EP1185331A4 - Systeme hybride implantable alliant une prothese auditive et un stimulateur cochleaire - Google Patents

Systeme hybride implantable alliant une prothese auditive et un stimulateur cochleaire

Info

Publication number
EP1185331A4
EP1185331A4 EP00928976A EP00928976A EP1185331A4 EP 1185331 A4 EP1185331 A4 EP 1185331A4 EP 00928976 A EP00928976 A EP 00928976A EP 00928976 A EP00928976 A EP 00928976A EP 1185331 A4 EP1185331 A4 EP 1185331A4
Authority
EP
European Patent Office
Prior art keywords
acoustic
hearing aid
basal
cochlea
hybrid
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
Application number
EP00928976A
Other languages
German (de)
English (en)
Other versions
EP1185331A1 (fr
Inventor
William Vanbrooks Harrison
Janusz A Kuzma
Alfred E Mann
Thomas J Balkany
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Boston Scientific Neuromodulation Corp
Original Assignee
Advanced Bionics Corp
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Advanced Bionics Corp filed Critical Advanced Bionics Corp
Publication of EP1185331A1 publication Critical patent/EP1185331A1/fr
Publication of EP1185331A4 publication Critical patent/EP1185331A4/fr
Withdrawn legal-status Critical Current

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/3605—Implantable neurostimulators for stimulating central or peripheral nerve system
    • A61N1/3606—Implantable neurostimulators for stimulating central or peripheral nerve system adapted for a particular treatment
    • A61N1/361—Phantom sensations, e.g. tinnitus
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/36036—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation of the outer, middle or inner ear
    • A61N1/36038—Cochlear stimulation
    • A61N1/36039—Cochlear stimulation fitting procedures
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/02—Details
    • A61N1/04—Electrodes
    • A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
    • A61N1/0526—Head electrodes
    • A61N1/0541—Cochlear electrodes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/36036—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation of the outer, middle or inner ear

Definitions

  • the present invention relates to hearing aid systems, and more particularly to a hybrid hearing aid system that combines a cochlear stimulator and a hearing aid to provide a hearing aid system that relies primarily on the cochlear stimulator portion of the system for being able to sense high frequency sounds, and that relies primarily on normal hearing processes, or a hearing aid, for being able to sense lower frequency sounds.
  • Such hybrid hearing aid system is best suited for use with a short cochlear electrode array of the type described in applicant's copending patent application, filed concurrently herewith, entitled “Electrode Array for Hybrid Cochlear Stimulator" (Attorney Docket Number AB-084-PC), which application is incorporated herein by reference.
  • a hybrid cochlear stimulation system provides electrical stimulation only to the basal end of the cochlea to stimulate ganglion cells responsible for sensing higher-frequency sounds, and relies on normal hearing (activation of hair cells through fluid motion within the cochlea), which may occur with or without the assistance of a conventional or a custom hearing aid, to sense middle-to-lower frequency sounds.
  • Hearing loss is generally of two types: conductive and sensorineural. Of these, conductive hearing loss occurs where the normal mechanical pathways for sound to reach the hair cells in the cochlea are impeded, for example, by damage to the ossicles. Conductive hearing loss may often be helped by use of conventional hearing aids, which amplify sound so that acoustic information does reach the cochlea and the hair cells. Some types of conductive hearing loss are also amenable to alleviation by surgical procedures.
  • Sensorineural hearing loss results due to the absence or the destruction of the hair cells in the cochlea which are needed to transduce acoustic signals into auditory nerve impulses.
  • Persons who suffer from sensorineural hearing loss are unable to derive any benefit from conventional hearing aid systems, no matter how loud the acoustic stimulus is made, because their mechanisms for transducing sound energy into auditory nerve impulses have been damaged.
  • auditory nerve impulses can be generated directly from sounds.
  • cochlear implant systems or cochlear prosthesis— which seek to bypass the hair cells in the cochlea by presenting electrical stimuli directly to the ganglia of the auditory nerve located adjacent the modiolar wall of the cochlea.
  • the ganglia also referred to as ganglion cells send nerve impulses to the brain via the auditory nerve, leading to the perception of sound in the brain, and an at least partial restoration of hearing function.
  • the common denominator in these cochlear prosthesis systems has been the implantation into the cochlea of electrodes which are responsive to a suitable external source of electrical stimuli and which are intended to transmit those stimuli to the ganglion cells, and thereby to the auditory nerve fibers. As people age, they frequently experience progressive hearing loss.
  • a cochlear prosthesis operates by direct electrical stimulation of the auditory nerve cells, bypassing the defective cochlear hair cells that normally transduce acoustic energy into electrical activity in such nerve cells.
  • a hybrid cochlear stimulation system thus requires an electrode array that can be inserted within the cochlea a sufficient depth to be near such cells, but which also does not block or significantly interfere with the normal functioning of the cochlea for hair cells located deeper within the cochlea.
  • an electrode array that may be used with a hybrid implantable cochlear stimulator hearing aid system.
  • the present invention addresses the above and other needs by providing a hybrid implantable cochlear stimulator and hearing aid system that relies primarily on the cochlear stimulator portion of the system for being able to sense high frequency sounds, and that relies primarily on normal hearing processes, or other acoustic boosting devices and systems, for being able to sense lower frequency sounds.
  • Such hybrid hearing aid system uses a relatively short and unobtrusive cochlear electrode array, e.g., of 6-8 mm in length, of the type described in applicant's copending patent application, previously referenced, entitled "Electrode Array for Hybrid Cochlear Stimulator" (Attorney Docket Number AB-084-PC), or something equivalent thereto.
  • a hybrid cochlear implant hearing aid system in accordance with the present invention provides low frequency acoustic energy boost, if needed, and high frequency direct neural stimulation.
  • the high frequency neurons are located at the basal end of the cochlea, providing easy access for the surgical placement of a short electrode that stimulates only the high frequencies.
  • the electrode array typically has from four to eight electrode contacts, e.g., 4 or 5 electrode contacts. The design of the electrode array allows the surgeon to place the array using minimally invasive surgical techniques and requires no cochleostomy.
  • the electrode array is thin, and can typically be inserted directly through the round window membrane to make contact with, or to be positioned in close proximity to, the modiolus wall in the basal region of the cochlea.
  • the front-end amplifier and processor and spectral decomposition filters used with the hybrid system of the present invention may be the same for both acoustic boost and neural stimulation applications.
  • the frequencies are separated and sent to circuits that either convert them into mechanical vibrations to boost low-to- middle frequency acoustic energy, or into high frequency energy that is further divided and converted to stimulation pulses that are applied directly to the neurons located in the basal region of the cochlea through the short electrode.
  • a smoothing circuit may be provided to allow a smooth, seamless transition from the acoustic enhancement provided for low-to-middle frequencies and the neural stimulation provided for the high frequencies.
  • tinnitus which is a buzzing, or ringing, sound in the ear
  • acoustic enhancement is provided in the low frequency range.
  • the hybrid system of the present invention may be used for several applications.
  • Such applications include, but are not limited to:
  • FIG. 1 is a functional schematic diagram of the ear, showing the manner in which an implantable cochlear stimulator and short cochlear electrode in the basal region of the cochlea may be used to practice the invention in accordance with one embodiment thereof;
  • FIG. 2 is a functional schematic diagram of the ear as in FIG. 1, and further shows the manner in which a conventional in-the-ear hearing aid may be used to supplement the practice of the invention
  • FIG. 3 is a functional schematic diagram of the ear as in FIGS. 1 and 2, and further shows how a middle-ear acoustic boosting system or hearing-aid device may be used as part of the hybrid system of the invention.
  • FIG. 4 is a block diagram of the signal processing portions of the invention.
  • Corresponding reference characters indicate corresponding components or elements throughout the several views of the drawings.
  • FIG. 1 one embodiment of the hybrid cochlear stimulation system of the present invention is shown.
  • Such embodiment relies upon an implantable cochlear stimulator (ICS) 50 to provide direct electrical stimulation of the ganglion cells located at the basal end of the cochlea, to thereby enhance the hearing of high frequency sounds; and relies upon the patient's normal hearing processes, e.g., the patient's residual low and mid frequency hearing, to sense low-to- mid frequency sounds.
  • ICS implantable cochlear stimulator
  • the outer ear includes the auricle 14 and the ear canal 16.
  • the "ear drum" 18 At the end of the ear cannel 16 is the "ear drum" 18, or in medical terms, the tympanic membrane 18.
  • the received acoustic wave 12 causes the tympanic membrane 18 to vibrate, which vibration is coupled through three tiny bones, the malleus (“hammer”) 20, the incus (“anvil”) 22 and the stapes ("stirrup") 24, to the fenestra 30.
  • the fenestra comprises an opening resembling a window.
  • the fenestra ovalis, or oval window is the opening between the middle ear and the vestibule of the inner ear. It is closed by a membrane to which the stapes is attached.
  • the fenestra rotunda, or round window is the opening between the scala tympani of the cochlea and the middle ear.
  • the round window is also closed by a membrane, which for purposes of the present application, may be referred to as the round window membrane.
  • the function of both the oval window and round window is represented by the single membrane 30.
  • the bones of the middle ear serve to filter and amplify the perceived acoustic wave 12, causing the fenestra membrane 30 to articulate, or vibrate, in response to the acoustic wave 12.
  • Vibration of the membrane 30 sets up waves of fluid motion within the fluid contained within the snail-shaped cochlea 36.
  • Such fluid motion in turn, activates tiny hair cells (not shown in FIG. 1) that line the inside of the cochlea 36.
  • Activation of the hair cells causes appropriate nerve impulses to be transferred through the spiral ganglion 40 to the brain, where they are perceived as sound.
  • an implantable cochlear stimulator (ICS) 50 may be implanted near the ear, and a short cochlear electrode array 52, having a plurality of spaced apart electrodes 54 thereon, is inserted into the cochlea 36 through the membrane 30.
  • Such ICS 50 is coupled to a microphone, e.g., an external microphone 40 (although an internal, i.e., implanted, microphone could also be used) that senses sounds.
  • the microphone signals are amplified and processed by a suitable speech processor (S.P.) 42, which S.P. may also be external or implanted.
  • S.P. speech processor
  • the speech processor generates appropriate control signals that are coupled to the ICS 50.
  • Such coupling may occur through various means, but is usually achieved through an inductive coupling link, represented by the arrow 44, with an external head piece, connected to the speech processor 42.
  • Such link also provides a way for power to be coupled into the implanted ICS 50.
  • the processor and power source to be implanted, either as an integral part of the ICS 50 or in a separate housing coupled to the ICS. (See, e.g., International
  • the speech processor 42 functions as a signal processing means for processing the electrical signals received from the microphone and for generating high-frequency control signals therefrom representative of the higher frequency content of the sensed acoustic sounds. These control signals are then coupled to the ICS 50 through the link 44.
  • the ICS 50 has means responsive to the high-frequency control signals for selectively generating electrical stimuli and applying the electrical stimuli to the electrode (52). In this manner, the basal region of the scala tympani duct is stimulated with electrical stimuli representative of the higher-frequency content of the sensed acoustic sounds.
  • the sounds sensed by the microphone 40 are processed and filtered to separate out the high frequency sounds.
  • These high frequency sounds are then converted to appropriate electrical stimuli that are selectively applied to the electrode contacts 54 of the electrode array 52 positioned in the basal region of the cochlea.
  • Such electrical stimuli bypass the defective hair cells in the basal region of the cochlea and directly activate the nerves within the of the spiral ganglion, causing nerve impulses to be transferred to the brain, where they may be perceived as high frequency sounds.
  • the other hair cells in the cochlea i.e., those in the apical and mid regions of the scala tympani duct, retain their functionality. That is, these hair cells are able to sense the fluid waves set up by vibrations of the membrane 30 corresponding to low-to-mid frequency sounds.
  • the patient or user of the hybrid system shown in FIG. 1 is able to sense high frequency sounds through the ICS portion of the system, and is able to sense lower frequency sounds through the normal hearing processes of the ear.
  • FIG. 2 another embodiment of the invention is depicted.
  • the embodiment shown in FIG. 2 is the same as the embodiment shown in FIG. 1 except for the addition of an in-the-canal hearing aid 15.
  • the in-the-canal hearing aid 15 which may be of conventional design, receives the acoustic waves 12 and amplifies them, thereby presenting amplified acoustic waves 13 to the tympanic membrane 18.
  • the amplified acoustic waves 13 are thereby able to increase the magnitude of the vibrations that pass through the middle ear and articulate the membrane 30, thereby increasing the magnitude of the fluid waves within the cochlea, which higher- magnitude fluid waves may be more effective at activating the hair cells throughout the cochlea.
  • the cochlear stimulator portion (ICS 50 and electrode array 52) of the hybrid system must still be used if high frequency sounds are to be perceived.
  • FIG. 3 yet another embodiment of the invention is shown, comprising a middle ear hearing aid system 60 which is inserted into the middle ear.
  • system 60 includes an implanted acoustic microphone 62 attached to the malleus 20 and an implanted acoustic amplifier and driver 64 coupled to the stapes 24.
  • acoustic signals vibrate the tympanic membrane
  • an electrical or other signal e.g., optical or magnetic
  • This signal is then applied to the acoustic amplifier and driver device 64, where they are transduced back to mechanical vibrations that drive the stapes 24, and hence vibrate the membrane 30 with an amplified or increased intensity.
  • the vibration of the membrane 30 with an increased intensity or magnitude increases the intensity of the fluid waves that are set up within the scala tympanic duct of the cochlea, thereby more effectively activating the non-defective hair cells throughout the cochlea.
  • middle ear hearing aid system 60 thus provides an increased ability to sense lower frequency acoustic signals.
  • a stimulator circuit 50' coupled to the basal electrode array 52, senses the high frequency sounds and converts them to appropriate electrical stimuli for application to the respective electrode contacts 54 on the electrode array 52.
  • FIG. 4 a block diagram of the signal processing circuits used by the hybrid system of FIG. 3 is depicted.
  • a front- end amplifier and processor 70 including an analog-to-digital converter (ADC), senses acoustic signals.
  • the processor further uses appropriate spectral decomposition filters to separate the high frequency signal components from the low and middle frequency components.
  • the high frequency signal components are then sent to a cochlear signal processor 72, and the low and middle frequency signal components are sent to an acoustic signal processor 74.
  • Each of these processors 72 and 74 applies appropriate signal processing strategies to the signals and then applies them to a signal phase compensation and balance processor 76.
  • This phase compensator and balance processor performs, ter alia, a smoothing function that allows a smooth, seamless transition from the acoustic enhancement provided for low- to-middle frequencies and the neural stimulation provided for the higher frequencies.
  • the acoustic signals are sent to the output-to-acoustic amplifier and driver circuit 64 and the cochlear stimulator signals are sent to the stimulator circuits 50'.
  • the signals are converted into mechanical vibrations to boost low-to-middle frequency acoustic energy.
  • the signals are converted into high frequency energy that is further divided and converted into stimulation pulses that are applied directly to the neurons located in the basal region of the cochlea through the short basal electrode 52.
  • Tinnitus suppression is carried out by generating appropriate pulse sequences in the stimulator 50 or 50' and then delivering these pulse sequences to selected electrodes 54 on the electrode array 52. Such suppression may occur at the same time that acoustic enhancement takes place for the lower frequencies.
  • the various components of the invention i.e., high frequency neural stimulation, residual lower frequency hearing, high frequency neural stimulation with signal enhancement, lower frequency acoustic signal enhancement, and tinnitus suppression, may advantageously be combined in various ways to address several different applications.
  • the invention may be used for any or all of the following applications:
  • the present invention provides a versatile hybrid cochlear stimulation and hearing aid system that may restore hearing function over a wide frequency band, e.g., from low frequencies to high frequencies.
  • the invention provides such a hybrid system wherein minimally invasive surgical techniques need be employed.
  • the invention provides a versatile hybrid system that can be used for a wide variety of applications, ranging from higher frequency neural stimulation, with or without signal enhancement (balancing, smoothing and phase compensation); tinnitus suppression; residual lower frequency hearing, or lower frequency acoustic signal enhancement.

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  • Health & Medical Sciences (AREA)
  • Otolaryngology (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Neurology (AREA)
  • Neurosurgery (AREA)
  • Prostheses (AREA)

Abstract

L'invention concerne un système hybride implantable alliant une prothèse auditive et un stimulateur cochléaire (10) assurant une amplification de l'énergie acoustique basse fréquence, si nécessaire, et une stimulation neuronale directe haute fréquence. La suppression d'acouphène peut aussi faire l'objet de cette invention. Les neurones responsables de la détection des sons haute fréquence se trouvent à l'extrémité basale de la cochlée. Une électrode basale courte (52) s'étendant dans la cochlée uniquement au niveau de la région basale assure une stimulation directe des neurones grâce à un stimulateur cochléaire (5) correctement commandé. Le réseau d'électrodes comprend normalement entre 4 et 8 contacts (54) d'électrode. La conception du réseau d'électrodes permet au chirurgien de placer le réseau en faisant appel à des techniques de chirurgie non invasive et sans cochléostomie. Le réseau d'électrodes est fin et peut être inséré directement à travers la membrane de fenêtre ronde pour entrer en contact ou être placé à proximité de la paroi de la columelle dans la région basale de la cochlée. Le système hybride implantable alliant une prothèse auditive et un stimulateur cochléaire permet de détecter des sons haute fréquence grâce au stimulateur et de détecter des sons de fréquence plus basse grâce à des processus d'écoute normale ou à d'autres dispositifs et systèmes d'amplification acoustique.
EP00928976A 1999-05-14 2000-05-12 Systeme hybride implantable alliant une prothese auditive et un stimulateur cochleaire Withdrawn EP1185331A4 (fr)

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
US13428999P 1999-05-14 1999-05-14
US134289P 1999-05-14
PCT/US2000/013122 WO2000069512A1 (fr) 1999-05-14 2000-05-12 Systeme hybride implantable alliant une prothese auditive et un stimulateur cochleaire

Publications (2)

Publication Number Publication Date
EP1185331A1 EP1185331A1 (fr) 2002-03-13
EP1185331A4 true EP1185331A4 (fr) 2008-12-24

Family

ID=22462679

Family Applications (1)

Application Number Title Priority Date Filing Date
EP00928976A Withdrawn EP1185331A4 (fr) 1999-05-14 2000-05-12 Systeme hybride implantable alliant une prothese auditive et un stimulateur cochleaire

Country Status (4)

Country Link
EP (1) EP1185331A4 (fr)
AU (1) AU4712900A (fr)
CA (1) CA2370860A1 (fr)
WO (1) WO2000069512A1 (fr)

Families Citing this family (16)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6628991B2 (en) 2000-04-28 2003-09-30 Advanced Bionics Corporation Minimally-invasive access into the cochlea for electrode insertion and fluid delivery
US6549814B1 (en) 2000-06-09 2003-04-15 Juergen Strutz Blade electrode array for insertion under soft tissue of lateral wall of cochlea
US7962226B2 (en) 2001-04-06 2011-06-14 Cochlear Limited Cochlear endosteal electrode carrier member
WO2002080817A1 (fr) 2001-04-06 2002-10-17 Cochlear Limited Electrode endo-osseuse
AT503452B1 (de) * 2002-03-01 2007-10-15 Helms Jan Dr Hörvorrichtung
AUPS322702A0 (en) * 2002-06-28 2002-07-18 Cochlear Limited Cochlear implant electrode array
WO2004024212A2 (fr) 2002-09-10 2004-03-25 Vibrant Med-El Hearing Technology Gmbh Dispositifs medicaux implantables a plusieurs transducteurs
US7529587B2 (en) 2003-10-13 2009-05-05 Cochlear Limited External speech processor unit for an auditory prosthesis
WO2005097255A1 (fr) 2004-04-02 2005-10-20 Advanced Bionics Corporation Procedes et systemes de reglage d'une stimulation acoustique et electrique
US7937154B2 (en) 2005-12-08 2011-05-03 Cochlear Limited Promoting curvature and maintaining orientation of an electrode carrier member of a stimulating medical device
MY150957A (en) * 2007-01-10 2014-03-31 Winkler Peter Anthony Tinnitus treatment
US8526641B2 (en) * 2008-03-31 2013-09-03 Cochlear Limited Customizable mass arrangements for bone conduction devices
US20110190568A1 (en) * 2008-06-25 2011-08-04 Van Den Heuvel Koen Enhanced performance implantable microphone system
AU2009222439B2 (en) 2009-09-28 2011-07-21 Cochlear Limited Method and circuitry for measurement and control of stimulation current
WO2021216071A1 (fr) * 2020-04-23 2021-10-28 Advanced Bionics Ag Traitement des acouphènes avec un système d'implant cochléaire
EP4157433A1 (fr) * 2020-05-28 2023-04-05 Advanced Bionics AG Systèmes et méthodes de traitement d'acouphène fondés sur capteurs

Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5271397A (en) * 1989-09-08 1993-12-21 Cochlear Pty. Ltd. Multi-peak speech processor

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Publication number Priority date Publication date Assignee Title
US3764748A (en) * 1972-05-19 1973-10-09 J Branch Implanted hearing aids
US5776179A (en) * 1995-10-06 1998-07-07 The University Of Michigan Method for evaluating inner ear hearing loss
EP0999874B1 (fr) 1997-08-01 2004-09-29 Alfred E. Mann Foundation For Scientific Research Dispositif implantable a configuration amelioree d'alimentation et de recharge de batterie

Patent Citations (1)

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Publication number Priority date Publication date Assignee Title
US5271397A (en) * 1989-09-08 1993-12-21 Cochlear Pty. Ltd. Multi-peak speech processor

Non-Patent Citations (1)

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Title
See also references of WO0069512A1 *

Also Published As

Publication number Publication date
CA2370860A1 (fr) 2000-11-23
AU4712900A (en) 2000-12-05
EP1185331A1 (fr) 2002-03-13
WO2000069512A1 (fr) 2000-11-23

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