US3752939A - Prosthetic device for the deaf - Google Patents

Prosthetic device for the deaf Download PDF

Info

Publication number
US3752939A
US3752939A US00223415A US3752939DA US3752939A US 3752939 A US3752939 A US 3752939A US 00223415 A US00223415 A US 00223415A US 3752939D A US3752939D A US 3752939DA US 3752939 A US3752939 A US 3752939A
Authority
US
United States
Prior art keywords
means
conductors
electrode
base member
cochlea
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.)
Expired - Lifetime
Application number
US00223415A
Inventor
M Bartz
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.)
University of California
Boston Scientific Neuromodulation Corp
Original Assignee
Beckman Coulter Inc
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 Beckman Coulter Inc filed Critical Beckman Coulter Inc
Priority to US22341572A priority Critical
Application granted granted Critical
Publication of US3752939A publication Critical patent/US3752939A/en
Assigned to UNIVERSITY OF CALIFORNIA A NONPROFIT EDUCATIONAL INSTITUTION OF HIGHER LEARNING reassignment UNIVERSITY OF CALIFORNIA A NONPROFIT EDUCATIONAL INSTITUTION OF HIGHER LEARNING ASSIGNMENT OF ASSIGNORS INTEREST. Assignors: BECKMAN INSTRUMENTS, INC.
Anticipated expiration legal-status Critical
Assigned to BOSTON SCIENTIFIC NEUROMODULATION CORPORATION reassignment BOSTON SCIENTIFIC NEUROMODULATION CORPORATION CHANGE OF NAME (SEE DOCUMENT FOR DETAILS). Assignors: ADVANCED BIONICS CORPORATION
Assigned to BOSTON SCIENTIFIC NEUROMODULATION CORPORATION reassignment BOSTON SCIENTIFIC NEUROMODULATION CORPORATION CHANGE OF NAME (SEE DOCUMENT FOR DETAILS). Assignors: ADVANCED BIONICS CORPORATION
Application status is Expired - Lifetime legal-status Critical

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00Electrotherapy; Circuits therefor
    • A61N1/02Details
    • A61N1/04Electrodes
    • A61N1/05Electrodes for implantation or insertion into the body, e.g. heart electrode
    • A61N1/0526Head electrodes
    • A61N1/0541Cochlear electrodes
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F11/00Methods or devices for treatment of the ears, e.g. surgical; Protective devices for the ears, carried on the body or in the hand; Non-electric hearing aids
    • A61F11/004Ear surgery
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00Electrotherapy; Circuits therefor
    • A61N1/18Applying electric currents by contact electrodes
    • A61N1/32Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/36036Applying electric currents by contact electrodes alternating or intermittent currents for stimulation of the outer, middle or inner ear

Abstract

There is disclosed a method and apparatus for inducing the sensation of intelligible hearing by direct electrical excitation of the auditory nerve endings distributed along the basilar membrane within the cochlea. An electrode is positioned within the lower scala of the cochlea by insertion through the round window. The electrode consists of a resilient base member shaped to conform to the inner surface of the lower scala, such base member extending along the basilar membrane. The base member retains a pair of conductors which extend parallel to the length of the basilar membrane. Means are also provided for transmitting an excitation signal to a receiver implanted with and connected to the conductors. Several configurations for the electrode are disclosed as well as several techniques for the excitation thereof.

Description

United States Patent 1191 14 1 Aug. 14, 1973 Bartz PROSTHETIC DEVICE FOR THE DEAF [75] Inventor: Melvin C. Bartz, Newport Beach,

[21] Appl. No.: 223,415

Related US. Application Data [63] Continuation-impart of Ser. No. 075,142, Sept. 24,

1970, abandoned.

OTHER PUBLICATIONS The Crossed Cochlea Effect by Michelson, Actions of American Laryngological, Rhinological and Othological Society Inc. Presented 1/3/68, Received in Library of Medicine 1/8/69 Primary Examiner-Kathleen H. Claffy Assistant Examiner-Thomas D'Amico Attorney-R. J. Steinmeyer and James M. Thomson 7] ABSTRACT There is disclosed a method and apparatus for inducing the sensation of intelligible hearing by direct electrical [52] US. Cl. 179/107 R, 128/1 R, 3/1, excitation of the auditory nerve endings distributed 181/23 along the basilar membrane within the cochlea. An [51 Int. Cl. H041] 25/00 electrode is positioned within the lower scala of the [58] Field Of Search 179/107 R, 107 BC, chlea by insertion through the round window The elec [79/107 E; R; 3/1 trode consists of a resilient base membershaped to conform to the inner surface of the lower scala, such [56] References cued base member extending along the basilar membrane. UNITED STATES ATE TS The base member retains a pair of conductors which 3,449,768 6/1969 Doyle 128/1 R x nd pa alle t the length of the asilar membrane. 3,209,081 9/1965 Ducote 12811 R Means are also provided for transmitting an excitation 3.170.993 2/1965 Puharich... 128/1 R signal to a receiver implanted with and connected to $995,533 8/ Puhafichm- 179/107 BC the conductors. Several configurations for the elecg f s g trode are disclosed as well as several techniques for the u arrc 2,164,121 6/1939 Pescador 179/107 BC exctamm there 3,493,695 2/1970 Stork 179/107 R 24 Claims, l5 Drawing Figures 7'0! (an r 902 max/M wfiwaqk MO0UL 470R 77 g as cm 4470/? QEMOQVZJTUR 5565/1457? 1 rfifllvsM/rrfifi 79- WTQA- COCHZEAR PROSTHETIC DEVICE FOR THE DEAF CROSS REFERENCE TO RELATED APPLICATION This application is a continuation-in-part of my copending application Ser. No. 75,142, filed Sept. 24, 1970 now abandoned.

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a prosthetic device for the deaf and, more particularly, to a method and means for inducing the sensation of intelligible hearing, by direct electrical excitation of the auditory nerve endings distributed along the basilar membrane within the cochlea, in people suffering from sensory deafness. This condition is untreatable by acoustic amplification or bone conduction.

2. Description of the Prior Art The fundamentals of the hearing process, whereby the vibrations of the surrounding air called sound" are sensed by the auditory system and transmitted to the brain, are well defined. For present purposes, such hearing process may be briefly described as follows: The auditory system may be divided into its three component parts, namely the external, the middle and the internal ear. The external ear is outermost and includes the auricle attached to the side of the head and the external auditory meatus. Sound vibrations in the air are focused by the auricle and conveyed to the opening of the external ear canal which transmits such vibrations to the tympanic membrane which seals the inner end of the auditory meatus and forms the dividing line between the external and middle ears.

The middle ear is positioned within a space in the temporal bone of the skull and serves to transmit the vibratory movements of the tympanic membrane to the internal ear. The middle ear includes a series of bones called the auditory ossicles which include the ma]- leus, or hammer; the incus, or anvil; and the stapes or stirrup. The hammer is directly attached to the tympanic membrane whereas the stirrup is attached to a membrane positioned in a minute opening, called the oval window" in the bony area containing the internal ear. The auditory ossicles are interconnected so that the vibratory movements of the tympanic membrane are transmitted to the oval window, and sound is thus transmitted from the external to the inner ear.

The portion of the inner ear specifically concerned with hearing consists of the cochlea, a long, narrow duct within the temporal bone, which is wound spirally around its axis for approximately two and one-half turns. The cochlea is divided by a pair of membranes extending longitudinally therethrough into an upper, a middle and a lower scala. The oval window presents an opening into the upper scala. an additional minute opening, called the round window". providing an opening into the lower scala. the round window being closed by a membrane. The cochlea is filled with a fluid, the perilymph, which is free to circulate through the upper and lowerscalas which are interconnected at the apex of the cochlea.

The membrane between the middle scale and the lower scala, called the basilar membrane, extends the entire length of the cochlea duct. The auditory pathways from the cochlea terminate in the cerebral cortex of the brain. Theauditory nerve endings, distributed along the basilarmembrane, are indirect functional connection with the hair cells contained in the middle scala.

The vibratory movements of the tympanic membrane which are transmitted by the auditory ossicles to the oval window are distributed through the cochlea fluid throughout the cochlea. This vibratory input manifests itself in an alternating electrical field within the structure of the cochlea (which electrical field appears and has been detected at the round window). This electrical field (generated by the hair-cells) is sensed by the nerve endings in the basilar membrane and transmitted via the auditory nerve to the cerebral cortex of the brain which interprets such electrical signals as sound.

The loss of hearing, or a decrease in hearing sensitivity, may result from damage or abnormalities in the external, the middle or the internal ear. Where the hearing problem is a loss of sensitivity, the problem is usually solved by the use of a conventional hearing aid which simply amplifies the sound before transmission to the tympanic membrane. On the other hand, where hearing sensitivity is reduced to a point where additional amplification or bone conduction is useless, such conventional hearing aids are incapable of generating the sensation of hearing.

Where total loss of hearing is due to malfunctions in the external or middle ear, such as a stiffening of the tympanic membrane or an improper functioning of the auditory ossicles, hearing can usually be restored through surgical procedures whereby either the tympanic membrane or one or more of the auditory ossicles are replaced by man-made or human substitutes. However, the total loss of hearing as a result of difficulty in the external or middle ear represent a minority of actual cases. The majority of instances of total loss of hearing results from either sensory or neural deafness. In the former case, deafness results from a reduction in the sensitivity of the cochlea in the internal car which may be caused, for example, from a loss of hair cells, a chemical change in the perilymph, etc. ln the latter case, deafness results from damage to the auditory nerve itself, either through disease or physical rupture. In either case, where total deafness results, such that a conventional amplifying hearing aid is useless, no technology presently exists for successfully restoring the sensation of hearing.

Regarding the prior art which is considered to be relevant to the instant invention, reference is made to an article by Robin P. Michelson entitled The Crossed Cochlea Effect", published in the Transactions of the American Laryngological, Rhinological and Otoligical Society, pp. 626 to 644, 1968. In this publication Michelson describes experiments conducted to determine the extent of auditory reflexes in cats in order to obtain a better understanding of certain auditory functions and their interactions. In the experiments in audio signal (sound pressure signal) was applied to one ear of each cat and monitored by a cochlear microphonic electrode in the same ear. The signal was modified by an electrical stimulation in the contralateral ear. The purpose was to determine the levels of electrical stimulation in the contralateral ear which might suppress the cochlear microphonic signal in the acoustically stimulated ear. These levels were found to be approximately 250 microvolts to 2 millivolts. The center frequency of the tuning curve indicated a minimum stimulation or threshold level for acoustic reflex in the range of 250 to 500 microvolts. These stimulation levels are of the same order as the cochlear microphonic, i.e., the naturally generated electrical signal within the cochlea. Through these experiments it was demonstrated that there is an acoustic reflex ineraction between the two ears of a cat. The acoustic reflex, however, it not the same as the sensation of hearing. The experiments, therefore, did not demonstrate that the cats were actually hearing an audio signal. In fact, as will appear from the description hereinafter, the electrical and sound pressure stimuli used in these experiments was well below the minimum perception threshold required for the cats to hear.

The present invention involves the use of electrical stimulation of the auditory organ to produce hearing in the deaf. Reference is made to a second article by Robin P. Michelson entitled Electrical Stimulation of the Human Cochlea in Sensory Deafness, published in Archieves of Otolaryngology, March 1971, Vol. 93, pp. 317-323, which describes the efforts of other scientists prior to the present invention to produce hearing by electrical stimulation of the auditory organ, as well as results achieved with the use of the present invention. This article refers to an implanted electrode system dejveloped by James H. Doyle, which system is described in detail in US. Pat. No. 3,449,768. Doyle utilizes what he calls a neural potential generator which produces l KHZ clock pulses modulated in amplitude and width to create a complex modulation scheme which is intended to duplicate the firing rates and potentials of the neurons along the basilar membrane. A complex electrode is utilized consisting of a multiplicity of wires driven from a subcutaneous transformer in a unipolar manner from ground plane to the individual electrode wires. The electrode is so dimensioned that once it is inserted in the lower scala it is free to move therein. Thus, the pulses produced by the neural potential generator are distributed'in a random fashion along the basilar membrane without regard for the place frequency relationship. The place frequency relationship, first discovered by Von Bekesy, simply states that particular portions along the basilar membrane are related to specific frequencies. The area of the basilar membrane closest to the round window is associated with the high frequencies. The opposite end of the basilar membrane near the helicatrima is associated with the low frequencies. Doyle states that his patients heard the carrier frequency produced by the neural potential generator. The Doyle system has not been successful in inducing the sensation of intelligible hearing.

SUMMARY OF THE INVENTION In accordance with the present invention, there is disclosed a method for inducing the sensation of intelligible hearing by direct electrical stimulation of the auditory nerve endings of the auditory nerve. Since the present technique completely by-passes the external and middle ears and the hair cells of the inner ear, it is possible to induce the sensation of intelligible hearing in the absence of these structures. Thus, the present invention may be effectively used to induce the sensation of hearing in people suffering from deafness caused by abnormalities in any of these areas. However, the primary use will be in cases of sensory deafness which has, heretofore, been untreatable.

Briefly, the sensation of hearing is induced by positioning an electrode within the lower scala of the cochlea, such electrode being surgically inserted through the round window. The electrode consists of a resilient base member shaped to conform to the inner surface of the lower scala, such base member extending along the basilar membrane. The base member retains a pair of conductors which extend parallel to the length of the basilar membrane. Means are also provided for transmitting an excitation signal to a receiver implanted with and connected to the conductors. The excitation signal creates an electrical field between the conductors. This field is transmitted through the conductive cochlea fluid to the nerve endings in the basilar membrane, thus replacing the naturally generated auditory electric field.

It is therefore an object of the present invention to provide a prosthetic device for the deaf.

It is a further object of the present invention to provide a method and apparatus for inducing the sensation of hearing in individuals suffering from total or near total sensory deafness.

It is a still further object of the present invention to provide a method and apparatus for inducing the sensation of hearing by electrical stimulation of the nerve endings of the auditory nerve.

It is another-object of the present invention to provide a method and apparatus for inducing the sensation of hearing by positioning an electrode within the-lower scala of the cochlea and coupling electrical excitation signals to such electrode so as to directly stimulate the nerve endings of the auditory nerve distributed along the basilar membrane within the cochlea.

It is still another object of the present invention to provide means for exciting an intra-cochlear electrode.

Another object of the present invention is the provision of an intra-cochlear electrode which may be used to stimulate the nerve endings of the auditory nerve.

BRIEF DESCRIPTION'OF THE DRAWINGS FIG. 1 is a block diagram'showing the fundamental elements of the hearing process;

FIG. 2 is an enlarged, front elevation view, partly in section, of the human cochlea;

FIG. 3 is an enlarged, cross-sectional view taken along the line 3-3 in FIG. 2;

FIG. 4 is an enlarged, front elevation view of a first embodiment of intra-cochlear electrode;

FIG. 5 is a cross-sectional view taken along the line 5-5 in FIG. 4;

FIG. 6 is a cross-sectional view of the lower scala of the cochlea, similar to FIG. 3, showing the intracochlear electrode of FIGS. 4 and 5 in place;

FIGS. 7, 8 and 10 are front elevation views, partly in section, of alternate forms of intra-cochlear electrodes;

FIGS. 9 and 11 are cross-sectional views taken along the lines 9-9 and ll-11, respectively, in FIGS. 8 and 10, respectively;

FIG. 12 is a block diagram of a preferred embodiment of apparatus for exciting an ultra-cochlear electrode;

FIG. 13 is a circuit diagram of a preferred embodiment of the receiving elements of the circuit of FIG. 12;

FIG. 14 is a view showing the physical configuration of a preferred embodiment of electrode and receiver; and

FIG. 15 is a pictorial representation of an alternate embodiment of means for exciting an intra-cochlear electrode.

DESCRIPTION OF THE PREFERRED EMBODIMENTS Referring now to the drawings and, more particularly, to FIG. 1 thereof, there is shown, in block diagram form, the fundamental elements ofthe hearing process. Sound vibrations caused by an external'sound pressure generator set the air in motion producing spherical pressure waves 11. Pressure waves 11 are caught by the external ear 12 and transmitted to the tympanic membrane 13 which is displaced in response to such waves. The vibratory movements of the tympanic membrane 13 are transmitted via the auditory ossicles 14 to the oval window of the cochlea 15. Air cells within cochlea 15 function as a transducer to generate an alternating electrical field within cochlea 15. This electrical field is sensed by the nerve endings distributed through the basilar membrane and transmitted via the auditory nerve 16 to the celebral cortex 17 of the brain, which interprets such electrical signals as sound.

Referring now to FIGS. 2 and 3, the cochlea 15 is a long, narrow duct within the temporal bone which is wound spirally around its axis for approximately 2% turns. The cochlea is divided by a pair of membranes -21 and 22, extending longitudinally therethrough, into an upper scala 23, a middle scala 24 and a lower scala 25. The oval window 26, which is sealed by a membrane in contact with the stirrup of the auditory ossicles, presents an opening into upper scala 23. The round window 27, which is also closed by a membrane, provides an opening into lower scala 25. Cochlea 15 is filled with a fluid, the perilymph, which is free to circulate through upper scala 23 and lower scala 25 which are interconnected at the apex 28 of cochlea l5.

Membrane 21 between middle scala 24 and lower scala 25, called the basilar membrane, extends the entire length of cochlea 15. The auditory nerve 16 of the brain terminates in cochlea 15 and the nerve endings are distributed along basilar membrane 21. Minute hair cells 29 extend from basilar membrane 21 into middle scala 24.

The vibratory movements of tympanic membrane 13, which are transmitted by auditory ossicles 14 to oval window 26, are distributed through the cochlea fluid throughout cochlea 15. This vibratory input manifests itself in an alternating electrical field within the structure of the cochlea which electrical field appears and has been detected at round window 27). This electrical field (generated by hair cells 29) is sensed by the nerve endings of the auditory nerve in basilar membrane 21 and transmitted via the auditory nerve 16 to the cerebral cortex 17 of the brain which interprets such electrical signals as sound.

Where total loss of hearing results from sensory deafness, Le. a reduction in the sensitivity of the cochlea, no method or apparatus presently exists for restoring the sensation of hearing. However, in accordance with the present invention, it has been discovered that the sensation of hearing in people suffering from sensory deafness can be induced by direct electrical excitation of the auditory nerve endings distributed along basilar membrane 21 within cochlea 15 by using a bipolar electrode in the lower scala without the necessity of a complex encoding system such as disclosed in Doyle.

Referring now to FIGS. 4-6, direct electrical excitation of the auditory nerve endings within cochlea 15 is achieved by use of an intra-cochlear electrode, generally designated 30. The body 31 of electrode 30 is molded of a medically acceptable resilient material, such as silicone or other rubber or plastic material, which is of such a shape as to fit through round window 27 and into lower scala 25 of cochlea 15. Body 31 of electrode 30 includes a notch 32 which is designed to fit the round window margin and retain body 31 within lower scala 25 of cochlea 15. Electrode 30 further comprises a pair of gold or other suitable inert conductors 33 and 34 which are imbedded in and retained by base member 31. External leads 35 and 36 are connected to the ends of conductors 33 and 34, respectively, whereby leads 35 and 36 supply electrical signals to contacts 33 and 34, respectively. Body 31 may also include a stiffening member (not shown) imbedded therein, such as a strand of wire, to obtain the desired degree of resiliency.

As described more fully hereinafter, and as shown in FIG. 6, electrode 30 is inserted through round window 27 of cochlea 15 into lower scala 25 where it extends along the basilar membrane for approximately threefourths of a turn thereof. According to the embodiment of FIGS. 4-6, conductors 33 and 341 are positioned side-by-side, adjacent basilar membrane 21, each of conductors 33 and 34 extending parallel to the length of membrane 21. In addition, the shape of base member 31 is such so as to provide a space between the surface 37 thereof opposite conductors 33 and 34 and the wall of lower scala 25 to permit circulation of the cochlea fluid through lower scala 25 as well as a fluid escape path during insertion.

With an electrical excitation signal applied to conductors 33 and 34 via leads 35 and 36, respectively, a uniform alternating electrical field is generated therebetween. Because of the position of the conductors 33 and 34 in the lower scala, the electrical field generated therebetween is applied so as to allow place frequency selection to take place unlike the Doyle system. This field is tramsmitted through the conductive cochlea fluid to the nerve endings in basilar membrane 21, thus replacing the naturally generated auditory electric field. The electric field generated by conductors 33 and 34 is sensed by the nerve endings distributed along the basilar membrane 21 and conducted via the auditory nerve 16 to the cerebral cortex 17 of the brain which interprets such electrical signals as sound.

According to a preferred embodiment of the present invention, and as shown in FIGS. 4-6, conductors 33 and 34 are made from 2 mil gold wire wound on a 5 mil mandrel for approximately 30 turns. Conductors 33 and 341 so formed are inserted into notches in base member 31 so as to slightly extend beyond the outer periphery of base member 31. The conductors are then imbedded within base member 31 by filling such notches with additional resilient material. Three to five strands of 2 mil gold wire may serve as leads 35 and 36 for conducting an electrical excitation signal to conductors 33 and 34. In addition, as explained previously, conductors 33 and 34 extend parallel to the length of basilar membrane 21 for approximately three-fourths of a turn. This affords conductive means along a substantial length of basilar membrane 21, thereby exciting a relatively large frequency spectrum. More specificially, it has been found through experimentation that thenerve endings within basilar membrane 21 are frequency selective. The nerve endings adjacent round window 27 respond to frequencies at the high end of the audio spectrum and decrease in frequency sensitivity as the'apex 28 of cochlea is approached. Accordingly, by extending conductors 33 and 34 for a substantial length along basilar membrane 21, a relatively large frequency spectrum may be excited.

Referring now to FIG. 7, there is shown an alternate embodiment for an intra-cochlear electrode, generally designated 40. The external configuration of electrode 40 is identical to the external configuration of electrode 30 and includes a base member 41 composed of medically acceptable resilient material. Imbedded within base member 41 are a pair of inert conductors 42 and 43 which are positioned on opposite sides of base member 41, rather than being adjacent, on the same side as in the case of electrode 30. However, in spite of this different placement of conductors 42 and 43, the operation of electrode 40 is identical to the operation of electrode 30. In addition, external lead wires 44 and 45 are connected by weld, pressure form or solderfto one end of conductors 42 and 43, respectively. A notch 46 is also provided for'retaining electrode40 within cochlea 15 by pressure fit with the round window margin.

Other configurations of intra-cochlear electrodes suitable to other manufacturing methods are shown in FIGS. 8-11. In FIGS. 8 and 9,'an intra-cochlear electrode, generally designated 50, includes a base member 51 and multiple point contacts 52 and 53 plus gold flashing 54 and 55 over the length of base member 51 on opposite sides thereof. Vacuum deposition or other attachment means may be used for attaching the gold flashing. Lead wires 56 and 57 are connected to the multiple point contacts 52 and 53, respectively, to con duct electrical excitation signals to gold flashing 54 and 55, respectively. v

In FIGS. 10 and 1 1, an intra-cochlear electrode, generally designated 60, includes a base member 61 and large, flexible conductors 62 and 63 imbedded directly within base member 61 plus flashed or vacuum deposited gold or platinum surfaces 64 and 65 positioned on the surface of base member 61 on' opposite sides thereof. As before, a pair of lead wires 66 and 67 conduct electrical excitation signals to conductors 62 and 63, respectively.

Once intra-cochlear electrode 30, 40, 50 or 60 is positioned within lower scala 25 of cochlea 15, as will be explained more fully hereinafter, there must then be provided a means for coupling electrical signals to the conductors thereof. The problem with inducing electrical signals within the cochlea is, of course, the fact that no orifices are available for ready access to the tympanic cavity. The cochlea is well shielded within the heavy bony structure of the skull so that no direct entrance is possible without risk of infection. .The problem then become one of coupling electrical signals to the electrode within the cochlea without the use of normal wire conductive means.

Referring now to FIG. 12, there is shown a preferred embodiment of apparatus for exciting an intra-cochlear electrode. In this embodiment of FIG. 12, the vibrations of the surrounding air are sensed by a microphone 70 which converts the mechanical vibrations to an electrical signal in the audio spectrum which is applied to a preamplifier 71. The output of preamplifier 71 is applied via a tone control network 72, to be described more fully hereinafter, to a modulator 73. Modulator 73 is operative to modulate the output of a combination oscillator V.I-I.F. transmitter 74. .The output of oscillator/transmitter 74 is applied to an antenna 75 which, in its preferred form, is an inductive coil. The transmitting network, consisting of elements 70-75, may be mounted externally of the body to sense the sound waves and convert such sound waves into a modulated RF. signal. This modulated R.F. signal is sensed by a receiving antenna 76, which may also be an inductive coil, and applied to a receiver 77. The output of receiver 77 is demodulated by a demodulator 78 to restore the original audio excitation signal appearing at the output of tone control network 72. Finally, the output of demodulator 78 is applied to an intra-cochlear electrode 79.

The transmitting network consisting of elements 70 through 75 may have any suitable configuration since elements 70-75 are positioned externally'of the body, as will be explained more fully hereinafter, and size and complexity are not problems. On the other hand, since components 76-78 will be positioned internally of the body with electrode 79, theyshould be as simple as possible. A preferred configuration for elements 76-78 is shown in FIG. 13.

Referring now to FIG. 13,, receiver 77 may comprise a tuned circuit consisting of inductive coil 76 and a capacitor 81 tuned to the frequency of oscillator/transmitter 74. In the case where modulator 73 is an amplitude modulator, demodulator 78 may simply comprise a diode connected to one side of capacitor 81. The output of diode 82 may be shunted by a capacitor 83 and conducted via resistors 84 and 85 and a lead 87 to one conductor of electrode 79. An additional diode 86 shunts the junction between-resistors 84 and 85, the other side of capacitor 81 being connected via a lead 88 to the other conductor of electrode 79. In such circuit, capacitor 83 and resistor 84 act as a filter and current limiter, respectively. Diode 86 is a noise limiting diode such that noise peaks occurring due to electromagnetic discharges can be limited by forward conduction of diode'86. Resistor 85 also acts as a current limiting resistor in feeding theaudio signal to electrode 79.

Referring now to FIG. 14, the physical configuration of a preferred embodiment of the present invention is shown. Intra-cochlear electrode 79 is made integral with a continuous length 90 of medically acceptable resilient material in which leads 87 and 88 are imbedded. One end of leads 87 and 88 are connected to the conductors within electrode 79 whereas the other ends of leads 87 and 88 are connected to a small integrated circuit chip or substrate 91 carrying the inductors, capacitors, resistors and diodes. Included with chip 91 is receiving coil 76. Chip 91 is also imbedded within the resilient material. This entire structure, generally designated 92, would then be implanted "in vivo". A typical surgical procedure is as follows: The patient is placed on an operating table with the appropriate ear in a horizontal position exposed in a sterile field. The auricle is folded forwardly and clamped in position and an incision made posterior to the ear. Entry to the middle ear is gained by elevating the skin along the auditory meatus which permits a direct by-pass of the tympanic membrane. With the skin along the auditory meatus and the tympanic membrane elevated, visual contact may be made with the middle ear and the oval and round windows at the entrance to the cochlea. A bony promontory protruding above the round window is then removed to permit free access to the round window. The round window membrane is then removed and a portion of the upper margin excavated for easy access to the lower scala. Electrode 79 is then inserted through the round window such that the electrode conductors lay in close proximity to the basilar membrane between the lower scala and the scala media. Electrode 79 is inserted into the lower scala until the notch therein slips into the round window margin. A channel is then excavated in the bony structure along the auditory canal for ocation of material 90 containing leads 87 and 88, material 90 then being sutured into position. The elevated skin along the auditory canal is then carefully returned to its original position and the canal packed to assure proper adhesion.

The skin posterior to the incision is elevated and a small portion of the muscular structure attached to the skull removed to receive chip 91 which is then sutured in place. A pair of test leads 93 and 94, as shown in FIG. 14, are connected directly to leads 87 and 88 and extend outwardly from material 90 adjacent chip 91. Test leads 93 and 94 are brought out through the incision. The transmitting network is then activated and a signal transmitted to receiver. 77. The voltage across the intra-cochlear electrode is monitored on an oscilloscope via test leads 93 and 94 to insure operability. After the electrode is tested and found operative, test leads 93 and 94 are clipped and the incision sutured. The external ear is then returned to its normal position and the surgical procedure is completed.

With the surgical procedure completed, receiver 77 and antenna 76 in chip 91 are positioned immediately posterior to the ear close to and under the skin. A unit may then be mounted behind the ear, such unit including microphone 70, oscillator/transmitter 74 and transmitting antenna 75. The output of microphone 70 may be conducted through electrical leads to a pocketcarried unit containing preamplifier 71, tone control network 72, modulator 73 and a suitable power supply (not shown). The output of modulator 73 is then coupled back to the ear-mounted unit to oscillator/transmitter 74 and transmitting antenna 75. In this manner, transmitting and receiving antennas 75 and 76 will be positioned in close proximity to each other, only a thin layer of skin separating the two elements. As a result, the current passing through antenna 75 is induced in antenna 76 and applied to receiver 77.

With the elements so positioned, operation is as described previously with respect to FIGS. 12 and 13. In summary, the vibrations of the surrounding air are sensed by microphone 70 and converted to an amplified, shaped, modulated R.F. signal by components 71-74. The modulated signal is transmitted by antenna 74 to antenna 76 where receiver 77 and demodulator 78 reproduce the original audio excitation signal and apply it via leads 87 and 88 to electrode 79. With such electrical excitation signal applied to electrode 79, an electric field is generated between the conductors thereof. The electrical field so generated varies in amplitude proportioned to the pressure vibrations of the surrounding air, i.e., the audio signal to be heard. In other words, such field is an analog of the audio signal to be heard. The field generated between the conductors of electrode 79 is transmitted through the conductive cochlea fluid to the nerve endings in the basilar membrane, thus replacing the naturally generated auditory electric field. The electric field so generated is sensed by the nerve endingsdistributed along the basilar membrane and conducted via the auditory nerve to the cerebral cortex of the brain which interprets such electrical signals as sound.

Tone control network 72 is provided to shape the frequency spectrum of the signal applied to electrode 79, if desired. More specifically, initial tests with the present system have shown that it is not easy and, as a matter of fact, quite difficult, for a patient who has never heard to properly interpret the electrical stimulus now being applied to the auditory nerve endings. For this reason, it has been necessary to initially shape the frequency spectrum applied to a particular patient to correspond to stimuli his brain is capable of interpreting. As the patient gains experience in interpreting the signals applied to his cochlea, the frequency spectrum of the applied signal is slowly increased. Accordingly, tone control '72 is inserted between preamplifier 71 and modulator '73 to provide the desired shaping of the applied excitation signal.

The above-described system, including the intracochlear electrode shown in FIG. 4 and the electronics described with respect to FIGS. 12-14 have been tested by implantation in selected patients at Sequoia Hospital, Redwood City, California. The surgery has been performed by Dr. Robin P. Michelson. In one such implant procedure, the surgical approach was identical to that described hereinbefore. The patient was tested the following day by transmitting signals to the receiver and then in turn to the electrode. The patient exhibited the ability to distinguish tones over the frequency range 125 Hz to 4,000 Hz. His frequency discrimination at one octave steps from 250 Hz to 4,000 Hz was excellent. I-Ie exhibited amplitude discrimination of pure tones with a calculated change of less than 2 db. The patient further exhibited a dynamic range, i.e. threshold to maximum listening level, of approximately 10 db. He was given a Spondee Test and was able to recognize 6 of 35 words. The patient's previous score on this test with a hearing aid was zero. In further tests on this patient, transmitting to the patient a random series of the numbers one through 10, the patient is presently capable of correctly distinguishing the numbers approximately 65 percent of the time. In a second patient, where a similar implant procedure has been performed, such patient is capable of distinguishing a random series of the numbers one through ten approximately -95 percent of the time.

Several other configurations of excitation means are possible. With respect to the embodiment of FIG. 12, modulator '73 need not be an amplitude modulator but may be a frequency modulator, a pulse-width modulator or any other conventional form of modulator. In addition, it is theoretically possible to completely eliminate the use of a modulator. More specifically, the output of tone control network 72 may be applied directly to transmitting coil 75. Receiving coil '76 would then be connected directly to leads 37 and 88 of electrode 79, although filtering and noise and current limiting components may be employed. In other words, it is theoretically not necessary to modulate the audio signal on an R.F. carrier and then demodulate the signal, but rather the audio signal may be directly applied to receiving antenna 76 and electrode 79. The potential difficulty with this approach is possible patient sensitivity to random audio frequency noise in the atmosphere so that the modulation approach is preferred.

Referring now to FIG. 15, there is shown a still further embodiment of a means for exciting an intracochlear electrode where the auditory ossicles are intact. As explained previously, the tympanic membrane 101 couples sound vibrations through the hammer 102, the anvil 103 and the stirrup 104 to the membrane at the oval window of the cochlea. Accordingly, a small, permanent magnet 105 may be attached to the stirrup 104, as shown. An audio pick-up coil 106 may then be imbedded within the base of an intra-cochlear electrode 108 and connected via leads 107 to the conductors thereof. Coil 106 would be sutured adjacent or surrounding magnet 105.

in operation, motion of permanent magnet 105 in proximity to coil 106 induces an d.m.f. within coil 106. This e.m.f. is then carried by leads 107 to the electrode and presented to the basilar membrane between the scala mediav and the lower scala within the cochlea. The conversion of thise.m.f. to sound would then be as described previously.

in tests which have been conducted on human patients it has been found that the threshold of auditory perception under electrical stimulation is a function of frequency. The voltage measured across the conductors of the intra-cochlear electrode which is required to stimulate auditory perception increases as frequency increases. At 1 KHz, three patients exhibited a threshold of auditory perception of approximately 0.5 volt while at 100 Hz, this threshold was observed to be approximately '0.1 'volt. At higher frequencies, in the range of 2 to 5 KHz, stimulation levels as high as 1 volt were required. It has been found that the minimum electrical stimulation required for auditory perception in human patients is about 0.05 volt. Thus, in order to induce hearing ina human subject, it is necessary that at least 0.05 volt be impressed across the conductors of the intracochlear electrode of the present invention.

Comparative tests between brain reception and electrical or acoustical stimulation in cats and human subjects have been recently conducted to determine the stimulation level required to achieve equivalent hearing results. The brain reception of electrical and acoustical stimulation in cats was determined by recording the electrical response of the inferior colliculus, one of the higher hearing centers in the brain, since obviously a cat cannot relate to the investigator its level of auditory perception. The test demonstrated that cats appear to show identical responses from electrical andacoustical stimulation when stimulated at the same level as human patients. Since the minimum auditory perception threshold in humans is approximately 0.05 volt, it can be deduced that a comparable minimum perception level occurs in cats. Because the maximum electrical stimulation utilized in the previous tests described in the aforementioned Michelson article entitled "The Crossed Cochlea Effect was 250 microvolts,

it is apparent from the comparative tests discussed hereinbefore that the cats used in the previous tests could not hear at the levels of stimulation utilized.

Therefore, and in accordance with the present invention, there is disclosed a method and apparatus for including the sensation of hearing by direct electrical stimulation of the auditory nerve endings of the auditory nerve. Since the present technique completely bypasses the external and middle ears and most of the internal ear other than the basilar membrane, it may be effectively used to induce the sensation of hearing in people suffering from deafness caused by abnormalities in any of these areas. However, the primary use will be in the case of sensory deafness which has, heretofore, been untreatable.

In accordance with the present invention, the sensation of hearing is induced by positioning an intracochlear electrode within the lower scala of the cochlea, such electrode being surgically inserted through the round window. The electrode includes a pair of conductors which extend parallel to the length of the basilar membrane. Means are disclosed for transmitting an excitation signal to a receiver implanted with and connected to the conductors. Such excitation signal creates a uniform, alternating electrical field between the conductors, which electrical field is transmitted through the conductive cochlea fluid to the nerve endings in the basilar membrane, thus replacing the naturally generated auditory electric field. The electrical field so generated is sensed by the nerve endings distributed through basilar membrane '21 and conducted via the auditory nerve to the cerebral cortex of the brain which interprets such electrical signals as sound.

While the invention has been described with respect to the preferred physical embodiments. constructecl in accordance therewith, it will be apparent to those skilled in the art that various modifications and improvements may be made without departing from the scope and spirit ofthe invention. For example, although the preferred embodiment of apparatus for generating an alternatingelectrical field along the basilar membrane within the cochlea comprises an electrode adapted to be positioned within the lowerscala of the cochlea, it will be appreciated by those skilled in the art tht it is theoretically possible, although notpresently practical, to position an electrode within the upper scala or the middle scala of the cochlea. Accordingly, it is to be understood that the invention is not to be limited by the specific illustrative embodiments, but only by the scope of the appended claims.

I claim:

1. Apparatus for inducing sensations of hearing in a human subject comprising an elongate curved electrode adapted to be positioned within the lower scala of a cochlea of the subject, with the electrode extending lengthwise along a portion of the lower scala,

receiving means coupled to said electrode for receiving an electrical excitation signal being an analog of an externally generated audio signal and for applying said excitation signal uniformly to said electrode, and

transmitting means responsive to said externally generated audio signal for transmitting said electrical excitation signal to said receiving means.

2. The apparatus of claim 1 wherein said electrode includes an elongate resilient base member shaped to substantially conform to part of the inner surface of the lower scala, and

a pair of conductors secured to said base member for receiving said electrical excitation signal from said receiving means, said conductors extending lengthwise of the base member whereby each of the conductors is positioned proximate auditory nerve endings distributed along the same longitudinal section of the cochlea. 3. The apparatus of claim 2 wherein said base member has a cross-sectional area less than the crosssectional area of the portion of the lower scala within which it is positioned whereby flow of cochlea fluid past the base member is relatively unimpeded.

4. Apparatus according to claim 2 wherein said transmitting means comprises:

transducer means responsive to said externally generated audio signal for converting said audio signal into said electrical excitation signal; and

transmitting antenna means adapted to be positioned adjacent the external ear of the subject for radiating said excitation signal;

and wherein said receiving means for receiving and applying said excitation signal to said conductors comprises;

receiving antenna means adapted to be positioned under the skin adjacent said external ear; and

a pair of electrical leads connected between said receiving antenna means and said conductors.

5. Apparatus according to claim 4 wherein said receiving antenna means is connected via said electrical leads to said conductors, said receiving antenna means and said leads being imbedded within a resilient material, said receiving antenna means being adapted to be implanted between the skin and the temporal bone of the skull, posterior to the ear of the subject, and wherein said transducer means and said transmitting antenna means are positioned exterior to the skin, said transmitting antenna means being adapted to be positioned posterior to said ear adjacent to said receiving antenna means.

6. Apparatus according to claim 4 wherein said transmitting means further comprises:

means for generating a carrier signal having a frequency outside of the audio spectrum, said carrier signal being coupled to said transmitting antenna means; and

means for modulating said carrier signal with said electrical excitation signal; and wherein said means for receiving and applying said excitation signal to said conductors further includes:

tuned circuit means having a resonant frequency corresponding to the frequency of said carrier signal; and

means coupled between said tuned circuit means and said pair of electrical leads for demodulating said carrier signal and for applying said excitation signal to said electrical leads.

7. Apparatus according to claim 6 wherein said modulator means is an amplitude modulator and wherein said means for demodulating comprises:

a diode coupled between said tuned circuit means and said pair of electrical leads.

8. Apparatus according to claim 6 wherein said tuned circuit means, said demodulator means and said receiving antenna means are formed on a microelectronic substrate.

9. Apparatus according to claim 2 wherein said transmitting means comprises:

permanent magnet means permanently attached to the stapes of the auditory ossicles of the subject; and wherein said receiving means includes,

an inductive pick-up coil imbedded within said resilient base member and connected to said conductors, said inductive pick-up coil being positioned adjacent said permanent magnet.

10. Apparatus according to claim 2 wherein said conductors are flexible and are imbedded within said base member in side-by-side relationship proximate to the basilar membrane of the cochlea.

11. Apparatus according to claim wherein a por- 10 tion of each said conductor projects beyond the outer periphery of said base member.

12. Apparatus according to claim 10 wherein said conductors are positioned on opposite sides of said base member.

13. Apparatus according to claim 2 wherein each of said conductors includes multiple point contacts imbedded within said base member, said point contacts being arranged along a line adapted to extend parallel to the length of the basilar membrane within the cochlea; and

a conductive coating on the surface of said base member, said point contacts being in electrical contact with said coating. 14. Apparatus according to claim 2 wherein said rethe basilar membrane to which said electrode means is proximate, and generator means for inductively coupling to said electrode means an alternating electrical excitation 0 signal which is an analog of an audio signal.

16. The apparatus of claim 15 wherein said electrode means includes an elongate curved resilient base member and a pair of elongate conductors secured to said base member lengthwise thereof whereby said conductors are positioned lengthwise of the cochlea.

17. The apparatus of claim 16 wherein said generator means includes first means adapted to be implanted under the skin of the subject for applying said excitation signal to said conductor; and

second means responsive to said audio signal for inductively coupling said excitation signal to said first means.

18. The apparatus of claim 16 wherein each of said conductors comprises an elongate member adapted to extend parallel to the length of the basilar membrane and wherein said generator means generates a uniform field along a substantial portion of said basilar membrane.

19. Apparatus according to claim 16 wherein said generating means is operative to generate a uniform field along a substantial portion of said basilar membrane.

20. A method for inducing the sensation of hearing in a human subject comprising:

positioning an electrode within the cochlea, said electrode including a base member and a pair of conductors retained upon said base member said electrode being positioned with said conductors extending longitudinally along a portion of the chamher; and

inductively coupling an electrical excitation signal being an analog of an externally generated audio signal to said conductors.

21. The method of claim wherein a potential of not less than about 0.05 volts is impressed across said conductor. 7

22. The method of claim 20 wherein the step of inductively coupling an electrical excitation signal to said conductors comprises:

implanting a receiving antenna under the skin adjacent the external ear;

connecting said receiving antenna to said conductors; positioning a transducer externally of the skin, said transducer converting said externally generated audio signal into said electrical excitation signal;

coupling the output of said transducer to a transmitting antenna; and

positioning said transmitting antenna externally of the skin adjacent the external ear adjacent said receiving antenna.

23. The method of claim 22 wherein the step of coupling the output of said transducer to a transmitting an tenna comprises:

generating a carrier signal having a frequency outside of the audio spectrum;

coupling said carrier signal to said transmitting antenna;

modulating said carrier signal with said electrical excitation signal; and wherein said step of connecting said receiving antenna to said conductors comprises:

connecting said receiving antenna to a tuned circuit having a resonant frequency corresponding to the frequency of said carrier signal;

demodulating said carrier signal; and

coupling said demodulated carrier signal to said electrical leads.

24. The method of claim 20 wherein the step of inductively coupling an electrical excitation signal to said conductors comprises:

attaching a permanent magnet to the stapes of the auditory ossicles;

embedding an inductive pick-up coil within said base member;

connecting said inductive pick-up coil to said conductors; and

positioning said inductive pick-up coil adjacent said permanent magnet.

Claims (24)

1. Apparatus for inducing sensations of hearing in a human subject comprising an elongate curved electrode adapted to be positioned within the lower scala of a cochlea of the subject, with the electrode extending lengthwise along a portion of the lower scala, receiving means coupled to said electrode for receiving an electrical excitation signal being an analog of an externally generated audio signal and for applying said excitation signal uniformly to said electrode, and transmitting means responsive to said externally generated audio signal for transmitting said electrical excitation signal to said receiving means.
2. The apparatus of claim 1 wherein said electrode includes an elongate resilient base member shaped to substantially conform to part of the inner surface of the lower scala, and a pair of conductors secured to said base member for receiving said electrical excitation signal from said receiving means, said conductors extending lengthwise of the base member whereby each of the conductors is positioned proximate auditory nerve endings distributed along the same longitudinal section of the cochlea.
3. The apparatus of claim 2 wherein said base member has a cross-sectional area less than the cross-sectional area of the portion of the lower scala within which it is positioned whereby flow of cochlea fluid past the base member is relatively unimpeded.
4. Apparatus according to claim 2 wherein said transmitting means comprises: transducer means responsive to said externally generated audio signal for converting said audio signal into said electrical excitation signal; and transmitting antenna means adapted to be positioned adjacent the external ear of the subject for radiating said excitation signal; and wherein said receiving means for receiving and applying said excitation signal to said conductors comprises; receiving antenna means adapted to be positioned under the skin adjacent said external ear; and a pair of electrical leads connected between said receiving antenna means and said conductors.
5. Apparatus according to claim 4 wherein said receiving antenna means is connected via said electrical leads to said conductors, said receiving antenna means and said leads being imbedded within a resilient material, said receiving antenna means being adapted to be implanted between the skin and the temporal bone of the skull, posterior to the ear of the subject, and wherein said transducer means and said transmitting antenna means are positioned exterior to the skin, said transmitting antenna means being adapted to be positioned posterior to said ear adjacent to said receiving antenna means.
6. Apparatus according to claim 4 wherein said transmitting means further comprises: means for generating a carrier signal having a frequency outside of the audio spectrum, said carrier signal being coupled to said transmitting antenna means; and means for modulating said carrier signal with said electrical excitation signal; and wherein said means for receiving and applying said excitation signal to said conductors further includes: tuned circuit means having a resonant frequency corresponding to the frequency of said carrier signal; and means coupled between said tuned circuit means and said pair of electrical leads for demodulating said carrier signal and for applying said excitation signal to said electrical leads.
7. Apparatus according to claim 6 wherein said modulator means is an amplitude modulator and wherein said means for demodulating comprises: a diode coupled between said tuned circuit means and said pair of electrical leads.
8. Apparatus according to claim 6 wherein said tuned circuit means, said demodulator means and said receiving antenna means are formed on a microelectronic substrate.
9. Apparatus according to claim 2 wherein said transmitting means comprises: permanent magnet means permanently attached to the stapes of the auditory ossicles of the subject; and wherein said receiving means includes, an inductive pick-up coil imbedded within said resilient base member and connected to said conductors, said inductive pick-up coil being positioned adjacent said permanent magnet.
10. Apparatus according to claim 2 wherein said conductors are flexible and are imbedded within said base member in side-by-side relationship proximate to the basilar membrane of the cochlea.
11. Apparatus according to claim 10 wherein a portion of each said conductor projects beyond the outer periphery of said base member.
12. Apparatus according to claim 10 wherein said conductors are positioned on opposite sides of said base member.
13. Apparatus according to claim 2 wherein each of said conductors includes multiple point contacts imbedded within said base member, said point contacts being arranged along a line adapted to extend parallel to the length of the basilar membrane within the cochlea; and a conductive coating on the surface of said base member, said point contacts being in electrical contact with said coating.
14. Apparatus according to claim 2 wherein said receiving means applies a potential of at least 0.05 volts across said condUctors.
15. Apparatus for inducing sensations of hearing in a human subject comprising elongate electrode means adapted to be positioned in a cochlea of the subject, lengthwise of a portion of the lower scala, responsive to an alternating electrical excitation signal for applying a uniform electrical field to stimulate auditory nerve endings located along a corresponding lengthwise portion of the basilar membrane to which said electrode means is proximate, and generator means for inductively coupling to said electrode means an alternating electrical excitation signal which is an analog of an audio signal.
16. The apparatus of claim 15 wherein said electrode means includes an elongate curved resilient base member and a pair of elongate conductors secured to said base member lengthwise thereof whereby said conductors are positioned lengthwise of the cochlea.
17. The apparatus of claim 16 wherein said generator means includes first means adapted to be implanted under the skin of the subject for applying said excitation signal to said conductor; and second means responsive to said audio signal for inductively coupling said excitation signal to said first means.
18. The apparatus of claim 16 wherein each of said conductors comprises an elongate member adapted to extend parallel to the length of the basilar membrane and wherein said generator means generates a uniform field along a substantial portion of said basilar membrane.
19. Apparatus according to claim 16 wherein said generating means is operative to generate a uniform field along a substantial portion of said basilar membrane.
20. A method for inducing the sensation of hearing in a human subject comprising: positioning an electrode within the cochlea, said electrode including a base member and a pair of conductors retained upon said base member said electrode being positioned with said conductors extending longitudinally along a portion of the chamber; and inductively coupling an electrical excitation signal being an analog of an externally generated audio signal to said conductors.
21. The method of claim 20 wherein a potential of not less than about 0.05 volts is impressed across said conductor.
22. The method of claim 20 wherein the step of inductively coupling an electrical excitation signal to said conductors comprises: implanting a receiving antenna under the skin adjacent the external ear; connecting said receiving antenna to said conductors; positioning a transducer externally of the skin, said transducer converting said externally generated audio signal into said electrical excitation signal; coupling the output of said transducer to a transmitting antenna; and positioning said transmitting antenna externally of the skin adjacent the external ear adjacent said receiving antenna.
23. The method of claim 22 wherein the step of coupling the output of said transducer to a transmitting antenna comprises: generating a carrier signal having a frequency outside of the audio spectrum; coupling said carrier signal to said transmitting antenna; modulating said carrier signal with said electrical excitation signal; and wherein said step of connecting said receiving antenna to said conductors comprises: connecting said receiving antenna to a tuned circuit having a resonant frequency corresponding to the frequency of said carrier signal; demodulating said carrier signal; and coupling said demodulated carrier signal to said electrical leads.
24. The method of claim 20 wherein the step of inductively coupling an electrical excitation signal to said conductors comprises: attaching a permanent magnet to the stapes of the auditory ossicles; embedding an inductive pick-up coil within said base member; connecting said inductive pick-up coil to said conductors; and positioning said inductive pick-up coil adjacent said permanent magnet.
US00223415A 1972-02-04 1972-02-04 Prosthetic device for the deaf Expired - Lifetime US3752939A (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
US22341572A true 1972-02-04 1972-02-04

Publications (1)

Publication Number Publication Date
US3752939A true US3752939A (en) 1973-08-14

Family

ID=22836391

Family Applications (1)

Application Number Title Priority Date Filing Date
US00223415A Expired - Lifetime US3752939A (en) 1972-02-04 1972-02-04 Prosthetic device for the deaf

Country Status (1)

Country Link
US (1) US3752939A (en)

Cited By (61)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
FR2403084A1 (en) * 1977-09-15 1979-04-13 Commissariat Energie Atomique Hearing aid implant having a shaped silicone rubber body - and opt. having PTFE clad conductor terminals
EP0002068A2 (en) * 1977-11-22 1979-05-30 Carl Christian Hansen Electrode for implantation into cochlea
EP0002226A1 (en) * 1977-11-22 1979-06-13 Carl Christian Hansen Electrode for implantation into cochlea
EP0007157A2 (en) * 1978-05-04 1980-01-23 The University Of Melbourne Improved electrode array and method of making the same
US4207441A (en) * 1977-03-16 1980-06-10 Bertin & Cie Auditory prosthesis equipment
US4267410A (en) * 1977-11-03 1981-05-12 The University Of Melbourne Prosthesis
EP0054418A2 (en) * 1980-12-12 1982-06-23 The Commonwealth Of Australia Improvements in speech processors
USRE31031E (en) * 1977-03-16 1982-09-14 Implantable electronic hearing aid
US4400590A (en) * 1980-12-22 1983-08-23 The Regents Of The University Of California Apparatus for multichannel cochlear implant hearing aid system
US4419995A (en) * 1981-09-18 1983-12-13 Hochmair Ingeborg Single channel auditory stimulation system
DE3227483A1 (en) * 1981-04-09 1984-01-26 Telectronics Pty Ltd Implantable tissue-stimulating prosthesis
EP0109304A1 (en) * 1982-11-15 1984-05-23 Minnesota Mining And Manufacturing Company Anchor and insertion tool for anchoring electrode leads used in cochlear implantation
US4462402A (en) * 1982-11-15 1984-07-31 Minnesota Mining And Manufacturing Company Method and anchor for anchoring
US4462401A (en) * 1982-11-15 1984-07-31 Minnesota Mining And Manufacturing Company Method and anchor for anchoring electrode leads used in cochlear implantation
US4487210A (en) * 1982-11-15 1984-12-11 Minnesota Mining And Manufacturing Company Anchor for anchoring electrode leads used in cochlear implantation
US4535785A (en) * 1982-09-23 1985-08-20 Minnesota Mining And Manufacturing Co. Method and apparatus for determining the viability and survival of sensori-neutral elements within the inner ear
EP0179536A2 (en) * 1984-10-22 1986-04-30 Cochlear Pty., Ltd. Improvements in power transfer for implanted prostheses
US4611596A (en) * 1980-10-14 1986-09-16 Purdue Research Foundation Sensory prostheses
US4628907A (en) * 1984-03-22 1986-12-16 Epley John M Direct contact hearing aid apparatus
EP0241101A1 (en) 1983-04-11 1987-10-14 The Commonwealth Of Australia Cochlear implant system with psychological testing or programming with mapped patient responses provided to encoder
AU582264B2 (en) * 1985-08-19 1989-03-16 University Of Melbourne, The Prosthetic electrode array
US4890618A (en) * 1985-09-12 1990-01-02 Bertin & Cie Nerve-stimulating device for auditory prosthesis
US4918745A (en) * 1987-10-09 1990-04-17 Storz Instrument Company Multi-channel cochlear implant system
US5015224A (en) * 1988-10-17 1991-05-14 Maniglia Anthony J Partially implantable hearing aid device
US5073947A (en) * 1988-10-22 1991-12-17 Dragerwerk Ag Hearing device for a protective helmet
US5095904A (en) * 1989-09-08 1992-03-17 Cochlear Pty. Ltd. Multi-peak speech procession
WO1993006698A1 (en) * 1991-09-27 1993-04-01 Cochlear Pty. Limited Self-curving cochlear electrode array
US5217011A (en) * 1989-06-20 1993-06-08 Storz Instrument Company Method and apparatus for transdermal communication
US5271397A (en) * 1989-09-08 1993-12-21 Cochlear Pty. Ltd. Multi-peak speech processor
US5443493A (en) * 1989-09-22 1995-08-22 Alfred E. Mann Foundation For Scientific Research Cochlea stimulating electrode assembly, insertion tool, holder and method of implantation
DE3250100C2 (en) * 1982-07-20 1996-06-05 Cochlear Pty Ltd Single chip implantable cochlear stimulating prosthesis
US5549658A (en) * 1994-10-24 1996-08-27 Advanced Bionics Corporation Four-Channel cochlear system with a passive, non-hermetically sealed implant
US5603726A (en) * 1989-09-22 1997-02-18 Alfred E. Mann Foundation For Scientific Research Multichannel cochlear implant system including wearable speech processor
US5624376A (en) * 1993-07-01 1997-04-29 Symphonix Devices, Inc. Implantable and external hearing systems having a floating mass transducer
WO1997030670A1 (en) * 1996-02-26 1997-08-28 Med-El Elektromedizinische Geräte GmbH Structure method of use, and method of manufacture of an implanted hearing prosthesis
US5712917A (en) * 1994-11-22 1998-01-27 George C. Offutt System and method for creating auditory sensations
US5800336A (en) * 1993-07-01 1998-09-01 Symphonix Devices, Inc. Advanced designs of floating mass transducers
US5876425A (en) * 1989-09-22 1999-03-02 Advanced Bionics Corporation Power control loop for implantable tissue stimulator
US5891183A (en) * 1996-06-04 1999-04-06 Med-El Elektromedizinische Gerate Ges.M.B.H. Device for transferring electromagnetic energy between primary and secondary coils
US5897486A (en) * 1993-07-01 1999-04-27 Symphonix Devices, Inc. Dual coil floating mass transducers
US5913815A (en) * 1993-07-01 1999-06-22 Symphonix Devices, Inc. Bone conducting floating mass transducers
US6214046B1 (en) 1996-11-25 2001-04-10 St. Croix Medical, Inc. Method of implanting an implantable hearing assistance device with remote electronics unit
US6231604B1 (en) * 1998-02-26 2001-05-15 Med-El Elektromedizinische Gerate Ges.M.B.H Apparatus and method for combined acoustic mechanical and electrical auditory stimulation
US20030161481A1 (en) * 2002-02-26 2003-08-28 Miller Douglas Alan Method and system for external assessment of hearing aids that include implanted actuators
US20030161482A1 (en) * 2002-02-26 2003-08-28 Miller Douglas Alan Method and system for external assessment of hearing aids that include implanted actuators
US6676592B2 (en) 1993-07-01 2004-01-13 Symphonix Devices, Inc. Dual coil floating mass transducers
US6731769B1 (en) * 1998-10-14 2004-05-04 Sound Techniques Systems Llc Upper audio range hearing apparatus and method
US20050131272A1 (en) * 2003-12-11 2005-06-16 Bernd Waldmann Electrophysiological measurement method and system for positioning an implantable, hearing instrument transducer
US20060085051A1 (en) * 2004-10-19 2006-04-20 Fritsch Michael H Electrical implants
US7054691B1 (en) 2002-01-02 2006-05-30 Advanced Bionics Corporation Partitioned implantable system
US20060247488A1 (en) * 2005-04-27 2006-11-02 Bernd Waldmann Implantable hearing aid actuator positioning
US20060269076A1 (en) * 2002-02-26 2006-11-30 Miller Douglas A Method and system for external assessment of hearing aids that include implanted actuators
US20090041285A1 (en) * 2006-08-31 2009-02-12 Red Tail Hawk Corporation Wireless Communications Headset System Employing a Loop Transmitter that Fits Around the Pinna
WO2010025514A1 (en) * 2008-09-04 2010-03-11 Cochlear Limited Ion switch for neural stimulation
US20100296667A1 (en) * 2006-08-31 2010-11-25 Red Tail Hawk Corporation Wireless Earplug with Improved Sensitivity and Form Factor
CN104013480A (en) * 2014-06-13 2014-09-03 山东大学 Artificial cochlea acoustic nerve conductive electrode array capable of sensing music melodies
US9083388B2 (en) 2012-08-29 2015-07-14 Red Tail Hawk Corporation Transmitter with improved sensitivity and shielding
US9525930B2 (en) 2006-08-31 2016-12-20 Red Tail Hawk Corporation Magnetic field antenna
US10058698B2 (en) 2013-08-27 2018-08-28 Advanced Bionics Ag Asymmetric cochlear implant electrodes and method
US10058699B2 (en) 2013-08-27 2018-08-28 Advanced Bionics Ag Implantable leads with flag extensions
US10058697B2 (en) 2013-08-27 2018-08-28 Advanced Bionics Ag Thermoformed electrode arrays

Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2164121A (en) * 1938-05-04 1939-06-27 Pescador Hector Electric hearing apparatus for the deaf
US2995633A (en) * 1958-09-25 1961-08-08 Henry K Puharich Means for aiding hearing
US3170993A (en) * 1962-01-08 1965-02-23 Henry K Puharich Means for aiding hearing by electrical stimulation of the facial nerve system
US3209081A (en) * 1961-10-02 1965-09-28 Behrman A Ducote Subcutaneously implanted electronic device
US3267931A (en) * 1963-01-09 1966-08-23 Henry K Puharich Electrically stimulated hearing with signal feedback
US3393279A (en) * 1962-03-13 1968-07-16 Listening Inc Nervous system excitation device
US3449768A (en) * 1966-12-27 1969-06-17 James H Doyle Artificial sense organ
US3493695A (en) * 1967-03-10 1970-02-03 Fredrick J Stork Hearing aid

Patent Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2164121A (en) * 1938-05-04 1939-06-27 Pescador Hector Electric hearing apparatus for the deaf
US2995633A (en) * 1958-09-25 1961-08-08 Henry K Puharich Means for aiding hearing
US3209081A (en) * 1961-10-02 1965-09-28 Behrman A Ducote Subcutaneously implanted electronic device
US3170993A (en) * 1962-01-08 1965-02-23 Henry K Puharich Means for aiding hearing by electrical stimulation of the facial nerve system
US3393279A (en) * 1962-03-13 1968-07-16 Listening Inc Nervous system excitation device
US3267931A (en) * 1963-01-09 1966-08-23 Henry K Puharich Electrically stimulated hearing with signal feedback
US3449768A (en) * 1966-12-27 1969-06-17 James H Doyle Artificial sense organ
US3493695A (en) * 1967-03-10 1970-02-03 Fredrick J Stork Hearing aid

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
The Crossed Cochlea Effect by Michelson, Actions of American Laryngological, Rhinological and Othological Society Inc. Presented 1/3/68, Received in Library of Medicine 1/8/69 *

Cited By (89)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
USRE31031E (en) * 1977-03-16 1982-09-14 Implantable electronic hearing aid
DK155033B (en) * 1977-03-16 1989-01-30 Bertin & Cie Equipment for hoereprotese
US4207441A (en) * 1977-03-16 1980-06-10 Bertin & Cie Auditory prosthesis equipment
FR2403084A1 (en) * 1977-09-15 1979-04-13 Commissariat Energie Atomique Hearing aid implant having a shaped silicone rubber body - and opt. having PTFE clad conductor terminals
US4267410A (en) * 1977-11-03 1981-05-12 The University Of Melbourne Prosthesis
EP0002068A2 (en) * 1977-11-22 1979-05-30 Carl Christian Hansen Electrode for implantation into cochlea
EP0002068A3 (en) * 1977-11-22 1979-06-13 Carl Christian Hansen Electrode for implantation into cochlea
US4261372A (en) * 1977-11-22 1981-04-14 Hansen Carl C Electrode for implantation into cochlea
EP0002226A1 (en) * 1977-11-22 1979-06-13 Carl Christian Hansen Electrode for implantation into cochlea
US4284085A (en) * 1977-11-22 1981-08-18 Hansen Carl C Electrode for implantation into the cochlea (II)
EP0007157A3 (en) * 1978-05-04 1980-08-20 The University Of Melbourne Improved electrode array and method of making the same
EP0007157A2 (en) * 1978-05-04 1980-01-23 The University Of Melbourne Improved electrode array and method of making the same
US4611596A (en) * 1980-10-14 1986-09-16 Purdue Research Foundation Sensory prostheses
EP0054418A3 (en) * 1980-12-12 1982-08-11 The Commonwealth Of Australia Improvements in speech processors
EP0054418A2 (en) * 1980-12-12 1982-06-23 The Commonwealth Of Australia Improvements in speech processors
US4400590A (en) * 1980-12-22 1983-08-23 The Regents Of The University Of California Apparatus for multichannel cochlear implant hearing aid system
DE3227483A1 (en) * 1981-04-09 1984-01-26 Telectronics Pty Ltd Implantable tissue-stimulating prosthesis
US4419995A (en) * 1981-09-18 1983-12-13 Hochmair Ingeborg Single channel auditory stimulation system
DE3250100C2 (en) * 1982-07-20 1996-06-05 Cochlear Pty Ltd Single chip implantable cochlear stimulating prosthesis
US4535785A (en) * 1982-09-23 1985-08-20 Minnesota Mining And Manufacturing Co. Method and apparatus for determining the viability and survival of sensori-neutral elements within the inner ear
US4462401A (en) * 1982-11-15 1984-07-31 Minnesota Mining And Manufacturing Company Method and anchor for anchoring electrode leads used in cochlear implantation
US4487210A (en) * 1982-11-15 1984-12-11 Minnesota Mining And Manufacturing Company Anchor for anchoring electrode leads used in cochlear implantation
EP0109304A1 (en) * 1982-11-15 1984-05-23 Minnesota Mining And Manufacturing Company Anchor and insertion tool for anchoring electrode leads used in cochlear implantation
US4462402A (en) * 1982-11-15 1984-07-31 Minnesota Mining And Manufacturing Company Method and anchor for anchoring
EP0241101A1 (en) 1983-04-11 1987-10-14 The Commonwealth Of Australia Cochlear implant system with psychological testing or programming with mapped patient responses provided to encoder
EP0247649A1 (en) 1983-04-11 1987-12-02 The Commonwealth Of Australia Cochlear implant prosthesis current switching and power supply
US4628907A (en) * 1984-03-22 1986-12-16 Epley John M Direct contact hearing aid apparatus
EP0179536A2 (en) * 1984-10-22 1986-04-30 Cochlear Pty., Ltd. Improvements in power transfer for implanted prostheses
EP0179536A3 (en) * 1984-10-22 1987-05-13 Cochlear Pty., Ltd. Improvements in power transfer for implanted prostheses
AU582264B2 (en) * 1985-08-19 1989-03-16 University Of Melbourne, The Prosthetic electrode array
US4890618A (en) * 1985-09-12 1990-01-02 Bertin & Cie Nerve-stimulating device for auditory prosthesis
US4918745A (en) * 1987-10-09 1990-04-17 Storz Instrument Company Multi-channel cochlear implant system
US5015224A (en) * 1988-10-17 1991-05-14 Maniglia Anthony J Partially implantable hearing aid device
US5073947A (en) * 1988-10-22 1991-12-17 Dragerwerk Ag Hearing device for a protective helmet
US5217011A (en) * 1989-06-20 1993-06-08 Storz Instrument Company Method and apparatus for transdermal communication
US5095904A (en) * 1989-09-08 1992-03-17 Cochlear Pty. Ltd. Multi-peak speech procession
US5271397A (en) * 1989-09-08 1993-12-21 Cochlear Pty. Ltd. Multi-peak speech processor
US5603726A (en) * 1989-09-22 1997-02-18 Alfred E. Mann Foundation For Scientific Research Multichannel cochlear implant system including wearable speech processor
US5443493A (en) * 1989-09-22 1995-08-22 Alfred E. Mann Foundation For Scientific Research Cochlea stimulating electrode assembly, insertion tool, holder and method of implantation
US5609616A (en) * 1989-09-22 1997-03-11 Alfred E. Mann Foundation For Scientific Research Physician's testing system and method for testing implantable cochlear stimulator
US5876425A (en) * 1989-09-22 1999-03-02 Advanced Bionics Corporation Power control loop for implantable tissue stimulator
WO1993006698A1 (en) * 1991-09-27 1993-04-01 Cochlear Pty. Limited Self-curving cochlear electrode array
US5578084A (en) * 1991-09-27 1996-11-26 Cochlear Ltd. Self-curving cochlear electrode array
US5913815A (en) * 1993-07-01 1999-06-22 Symphonix Devices, Inc. Bone conducting floating mass transducers
US6475134B1 (en) 1993-07-01 2002-11-05 Symphonix Devices, Inc. Dual coil floating mass transducers
US6676592B2 (en) 1993-07-01 2004-01-13 Symphonix Devices, Inc. Dual coil floating mass transducers
US5624376A (en) * 1993-07-01 1997-04-29 Symphonix Devices, Inc. Implantable and external hearing systems having a floating mass transducer
US5800336A (en) * 1993-07-01 1998-09-01 Symphonix Devices, Inc. Advanced designs of floating mass transducers
US5857958A (en) * 1993-07-01 1999-01-12 Symphonix Devices, Inc. Implantable and external hearing systems having a floating mass transducer
US5897486A (en) * 1993-07-01 1999-04-27 Symphonix Devices, Inc. Dual coil floating mass transducers
US5749912A (en) * 1994-10-24 1998-05-12 House Ear Institute Low-cost, four-channel cochlear implant
US5549658A (en) * 1994-10-24 1996-08-27 Advanced Bionics Corporation Four-Channel cochlear system with a passive, non-hermetically sealed implant
US5712917A (en) * 1994-11-22 1998-01-27 George C. Offutt System and method for creating auditory sensations
WO1997030670A1 (en) * 1996-02-26 1997-08-28 Med-El Elektromedizinische Geräte GmbH Structure method of use, and method of manufacture of an implanted hearing prosthesis
US5891183A (en) * 1996-06-04 1999-04-06 Med-El Elektromedizinische Gerate Ges.M.B.H. Device for transferring electromagnetic energy between primary and secondary coils
US6235056B1 (en) 1996-11-25 2001-05-22 St. Croix Medical, Inc. Implantable hearing assistance device with remote electronics unit
US6214046B1 (en) 1996-11-25 2001-04-10 St. Croix Medical, Inc. Method of implanting an implantable hearing assistance device with remote electronics unit
US6231604B1 (en) * 1998-02-26 2001-05-15 Med-El Elektromedizinische Gerate Ges.M.B.H Apparatus and method for combined acoustic mechanical and electrical auditory stimulation
US6731769B1 (en) * 1998-10-14 2004-05-04 Sound Techniques Systems Llc Upper audio range hearing apparatus and method
US7054691B1 (en) 2002-01-02 2006-05-30 Advanced Bionics Corporation Partitioned implantable system
US20030161481A1 (en) * 2002-02-26 2003-08-28 Miller Douglas Alan Method and system for external assessment of hearing aids that include implanted actuators
US20060269076A1 (en) * 2002-02-26 2006-11-30 Miller Douglas A Method and system for external assessment of hearing aids that include implanted actuators
US6879693B2 (en) * 2002-02-26 2005-04-12 Otologics, Llc. Method and system for external assessment of hearing aids that include implanted actuators
US7447319B2 (en) 2002-02-26 2008-11-04 Otologics, Llc Method and system for external assessment of hearing aids that include implanted actuators
US20030161482A1 (en) * 2002-02-26 2003-08-28 Miller Douglas Alan Method and system for external assessment of hearing aids that include implanted actuators
US20050131272A1 (en) * 2003-12-11 2005-06-16 Bernd Waldmann Electrophysiological measurement method and system for positioning an implantable, hearing instrument transducer
US7137946B2 (en) 2003-12-11 2006-11-21 Otologics Llc Electrophysiological measurement method and system for positioning an implantable, hearing instrument transducer
US20060085051A1 (en) * 2004-10-19 2006-04-20 Fritsch Michael H Electrical implants
US20060247488A1 (en) * 2005-04-27 2006-11-02 Bernd Waldmann Implantable hearing aid actuator positioning
US7582052B2 (en) 2005-04-27 2009-09-01 Otologics, Llc Implantable hearing aid actuator positioning
US9351064B2 (en) 2006-08-31 2016-05-24 Red Rail Hawk Corporation Wireless communications headset system employing a loop transmitter that fits around the pinna
US20090041285A1 (en) * 2006-08-31 2009-02-12 Red Tail Hawk Corporation Wireless Communications Headset System Employing a Loop Transmitter that Fits Around the Pinna
US20100296667A1 (en) * 2006-08-31 2010-11-25 Red Tail Hawk Corporation Wireless Earplug with Improved Sensitivity and Form Factor
US9525930B2 (en) 2006-08-31 2016-12-20 Red Tail Hawk Corporation Magnetic field antenna
US9774946B2 (en) 2006-08-31 2017-09-26 Red Tail Hawk Corporation Wireless earplug with improved sensitivity and form factor
US8688036B2 (en) 2006-08-31 2014-04-01 Red Tail Hawk Corporation Wireless communications headset system employing a loop transmitter that fits around the pinna
US8693720B2 (en) 2006-08-31 2014-04-08 Red Tail Hawk Corporation Wireless earplug with improved sensitivity and form factor
US9516404B2 (en) 2006-08-31 2016-12-06 Red Tail Hawk Corporation Wireless earplug with improved sensitivity and form factor
US8311640B2 (en) 2008-09-04 2012-11-13 Cochlear Limited Variable impedance bypass pathway for a tissue stimulating prosthesis
US8843208B2 (en) 2008-09-04 2014-09-23 Cochlear Limited Variable impedance shunt for a tissue stimulating prosthesis
US20110166627A1 (en) * 2008-09-04 2011-07-07 Paul Carter Variable impedance bypass pathway for a tissue stimulating prosthesis
WO2010025514A1 (en) * 2008-09-04 2010-03-11 Cochlear Limited Ion switch for neural stimulation
US9083388B2 (en) 2012-08-29 2015-07-14 Red Tail Hawk Corporation Transmitter with improved sensitivity and shielding
US9548537B2 (en) 2012-08-29 2017-01-17 Red Tail Hawk Corporation Transmitter with improved sensitivity and shielding
US10058697B2 (en) 2013-08-27 2018-08-28 Advanced Bionics Ag Thermoformed electrode arrays
US10058698B2 (en) 2013-08-27 2018-08-28 Advanced Bionics Ag Asymmetric cochlear implant electrodes and method
US10058699B2 (en) 2013-08-27 2018-08-28 Advanced Bionics Ag Implantable leads with flag extensions
CN104013480A (en) * 2014-06-13 2014-09-03 山东大学 Artificial cochlea acoustic nerve conductive electrode array capable of sensing music melodies
CN104013480B (en) * 2014-06-13 2016-04-13 山东大学 Melody perceived auditory nerve conduction cochlear electrode array

Similar Documents

Publication Publication Date Title
Doyle et al. Electrical stimulation of eighth cranial nerve
Wilson et al. Cochlear implants: some likely next steps
AU597661B2 (en) Cochlear implant system with psychophysical testing or programming with mapped patient responses provided to encoder
EP1009316B1 (en) Apparatus and method for an auditory stimulator
AU2003294020B2 (en) Implantable hearing system
US4267410A (en) Prosthesis
US8945216B2 (en) Objective fitting of a hearing prosthesis
US8265773B2 (en) Electrode assembly having a flexible tip
Wilson et al. Cochlear implants: current designs and future possibilities
US5571148A (en) Implantable multichannel stimulator
US6175767B1 (en) Multichannel implantable inner ear stimulator
US3629521A (en) Hearing systems
US5788656A (en) Electronic stimulation system for treating tinnitus disorders
US7617000B2 (en) Methods for programming a neural prosthesis
US7974711B2 (en) Double stylet insertion tool for a cochlear implant electrode array
US5344387A (en) Cochlear implant
NL192973C (en) The implantable electromagnetic hearing aid with middle ear bone-conduction.
AU2005304453B2 (en) Method and system of matching information from cochlear implants in two ears
US7367992B2 (en) Curved cochlear implant electrode array
Eddington et al. Auditory prostheses research with multiple channel intracochlear stimulation in man
US20070118185A1 (en) Transcutaneous power optimization circuit for a medical implant
US7974712B2 (en) Pre-curved cochlear implant electrode array
Chouard et al. Implantation of multiple intracochlear electrodes for rehabilitation of total deafness: preliminary report
EP1173044B1 (en) Implantable system for the rehabilitation of a hearing disorder
US20060052841A1 (en) Multiple channel-electrode mapping

Legal Events

Date Code Title Description
AS Assignment

Owner name: UNIVERSITY OF CALIFORNIA A NONPROFIT EDUCATIONAL I

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST.;ASSIGNOR:BECKMAN INSTRUMENTS, INC.;REEL/FRAME:003990/0485

Effective date: 19820301

AS Assignment

Owner name: BOSTON SCIENTIFIC NEUROMODULATION CORPORATION, CAL

Free format text: CHANGE OF NAME;ASSIGNOR:ADVANCED BIONICS CORPORATION;REEL/FRAME:020299/0200

Effective date: 20071116

AS Assignment

Owner name: BOSTON SCIENTIFIC NEUROMODULATION CORPORATION, CAL

Free format text: CHANGE OF NAME;ASSIGNOR:ADVANCED BIONICS CORPORATION;REEL/FRAME:020309/0361

Effective date: 20071116