G]B2-related
deafness is associated with good performance. In fact, some
studies have found that patients with G]B2-related deafness
perform better than patients with other causes of deafness
when congenitally deaf Cl patients are divided into two groups
based on G]B2 status.22·2B-33 There is only one report ofa patient
with G]B2-related deafness performing poorly; however,
the implant was not performed until age 36.34 Consistent with
this poor outcome, prolonged profound deafness prior to
implantation is associated with higher rates of spiral ganglion
cell degeneration, which is an important determinant of CI
performance.25·26
http://medical.dentalebooks.com
29. . . . . . . .
Membranous Expressed Genes
GJB2, SLC26A4, OTOF, LOXHD I, KCNO I,
CDH23, MY07A, POU3F4, MYH9, TMCI,
COCH, Mitochondrial
Fig. 2.2 Genes with established genotype-phenotype correlations and their location of expression. (Adapted from the Hereditary Hearing Loss
Homepage (hereditaryhearingloss.org) with permission from G. Van Camp and R.J.H. Smith.)
SLC26A4
SLC26A4 encodes the protein pendrin, a sodium-independent
chloride/iodide symporter, and is implicated in Pendred
syndrome (SNHL, enlarged vestibular aqueduct, thyroid abnor
malities). There have been five reports of 49 patients with
SLC26A4-related hearing loss correlating Cl performance with
SLC26A4 mutations. The majority of these patients had both
SNHL and enlarged vestibular aqueduct. The pathophysiological
basis of SLC26A4 hearing loss appears to be secondary to mem
branous labyrinth dysfunction, and, as such, we would expect
these Cl recipients to perform well.35 All reports confirm that
this is indeed the case.36-4o
OTOF
There have been four reports (1 2 patients) of Cl performance
in patients with otoferlin (OTOF) mutations, all of whom
benefited from implantation.41-44 The encoded trans
membrane protein controls calcium binding and vesicle
release at the interface of the inner and outer hair cells and
the auditory nerve.45 Hence, otoferlin mutations cause a
unique phenotype, which mimics auditory neuropathy or
dyssynchrony. The hearing loss is congenital; however,
patients often pass newborn hearing screens based on otoa
coustic emission (OAE) testing but demonstrate profound
deafness on auditory brainstem response testing. These
results reflect the expression pattern of otoferlin in both
outer and inner hair cells. In the presence of OTOF mutations,
the inner hair cells are affected first (hence the poor ABR)
followed by progressive degeneration of the outer hair cells
(the OAEs are ultimately lost).46 Because Cis directly stimulate
the spiral ganglion neurons, the causative lesion is bypassed
in OTOF-related deafness.
Mitochondrial Deafness
There have been over 14 reports (23 cases) of Cl performance in
mitochondrial deafness. Mitochondrial deafness is usually postlin
gual, progressive, and in many cases, syndromic. Virtually all cells,
including those in the inner ear, depend on mitochondria for
adenosine triphosphate (ATP) production via oxidative phospho
rylation. Typically, when a phenotype manifests in mitochondrial
associated disease, it does so in cells with high energy require
ments. Because there are many such cells in many different organ
systems, the result is often a multisystem syndromic phenotype.
In the cochlea, the cells with the highest energy demands are hair
cells and intermediate cells in the stria vascularis. Consequently,
mitochondrial deafness results in damage to hair cells and the
stria vascularis, and, as would be expected, patients with mito
chondrial deafness are good Cl performers.47-49
Spiral Ganglion Expressed Genes
Cochlear implants stimulate spiral ganglion cells. Therefore, in
persons with extensive degeneration of these cells, Cl perform
ance will be poor. Although there are very few reports of geno
type-phenotype correlations in genes with robust expression in
the spiral ganglia, in the few cases that are available, it does
appear that Cl outcomes are more variable.
TMPRSS3
TMPRSS3 is robustly expressed in the spiral ganglion, stria
vascularis, and cochlear supporting cells and encodes a trans
membrane serine protease, which is critical to spiral ganglion
function.so Although the function of TMPRSS3 has not
been completely elucidated, it may be involved in cleavage of
neurotrophins in spiral ganglion cells, and, when defective,
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