WO2000069513A1 - Reseau d'electrodes pour stimulateur cochleaire hybride - Google Patents

Reseau d'electrodes pour stimulateur cochleaire hybride Download PDF

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Publication number
WO2000069513A1
WO2000069513A1 PCT/US2000/013121 US0013121W WO0069513A1 WO 2000069513 A1 WO2000069513 A1 WO 2000069513A1 US 0013121 W US0013121 W US 0013121W WO 0069513 A1 WO0069513 A1 WO 0069513A1
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WO
WIPO (PCT)
Prior art keywords
electrode
cochlea
slit
wire
electrode array
Prior art date
Application number
PCT/US2000/013121
Other languages
English (en)
Inventor
Janusz A. Kuzma
William Vanbrooks Harrison
Thomas J. Balkany
Original Assignee
Advanced Bionics Corporation
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 Corporation filed Critical Advanced Bionics Corporation
Priority to US09/979,800 priority Critical patent/US6889094B1/en
Priority to EP00930682A priority patent/EP1185332A4/fr
Priority to CA002371125A priority patent/CA2371125A1/fr
Priority to AU48460/00A priority patent/AU4846000A/en
Publication of WO2000069513A1 publication Critical patent/WO2000069513A1/fr

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Classifications

    • 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

Definitions

  • the present invention relates to implantable electrode arrays, and more particularly to an implantable electrode array configured for implantation within the basal end of the scala tympani duct of a human cochlea.
  • Such electrode array is best suited for use with a hybrid cochlear stimulation of the type described in applicant's copending patent application, filed concurrently herewith, entitled “Hybrid Implantable Cochlear Stimulation Hearing Aid System” (Attorney Docket Number AB-088-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.
  • 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.
  • 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. Because the ganglion cells responsible for sensing higher frequency sounds are all generally located in or near the basal end of the cochlea (the end of the cochlea nearest the round window membrane), 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. No such electrode array, to applicants' knowledge, currently exists.
  • the present invention addresses the above and other needs by providing a cochlear electrode array suitable for use with a hybrid cochlear stimulation system.
  • the cochlear electrode array comprises a relatively skinny, elongate carrier of from 6-8 mm in length.
  • Four to eight spaced- apart electrode contacts reside along one of the flat sides of the carrier, each of which is connected to a respective wire embedded within the carrier.
  • the wires exit a proximal end of the carrier via a wire bundle.
  • the wire bundle is connectable to an implantable cochlear stimulator (ICS) or equivalent pulse generator.
  • ICS implantable cochlear stimulator
  • the electrode array is inserted into the relatively straight portion of the basal end of the scala tympani duct of the cochlea through a small slit made in the round window membrane that separates the cochlea from the middle ear.
  • the slit is oriented so as to place the electrode contacts facing the modiolar wall.
  • the proximal end of the carrier may include flexible flaps or tines that maintain the electrode array in its desired position within the basal end of the cochlea. Such tines or flaps further help seal the carrier against the slit opening to prevent fluids from escaping the cochlea.
  • the cochlea thus remains filled with fluid which can activate hair cells as fluid waves are established through motion of the round window membrane, which is the normal process for hearing.
  • a cochlear electrode is provided that is made by forming a small ball electrode of about 0.4 mm diameter on the end of a very fine, or thin, flexible platinum/iridium (Pt/Ir) wire.
  • the fine Pt/Ir wire is insulated at every point along its length, except at its ends.
  • the ball electrode is formed.
  • a suitable connector allows the wire to be detachably connected to a pulse generator or other stimulator or electrical circuitry.
  • the insulation is made from a suitable biocompatible insulative coating, such as a Teflon® coating.
  • the electrode thus formed at the distal end of the wire is referred to hereafter as a "ball electrode".
  • a very small incision or slit e.g., not much longer than the diameter of the ball electrode, is first made in the membrane of the round window.
  • the ball electrode is then loaded into the distal tip of an insertion tube in such a way that the ball end is held at the distal tip of the tube by tension applied to the thin wire.
  • the end of the insertion tube is preferably beveled so as to better hold the electrode ball in position at its distal tip.
  • Insertion of the ball electrode into the cochlea is made by forcing the ball electrode, held at the distal end of the insertion tube, through the small slit made in the round window membrane.
  • the round window tissue will stretch to allow the ball electrode to pop through to the inner side of the cochlea.
  • the insertion tube may be withdrawn, leaving behind the ball electrode held against the inside of the round window membrane with the thin flexible lead extending through the tiny incision made in the round window membrane.
  • the thin wire may then be coiled within the inner ear cavity, or elsewhere, as required to adjust its length, and connected to a suitable electrical stimulator through an appropriate connector.
  • the electrical stimulator may then be controlled in an appropriate manner so as to provide electrical current stimulation through the ball electrode to the tissue at the basal end of the cochlea, to thereby compensate for high frequency hearing loss, and/or to suppress tinnitus.
  • a reference or return electrode e.g., located on the case of the stimulator, may be used with the ball electrode in order to provide a suitable electrical return path for the electrical current that is applied through the ball electrode.
  • FIG. 1A is a side view of an electrode array made in accordance with a first embodiment the present invention
  • FIG. 1 B is a medial side view of the electrode array of FIG. 1A;
  • FIG. 2 illustrates placement of the electrode array of FIGS. 1A and 1 B into the basal end of the scala tympani duct of a human cochlea in accordance with the present invention
  • FIG. 3 is a sectional view of the cochlea taken along the line 3-3 of FIG. 2;
  • FIG. 4 depicts the manner in which a slit is made in the round window membrane in order to allow the electrode array to be inserted into the cochlea;
  • FIG. 5 shows an alternate insertion technique of the electrode array of FIGS. 1A and 1 B into the cochlea
  • FIG. 6 shows a ball electrode in accordance with a second embodiment of the present invention attached to the distal end of a thin, flexible, insulated Pt/Ir wire;
  • FIG. 7 illustrates the first step of implanting the ball electrode, i.e, making a small incision or slit in the round window membrane with a sharp cutting tool
  • FIG. 8A depicts the ball electrode loaded under tension at the distal end of an insertion tube
  • FIG. 8B is an enlarged view of the distal end of the insertion tube of FIG. 8A;
  • FIG. 9A schematically illustrates the manner in which the ball electrode is pushed through the small insertion so as to reside on the inner side of the round window membrane;
  • FIG. 9B shows the way in which the round window membrane closes around the thin flexible wire after the ball electrode has been pushed through the slit into the cochlea
  • FIG. 10 shows a stimulation or other system that uses the ball electrode of the present invention to, e.g., compensate for high frequency hearing loss, suppress tinnitus, or other purposes.
  • Corresponding reference characters indicate corresponding components or elements throughout the several views of the drawings.
  • FIGS. 1A and 1 B An electrode array 10 made in accordance with a first embodiment of the present invention is illustrated in FIGS. 1A and 1 B.
  • FIG. 1A is a side view of the electrode array 10; and
  • FIG. 1 B is a view of a medial side of the electrode array 10.
  • the "medial side” of the electrode array 10 is the side on which a plurality of spaced-apart electrode contacts 14 are located.
  • the electrode array 10 includes a plurality of spaced-apart electrode contacts 14 on a flexible carrier 12.
  • each of the electrode contacts 14 resides on the same side - the medial side 15- of the carrier 12.
  • Each electrode contact 12 has at least one wire conductor 22 connected thereto. These wire conductors are embedded within the flexible carrier 12 and exit through a proximal end of the carrier 12 within a flexible cable 20.
  • the cable 20, including its wire conductors 22, connect to a pulse generator, or other suitable stimulator (not shown).
  • Such wire conductors 22 thus provide a means for making electrical contact with each of the electrode contacts 14.
  • the pulse generator When used as part of a hybrid or other cochlear stimulator system, the pulse generator, or other stimulator, thus generates electrical pulses or electrical currents ("electrical stimuli") that is/are applied to selective ones of the electrode contacts 14 in order to evoke a desired response from the ganglion cells located in the vicinity of the electrode contacts 14.
  • electrical stimuli electrical pulses or electrical currents
  • a head 18 At a proximal end of the electrode array 10 is a head 18.
  • the head 18 comprises a portion of the flexible carrier 12 that is larger than the carrier 12, thereby creating a shoulder 19 that defines the boundary between the carrier 12 and the head 18.
  • a plurality of flaps 16, or tines, protrude out from the body of the carrier 12 near the proximal end of the carrier at a slanting angle ⁇ , where ⁇ is as defined in FIG. 1A.
  • ⁇ is an acute angle of from 20-45°.
  • the wire conductors 22 pass through the head 18, exiting via the cable 20 which is connected to the head 18 at its proximal end.
  • the electrode array 10 is thinner in one direction than in the other. Stated differently, the electrode array 10 is flattened in one direction, and when viewed in cross section (see FIG. 3), resembles a pancake or paddle. As seen in FIG. 1A, for example, with the electrode contacts 14 facing upwards, the width of the carrier body 14 is W1. As seen in FIG. 1B, with the electrode contacts 14 facing out of the plane of the paper, the width of the carrier body 14 is W2, where W2 is 3-4 times larger than W1. Typically, W1 may be about 0.5 to 1.0mm; whereas W2 may be on the order of 2-3mm.
  • the length of the electrode array 10, from the shoulder 19 to a distal tip 13 is a distance L1. This distance L1 will typically be 6-8 mm.
  • the number of spaced-apart electrode contacts 14 positioned on the medial side of the carrier body 14 may vary from four to eight.
  • the electrode contacts 14 are all on a medial side of the electrode array, i.e., are all on the same side of the carrier 12, and the medial side is one of the "flat" sides of the carrier 12.
  • This medial side of the electrode array 10 is positioned so as to face the modiolar wall of the cochlea, where the ganglion cells are located.
  • the electrode contacts 14 are not mandatory. In practice, the electrode contacts 14 could be located on any side of the flexible carrier body 14, or on all sides (e.g., bands or rings), and the electrode array could still perform its intended function of stimulating the ganglion cells located near the basal end of the cochlea.
  • the electrode array 10 is a short electrode array, e.g., 6-8 mm, compared with a conventional cochlear electrode array, (which is typically 25-30 mm in length).
  • the electrode array 10 extends into the scala tympani duct only in the region 34 near the basal end of the scala tympani duct, and the array 10 remains substantially straight, without having to extend past the first bend of the spiraling scala tympani duct.
  • the electrode array 10 may be inserted into the basal region 14 through a narrow slit 42 (FIG. 4) made in the round window membrane (round window) 40.
  • the electrode array 10 is inserted through the slit 42 until the flaps or tines 16 have passed through the slit into the basal region 34, and the shoulder 19, formed by the head 18, rests against the middle-ear side of the round window membrane 40.
  • the body 12 of the electrode array 12 effectively plugs the narrow slit 42 so that the fluid normally present within the scala tympani duct is retained therein.
  • Retaining such fluid within the scala tympani duct is important so that the normal hearing processes may continue throughout the remaining portions -e.g., the middle and apex portions- of the cochlea. Further, the flexible flaps or tines 16, once passed through the slit 42, prevent the electrode array from slipping out of the slit 42.
  • the array 10 is held in position within the basal region 34 by the shoulder 19, and flaps or tines 16. Moreover, because the electrode array 10 is "flattened", or pancake shaped (when viewed in cross section as seen in FIG. 3), the distal tip 13 and the rest of the array 10 readily slide through the slit 42.
  • the slit 42 advantageously maintains the medial side of the array 10 facing in the right direction -i.e., facing the modiolar wall 32. Insertion of the electrode array 10 into the cochlea is thus a simple and straight-forward process, requiring only a few seconds, once access to the round window has been obtained.
  • the electrode array 10 may be made using conventional techniques, from conventional materials, as is known in the cochlear electrode array art.
  • the alternate approach shown in FIG. 5 has the electrode array 10 being inserted into the basal region 34 through a side slit made near the round window membrane. Such side slit is made at the bottom of a cavity 44, which cavity 44 is made in the bone structure adjacent the cochlea 30.
  • the electrode array 10 slides through the slit as shown, and is held in position by the shoulder 19 and flaps or tines 16, with its medial side and the electrode contacts 14 facing the modiolar wall 32.
  • the present invention provides an electrode array that may be easily inserted into the basal end of the cochlea of a hearing-impaired patient, with its electrode contacts held in position facing the modiolar wall where the ganglion cells responsible for sensing higher frequency sounds are located.
  • the electrode array 10 of the invention may be inserted into the basal end of the scala tympani duct of a human cochlea without destroying the function of the round window membrane, and without leaving an open hole through which fluid may escape from the scala tympani duct. This advantageously allows normal hearing processes (fluid motion activation of hair cells) to occur in regions other than the basal end of the cochlea.
  • the electrode array 10 described herein may be used with a hybrid cochlear implantable stimulator system designed to provide electrical stimulation through the electrode array for sensing high frequency audio sounds, which allows normal hearing processes to occur for sensing low and middle frequency sounds.
  • a hybrid cochlear stimulation syste is described in applicants' copending patent application, filed concurrently herewith, entitled “Hybrid Implantable Cochlear Stimulation Hearing Aid System” (Attorney Docket Number AB-088-PC).
  • the electrode 100 includes an exposed (non-insulated) ball electrode 120 located at the distal end of a flexible wire 140.
  • the ball electrode 120 is made from a suitable biocompatible conductive material, such as Pt/Ir, and has a diameter of about 0.40mm.
  • the wire 140 comprises a thin, e.g., 0.025 to 0.050 mm diameter, flexible Pt/Ir wire, insulated with a suitable biocompatible material, such as Teflon® insulation.
  • the ball electrode 120 may be formed using any suitable process, e.g., flaming and forming the end of the wire 140 into a ball of the desired size.
  • FIG. 7 illustrates the first step of implanting the ball electrode 100.
  • This first step involves making a small incision or slit 190 in the round window membrane 200 of the cochlea 300.
  • the slit 190 should have a length that is at least as large as the diameter of the ball electrode, and preferably a little larger. For example, where the ball electrode 120 has a diameter of 0.40mm, the slit 190 could have a length of about 0.50mm.
  • the small incision or slit 190 may be made in the round window membrane 200 using any suitable technique, e.g., by cutting the membrane 200 with the sharp tip 180 of a cutting tool 160.
  • FIG. 8A a second step of implanting the electrode 100 is depicted.
  • Such second step involves the use of an insertion tube 400. More particularly, the ball electrode 120 is loaded under tension at a distal end 420 of the insertion tube 400, with the flexible wire 140 passing through the insertion tube.
  • the diameter of the insertion tube should be similar to the diameter of the ball electrode 120, e.g., 0.4mm.
  • FIG. 8B which shows an enlarged view of the distal end of the insertion tube of FIG. 8A, the distal end 42 of the insertion tube 400 is preferably beveled to match the curvature of the surface of the ball electrode 120.
  • Such beveling advantageously helps secure the ball electrode 120 firmly at the distal end 420 of the insertion tube when tension is placed on the wire 140 exiting from a proximal end 440 of the tube, thereby preventing the ball electrode 120 from rolling off of the distal tip when it is forced through the slit 190 of the round window.
  • FIG. 9A schematically illustrates a side view of the manner in which the ball electrode 120 is pushed through the small insertion 190 so as to reside on the inner side of the round window membrane 200.
  • FIG. 9B shows a front view of the round window membrane 200 and best illustrates the way in which the round window membrane 200 closes around the thin flexible wire 140 after the ball electrode has been pushed through the slit 190 into the cochlea.
  • the insertion is performed by forcing the ball electrode 120 through the slit 190 while the ball electrode is held under tension at the distal tip 420 of the insertion tube 400.
  • the round window membrane 200 will stretch, as needed, to allow the ball electrode to pop through to the inner side, as seen best in FIG. 9A.
  • the insertion tool 400 may be withdrawn, as shown in FIG. 9A, leaving the round window membrane 200 closed tightly around the thin wire 140, and thereby holding the ball electrode 120 in place and minimizing any leak of fluid from the cochlea.
  • the wire 140 may be coiled or otherwise routed to an implanted, or external, electrical circuitry 500, as seen in FIG. 10.
  • the electrical circuitry 500 comprises an electrical stimulator, e.g., a pulse generator.
  • the circuitry 500 in addition to comprising a pulse generator, may also comprise monitoring or sensing circuitry, or other types of signal generation circuitry, e.g., an analog current source that can provide continuous or pulsed currents through the electrode ball 120 and a return electrode 520.
  • the stimulator (or other circuitry) 500 will typically be implanted, but may be external as circumstances warrant.
  • the electrode wire 140 is detachably connected to the circuitry 500 by means of an appropriate connector 540.
  • the circuitry 500 may generate electrical stimulation pulses 560 which are controlled to occur in a desired spatiotemporal pattern.
  • spatialotemporal refers to the relative time duration or time delay between pulses of controlled amplitudes.
  • the pulses 560 may comprise a pulse train having a pulse separation time of T1 seconds (thereby providing a pulse repetition rate of 1/T1 Hz), with a pulse width of time PW1 , and with a pulse amplitude modulated with an appropriate control signal.
  • the pulse separation time may range, e.g., from 10 microseconds to 100 milliseconds, with a pulse width PW1 ranging from 1 microsecond to 100 milliseconds, depending upon the purpose for which the pulses are applied.
  • the pulses 560 are applied to the ball electrode 120, which electrode is paired with a suitable reference or return electrode 520. Typically, the return electrode 520 forms an integral part of the case within which the stimulator 500 is housed.
  • the stimulation pattern of electrical pulses 560 applied through the ball electrode are thus applied monopolariy to the cochlear tissue at the basal end of the cochlea.
  • the return electrode may be positioned at any desired location outside or inside of the cochlea; or a second ball electrode could be inserted through the round window membrane near the first, and electrical stimulation applied bipolarly through the two ball electrodes.
  • the spatiotemporal pattern of electrical pulses applied through one or more ball electrodes (120) is controlled for the purpose of enhancing or compensating for high frequency hearing loss by stimulating the cochlea in the basal region where the electrode ball(s) 120 is/are positioned.
  • the spatiotemporal pattern of stimulation may be controlled for the purpose of suppression of tinnitus.
  • the round window membrane 200 is able to continue to function as a vibrating membrane, thereby allowing the normal residual hearing functions of the cochlea and inner ear to continue to function.
  • the ball electrode 120 is minimally invasive to the hearing process, is easy to implant or insert, and provides desired benefits (compensation of high frequency hearing loss, and/or suppression of tinnitus).
  • the stimulator 500 may be of any suitable design.
  • Representative cochlear stimulators that may be used with the electrode 100 are disclosed, e.g., in United States Patent Numbers 3,752,939; 4,400,590; and/or 5,603,726; each of which is incorporated herein by reference.
  • One-channel pulse generators of any conventional design e.g., of the type commonly employed in single channel implantable pacemakers, could also be employed.
  • the second embodiment of the present invention provides a small ball electrode that may be inserted into the basal end of the cochlea through a minimally invasive insertion process.
  • Such electrode may thereafter be used to stimulate ganglion cells located near the basal end of the cochlea for the purpose of, e.g., compensating for high frequency hearing loss and/or to suppress tinnitus.
  • the second embodiment of the invention provides a method of implanting a ball electrode through the round window membrane of the cochlea that is minimally invasive, thereby avoiding, or at least significantly minimizing, any adverse reaction to the implant, such as tissue or new bone formation that adversely affects residual hearing function in the implanted ear.

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  • Otolaryngology (AREA)
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  • Radiology & Medical Imaging (AREA)
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Abstract

L'invention concerne un réseau d'électrodes conçu pour être implanté dans l'extrémité basale de la rampe tympanique de la cochlée humaine. Selon un premier mode de réalisation, le réseau d'électrodes (10) est constitué d'un support allongé et mince (12) de 6 à 8 mm. de long. Entre quatre et huit contacts d'électrode espacés (14) sont placés le long d'un des côtés plats du support, chacun étant connecté à un câble (22) incrusté dans le support. Les câbles sortent d'une extrémité proximale du support via un faisceau de câbles qui est connecté, à son tour, à un stimulateur cochléaire implantable (ICS) ou à un générateur d'impulsions équivalent. Le réseau d'électrodes (10) est inséré dans la partie relativement droite de l'extrémité basale de la rampe tympanique de la cochlée à travers une petite fente (42) ménagée dans la membrane de la fenêtre ronde qui sépare la cochlée de l'oreille moyenne. La fente est orientée de telle sorte que les contacts d'électrodes sont placés face à la paroi de la columelle (32). L'extrémité proximale du support peut présenter des ailettes (16) ou des dents maintenant le réseau d'électrodes dans la position souhaitée au sein de l'extrémité basale de la cochlée. De telles dents ou ailettes facilitent le scellement du support contre l'ouverture de la fente pour éviter que les liquides ne s'échappent de la cochlée. Ce dernier est rempli d'un fluide qui active les cellules ciliées alors que des ondes fluidiques se forment par le mouvement de la membrane. La stimulation électrique est uniquement acheminée par l'extrémité basale de la cochlée via le réseau d'électrodes pour assurer l'écoute de sons haute fréquence. Une écoute normale (activation des cellules ciliées à travers le mouvement fluidique) se produit au niveau de régions supérieure et moyenne de la cochlée permettant de capter les sons basse fréquence. Selon un second mode de réalisation, on obtient l'électrode (100) en réalisant une petite bille (120) d'environ 0,4 mm de diamètre sur l'extrémité d'un câble souple de platine/iridium (Pt/Ir) très fin (140). Au niveau de l'extrémité proximale du câble, un connecteur adapté (540) assure la connexion/déconnexion du câble à un générateur d'impulsions (500).
PCT/US2000/013121 1999-05-14 2000-05-12 Reseau d'electrodes pour stimulateur cochleaire hybride WO2000069513A1 (fr)

Priority Applications (4)

Application Number Priority Date Filing Date Title
US09/979,800 US6889094B1 (en) 1999-05-14 2000-05-12 Electrode array for hybrid cochlear stimulator
EP00930682A EP1185332A4 (fr) 1999-05-14 2000-05-12 Reseau d'electrodes pour stimulateur cochleaire hybride
CA002371125A CA2371125A1 (fr) 1999-05-14 2000-05-12 Reseau d'electrodes pour stimulateur cochleaire hybride
AU48460/00A AU4846000A (en) 1999-05-14 2000-05-12 Electrode array for hybrid cochlear stimulator

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
US13429099P 1999-05-14 1999-05-14
US60/134,290 1999-05-14
US13521799P 1999-05-21 1999-05-21
US60/135,217 1999-05-21

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AU (1) AU4846000A (fr)
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Cited By (12)

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US6549814B1 (en) 2000-06-09 2003-04-15 Juergen Strutz Blade electrode array for insertion under soft tissue of lateral wall of cochlea
US6628991B2 (en) 2000-04-28 2003-09-30 Advanced Bionics Corporation Minimally-invasive access into the cochlea for electrode insertion and fluid delivery
WO2010035149A3 (fr) * 2008-09-16 2010-06-17 Med-El Elektromedizinische Geraete Gmbh Electrode d’implant cochléaire à deux branches
US8000798B2 (en) 2002-06-28 2011-08-16 Cochlear Limited Cochlear implant system substantially preserving the hydrodynamic nature of the cochlea
US8086319B2 (en) 2004-05-10 2011-12-27 Cochlear Limited Cochlear implant fitting
US8150527B2 (en) 2004-04-02 2012-04-03 Advanced Bionics, Llc Electric and acoustic stimulation fitting systems and methods
US8244365B2 (en) 2004-05-10 2012-08-14 Cochlear Limited Simultaneous delivery of electrical and acoustical stimulation in a hearing prosthesis
US8718795B2 (en) 2007-03-20 2014-05-06 Cochlear Limited Securing an implanted medical device in a patient
US9402990B2 (en) 2007-03-20 2016-08-02 Cochlear Limited Securing an implanted medical device in a patient
EP3024536A4 (fr) * 2013-07-26 2017-03-01 MED-EL Elektromedizinische Geräte GmbH Dispositif de support pour électrode d'implant cochléaire
WO2017040466A1 (fr) 2015-09-01 2017-03-09 Med-El Elektromedizinische Geraete Gmbh Raccord d'insertion d'électrode profonde chez des patients avec un implant cochléaire ayant une audition résiduelle
CN107661571A (zh) * 2017-05-19 2018-02-06 山东大学 多层结构柔性人工听觉神经刺激电极及制作方法

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JP4398728B2 (ja) 2001-10-24 2010-01-13 メド−エル・エレクトロメディツィニシェ・ゲラーテ・ゲーエムベーハー 埋込み式流体配送装置と埋込み式電極
CN110141782B (zh) * 2019-06-03 2024-05-14 浙江诺尔康神经电子科技股份有限公司 氧化石墨烯人工耳蜗电极及其制作方法

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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
US9119957B2 (en) 2002-06-28 2015-09-01 Cochlear Limited Cochlear implant system component having multiple electrode assemblies
US8630721B2 (en) 2002-06-28 2014-01-14 The University Of Iowa Hybrid cochlear implant
US8000798B2 (en) 2002-06-28 2011-08-16 Cochlear Limited Cochlear implant system substantially preserving the hydrodynamic nature of the cochlea
US8126564B2 (en) 2002-06-28 2012-02-28 The University Of Iowa Hybrid cochlear implant
US8150527B2 (en) 2004-04-02 2012-04-03 Advanced Bionics, Llc Electric and acoustic stimulation fitting systems and methods
US8155747B2 (en) 2004-04-02 2012-04-10 Advanced Bionics, Llc Electric and acoustic stimulation fitting systems and methods
US8244365B2 (en) 2004-05-10 2012-08-14 Cochlear Limited Simultaneous delivery of electrical and acoustical stimulation in a hearing prosthesis
US8086319B2 (en) 2004-05-10 2011-12-27 Cochlear Limited Cochlear implant fitting
US9402990B2 (en) 2007-03-20 2016-08-02 Cochlear Limited Securing an implanted medical device in a patient
US11426576B2 (en) 2007-03-20 2022-08-30 Cochlear Limited Securing an implanted medical device in a patient
US8718795B2 (en) 2007-03-20 2014-05-06 Cochlear Limited Securing an implanted medical device in a patient
AU2009295536B2 (en) * 2008-09-16 2012-11-22 Med-El Elektromedizinische Geraete Gmbh Double branch cochlear implant electrode
US8150528B2 (en) 2008-09-16 2012-04-03 Med-El Elektromedizinische Geraete Gmbh Double branch cochlear implant electrode
WO2010035149A3 (fr) * 2008-09-16 2010-06-17 Med-El Elektromedizinische Geraete Gmbh Electrode d’implant cochléaire à deux branches
EP3024536A4 (fr) * 2013-07-26 2017-03-01 MED-EL Elektromedizinische Geräte GmbH Dispositif de support pour électrode d'implant cochléaire
WO2017040466A1 (fr) 2015-09-01 2017-03-09 Med-El Elektromedizinische Geraete Gmbh Raccord d'insertion d'électrode profonde chez des patients avec un implant cochléaire ayant une audition résiduelle
CN107661571A (zh) * 2017-05-19 2018-02-06 山东大学 多层结构柔性人工听觉神经刺激电极及制作方法
CN107661571B (zh) * 2017-05-19 2024-01-30 山东大学 多层结构柔性听觉神经刺激电极阵列

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EP1185332A1 (fr) 2002-03-13
CA2371125A1 (fr) 2000-11-23
AU4846000A (en) 2000-12-05
EP1185332A4 (fr) 2008-12-24

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