WO2007090655A1 - Électrode cochléaire - Google Patents

Électrode cochléaire Download PDF

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Publication number
WO2007090655A1
WO2007090655A1 PCT/EP2007/001094 EP2007001094W WO2007090655A1 WO 2007090655 A1 WO2007090655 A1 WO 2007090655A1 EP 2007001094 W EP2007001094 W EP 2007001094W WO 2007090655 A1 WO2007090655 A1 WO 2007090655A1
Authority
WO
WIPO (PCT)
Prior art keywords
electrode
electrodes
carrier
electrode carrier
arrangement
Prior art date
Application number
PCT/EP2007/001094
Other languages
German (de)
English (en)
Inventor
Hans Wilhelm Pau
Detlef Behrend
Wolfram Schmidt
Katrin Sternberg
Klaus-Peter Schmitz
Original Assignee
Zyrus Beteiligungsgesellschaft Mbh & Co. Patente I Kg
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 Zyrus Beteiligungsgesellschaft Mbh & Co. Patente I Kg filed Critical Zyrus Beteiligungsgesellschaft Mbh & Co. Patente I Kg
Publication of WO2007090655A1 publication Critical patent/WO2007090655A1/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
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/67—Implantable hearing aids or parts thereof not covered by H04R25/606

Definitions

  • the present invention relates to a cochlea electrode assembly comprising an electrode carrier having a plurality of leads and a plurality of electrodes, the electrodes being spaced along the length of the electrode carrier, and each of the electrodes having an associated lead in the electrode carrier electrically connected.
  • the cochlea is part of the inner ear and consists of three superimposed channels, which are helically rolled up, namely the Scala tympani, the Scala media and the Scala vestibuli.
  • the Scala tympani and Scala vestibuli are filled with perilymph with high Na + concentration ( ⁇ 140 mmol / l), while the Scala media is filled with endolymph with high K + concentration ( ⁇ 145 mmol / l).
  • Between the Scala tympani and Scala media lies the basilar membrane, on which there is a thickening, namely the organ of Corti.
  • the outer and inner hair cells in whose membrane voltage-dependent channels are embedded. Each inner hair cell is followed by about 20 afferent neurons.
  • the neurons are bundled in the auditory nerve and pull themselves up to the brain stem, where they form their synapses in the nucleus cochlearis.
  • the stapes in the middle ear swings back and forth and thus transmits the sound to the perilymph of the Scala vestibuli.
  • the inner ear fluid is incompressible, so that the membrane of the round window, which is located between the middle ear and the Scala tympani, oscillates out of phase with the stapes to balance the volume.
  • This causes the basal region of the basilar membrane to be moved up and down in a sound-synchronous manner, which in turn propagates along the basilar membrane Wave triggers.
  • the structural rigidity of the Basil arm crane decreases from the stapes to the helicotrema, the propagation velocity of the wave towards the helicotrema becomes ever smaller.
  • the amplitudes become larger and larger. It comes at a certain point on the basilar membrane to an amplitude maximum, which is located at a different location for each frequency. Due to the mechanical properties of the basilar membrane there is thus a frequency-dependent stimulus generation. The stimulus is transmitted via the basilar membrane to the inner hair cells and from there to the auditory nerve, from where the stimulus is passed on to the brain for further processing.
  • Deafness or deafness can have different causes. You can u.a. caused by the fact that the hair cells are no longer functional. However, it is often the case that the auditory nerve is still intact, so that a sound perception can be caused by a targeted electrical stimulation of the nerve fibers in the inner abdominal snail.
  • cochlear electrode arrangements are usually introduced into the scala tympani of the cochlea and from there stimulate the nerve cells originally assigned to the inner hair cells.
  • the hearing nerve is electrically stimulated in the event of severe or complete hearing loss, bypassing the entire mechanical sound conduction.
  • a CI system includes, on the one hand, an implantable receiver, the cochlear stimulator, and the so-called cochlear electrode assembly, which has a plurality of electrodes.
  • the CI system includes a microphone, a voice processor, a transmitter and a battery unit. The energy required for operation is transferred to the receiver the integrated receiving antenna from the battery unit of the processor.
  • the speech processor which is usually worn behind the ear, calculates, by means of integrated software, from the acoustic signal picked up by the microphone, the electrical impulses which are transmitted to the auditory nerve with the aid of the electrode arrangement.
  • a stimulation electrode assembly is introduced into the cochlea, with the aid of which electrical signals generated from the acoustic signals are transmitted to the auditory nerve.
  • a stimulation electrode assembly is introduced into the cochlea, with the aid of which electrical signals generated from the acoustic signals are transmitted to the auditory nerve.
  • an electrode arrangement for a CI system is known, which is designed to strain relief of the cochlea, which facilitates the bending of the electrode when it is inserted into the cochlea.
  • this electrode arrangement it is possible that the latter shifts in the inner ear and thus no continuously good electrical signal transmission between the electrodes mounted on the carrier arrangement and the basilar membrane can be ensured.
  • EP 1 604 626 A2 also discloses a cochlear reshaped electrode carrier having a U-shaped lumen surrounded by a coating by which the carrier is held in a straight shape.
  • the layer dissolves into the cochlea after insertion of the electrode carrier, resulting in relaxation of the preformed electrode carrier so that it assumes a corrugated shape.
  • the disadvantage is that the electrode carrier is under tension, so that it can cause injury in the inner ear area in premature dissolution of the coating.
  • the insulation of the wires, which in the U-shaped lumen, without an additional layer can be easily damaged by in the inner ear administered Pharmakaaten.
  • WO 03/072193 discloses a similar to EP 1 604 626 A2, preformed for inclusion in the cochlea electrode carrier.
  • a stiffening wire is additionally embedded, which serves as an insertion aid. After the implant has been placed in the inner ear, the stiffening wire can be removed and the remaining channel used as a lead for pharmaceutical solutions.
  • the electrode carrier and thus also the electrodes can easily slip in the Scala tympani or can, so that no reliable contact between the electrodes and basilar membrane is ensured.
  • the electrode carrier is configured helically.
  • helical is understood here to mean that the course is at least partially such that it at least partially encloses a volume whose cross-sectional area is perpendicular to the direction of extent of the Carrier runs.
  • the course can be helical, wherein the enclosed volume can then have a rounded, for example circular or oval cross-sectional area.
  • deviating cross-sectional shapes are also conceivable.
  • the course of the electrode carrier can be helical, that is, with a circular cross-section of the enclosed volume, wherein sections with different orientation (clockwise and counterclockwise) can follow one another.
  • the term "helical" should be understood to mean that the electrode carrier has sections which run parallel to the direction of extension of the carrier and those which run perpendicularly or at least at an angle to the direction of extension. In this case, sections of different orientation follow each other, so that would result in a projection of the course of the carrier on a plane meandering course. Even with such a configuration, however, a volume is enclosed by the carrier.
  • the helical configuration allows good contact between the electrodes and the cochlea, since the electrode carrier is pressed by the helical shape to the cochlear walls and fixes the electrode assembly in this way in the cochlea. This ensures a permanently stable position of the electrode arrangement in the cochlea, which increases the number of electrodes in which there is an electrical contact with hair cells. However, the electrode assembly can still be removed from the cochlea, if necessary. This leads to a significantly improved signal transmission and thus to many different pitches perceivable by the patient, since the increased number of electrodes allows different areas of the basilar arm membrane to be electrically contacted.
  • the electrical designed as ring electrodes which extend annularly around the electrode carrier. This is particularly advantageous because they do not have to pay attention to the alignment of the electrodes for making contact between the hair cells and the electrodes.
  • Another preferred embodiment of the arrangement according to the invention uses half-ring electrodes. With proper positioning of the half-ring electrodes, they satisfy the same conditions as the aforementioned ring electrodes, but have the additional advantage of having a small area that can corrode. Corrosion or contamination, such as Protein adsorption of the electrodes is undesirable because it results in a deterioration of the electrical contact, resulting in an impedance increase due to the formation of connective tissue around the implant.
  • a tip electrode is preferably located in the distal region of the electrode carrier, which is guided farthest into the cochlea in the implanted state. As a result, an additional contact between the electrodes can be produced, and the electrode carrier shows a better insertion behavior.
  • the tip electrode is more preferably made of tungsten, platinum or platinum-iridium.
  • the electrode carrier which has a plurality of lines, is preferably made of electrically insulating material, so that adjacent electrodes do not influence.
  • the electrode carrier is preferably formed of silicone. Silicone is extremely flexible, kink-resistant and resistant to aging. Another preferred material of the electrode carrier is polyurethane, usually polyetherurethane (PUR). PUR is also used because of its excellent mechanical and chemical resistance. The silicone or PUR is Lichgue applied only after the formation of the helical electrode carrier. But it is also possible to first coat the electrode carrier and then deform.
  • the electrode assembly comprises a plurality of helical sections, wherein the sections may be spaced apart.
  • the electrode carrier has portions of lower rigidity, so that the electrode carrier has greater flexibility and can better adapt to the course of the cochlea.
  • the electrodes are preferably arranged at equal intervals in the direction of extension of the electrode carrier. As a result, there is a constant contact between the electrodes and the hair cells on the basilar membrane.
  • the electrodes are offset by 90 ° along the extension direction of the electrode carrier. This increases the likelihood that the electrodes on the helical electrode will make contact with the basilar membrane and thus the stimulating neurons and not with the opposite outer surface of the cochlea, where there are no neurons of the auditory nerve that could relay an electrical signal.
  • the electrodes are arranged offset by 180 ° to one another along the extension direction of the electrode carrier, which likewise leads to an increased contact probability between electrodes and basilar membrane.
  • the outer diameter of the cross-sectional area of the helical arrangement is between 0.5 and 1.2 mm, in order to be adapted to the Scala tympani or Scala vestibuli.
  • the electrode carrier is further preferably coated to prevent corrosion or contamination, for example by protein adsorption, of the lines inside the electrode carrier and of the electrodes, and to bring about favorable properties of the electrode carrier in relation to its surroundings. This includes, for example, that the electrode carrier is inert to biological material.
  • the electrode carrier is tubular, wherein the lines run in the interior of the electrode carrier.
  • the electrode carrier is coated on its surface with a hydrophilic material to be easily movable in the perilymph, the hydrophilic coating resulting in good lubricity.
  • a cuff or cuff which serves as a seal and / or additionally as a depot for pharmaceutical solutions, such. Can serve antibiotics.
  • the cuff is preferably displaceable in order to introduce the electrode arrangement individually differently far into the cochlea.
  • This sleeve preferably comprises microfiber material, preferably of polyethylene terephthalate (PET), and in a preferred embodiment contains silver threads which have an antibacterial effect.
  • microfiber sleeves are particularly suitable because they have a high binding capacity for pharmaceutical solutions, suspensions and powders.
  • the microfibers are configured as a circular knit or needle felt.
  • the electrode arrangement can have feed channels which run in the direction of extension of the arrangement. These are accessible from the proximal end of the electrode carrier and can serve to deliver drug solutions into the inner ear area.
  • the feed channels may be formed as grooves in the outer surface of the electrode carrier or as running in the interior of the electrode carrier tubular channels.
  • the electrodes of the electrode arrangement according to the invention are preferably designed as a wire mesh.
  • This wire mesh further preferably comprises wire of platinum or platinum-iridium. But there are also other materials, such as Gold or tungsten conceivable.
  • Wire mesh is highly flexible and has a larger surface area compared to continuous ring electrodes. It is also possible in the interdental spaces pasty masses, for example pharmaceutical compounds, e.g. a composition of polymers and pharmaceuticals, e.g. by means of doctor blade technology.
  • FIG. 1 is a perspective view of a first embodiment of a Cochleaelek- trodenan angel invention
  • FIG. 2 is a perspective view of a second embodiment
  • 3 shows the first and second embodiments in each case together with a guide wire
  • Fig. 4 is a perspective view of a portion of an embodiment of an electrode assembly with a ring electrode and
  • Fig. 5 is a perspective view of a portion of an embodiment of an electrode assembly with a sleeve.
  • a first embodiment of a cochlea electrode assembly 1 is shown with a flexible electrode carrier 3 having a plurality of lines 5, and having a plurality of electrodes 7, wherein the electrodes 7 are arranged along the length of the electrode carrier 3 spaced from each other. Further, each of the electrodes 7 is electrically connected to an associated line 5 in the electrode carrier 3. In the extension direction 11 is located in the end region of the electrode carrier 3, a tip electrode 12th
  • the electrode carrier 3 is made of electrically insulating material.
  • silicone and / or polyetherurethane (PUR) are suitable, since both materials are easy to apply, flexible and resistant.
  • the electrode carrier 3 is helically configured, wherein the electrode carrier 3 in this preferred embodiment, helical sections 9 which are spaced apart, so that the electrode carrier 3 is sufficiently flexible to adapt to the course of the cochlea.
  • the helical shape of the electrode carrier 3 causes a sufficiently high longitudinal stiffness of the electrode carrier 3, so that it can be fixed in the scala tympani of the cochlea without it slipping.
  • Helical in the sense of the present invention is understood to mean that the course is at least partially such that it at least partially encloses a volume whose cross-sectional area is perpendicular to the Extension direction 11 of the carrier 3 extends.
  • the course can be helical, wherein the enclosed volume can then have a round, for example circular, or oval cross-sectional area.
  • deviating cross-sectional shapes are also conceivable.
  • the course of the electrode carrier 3 as shown in Fig. 1 be helical, so with a circular cross-section of the enclosed volume, wherein sections with different orientation (clockwise and counterclockwise) can follow one another.
  • the electrodes 7 and the tip electrode 12 are arranged at approximately equal intervals in the extension direction 11 of the electrode carrier 3 so that the electrodes 7 and the tip electrode 12 make contact with the auditory nerve as evenly as possible via the basilar membrane. This is important to be able to transfer different pitches to the auditory nerve.
  • adjacent electrodes 7 are offset by 90 ° from each other, at least a quarter of the electrodes 7 with the basilar membrane contact. It is also conceivable that the electrodes 7 are arranged offset by 180 ° to each other. This arrangement also ensures that a large part of the electrodes 7 has contact with the basilar membrane and thus with the auditory nerve.
  • the outer diameter 13 of the enclosed by the electrode carrier 3 cross-sectional area of the helical arrangement 1 is preferably 0.5 to 1.2 mm. However, the size of the cross-sectional area of the electrode assembly 1 to be inserted into the cochlea can be tailored to the individual patient.
  • the helical section has first sections 15 that run parallel to the extension direction 11 of the electrode arrangement 1'.
  • second portions 15 ' are present, which run perpendicular or at least at an angle to the extension direction 11.
  • sections 15, 15 'of different orientation follow each other alternately, so that a meandering course would result in a projection of the profile of the carrier on a plane.
  • a volume is enclosed by the electrode carrier 3.
  • the electrodes 7 are further arranged offset by 180 ° to each other, so that a large proportion of the electrodes 7 has contact with the basilar membrane.
  • the electrode carrier 3 has in both embodiments, a tubular configuration, wherein the lines 5 extend in its interior. It is possible to coat the surface of the cochlea electrode assembly 1 with hydrophilic material in order to achieve good lubricity of the electrode assembly 1 in the cochlea with the coating. However, it is also conceivable that the configuration of the electrode carrier 3 is not tubular, but has only a guiding function for the lines 5 running in it.
  • Fig. 3 shows the first and second embodiment 1, 1 'of Fig. 1 and 2, each with a guide wire 17.
  • the guide wire 17 serves as an insertion instrument. It also represents the volume enclosed by the electrode carrier 3.
  • FIG. 4 shows a section of the embodiment of cochlear electrode arrangements 1, 1 'on which an electrode 7 is located.
  • This electrode 7 is designed here as a ring electrode 19. Ring electrodes 19 are advantageous because each electrode 7 can stimulate the largest possible area of the Basilarmebran and the electrode assembly 1 must not be brought in the introduction in a precisely predetermined position.
  • the electrodes 7 are formed as half-ring electrodes, so that the dirty and corrodible surface of the electrodes 7 is kept small in comparison to the ring electrodes 19.
  • the ring electrodes 19 and the tip electrode 12 are constructed in a preferred embodiment of a wire mesh 21, which preferably consists of platinum or platinum-iridium wire and with an associated, extending in the electrode support 3 line 5 is electrically connected.
  • the tubular wire mesh is highly flexible and has a larger surface area compared to continuous ring electrodes. It is also possible in the inter-mesh areas pasty masses, for example, pharmaceutical compounds or pharmaceutical polymer compounds, for example by means of doctor blade technology to bring. Platinum or platinum-iridium has been found to be beneficial because it is biocompatible and chemically inert. But other materials are conceivable as long as they meet the same requirements. Fig.
  • FIG. 5 shows a portion of an electrode carrier 3 according to the invention, which has a sleeve 23 at the proximal end of the electrode carrier 3, which is arranged in the implanted state at the passage point of the carrier 3 in the vicinity of the oval window.
  • the sleeve 23 is constructed of microfibers.
  • the cuff 23 made of microfibers may be affected by silver threads which prevent an ascending infection.
  • other materials for the cuff 23 or other materials for antibacterial components are conceivable as long as they ensure biocompatibility.
  • the cuff 23 serves as a seal and / or additionally as a depot for anti-inflammatories or antibiotics.
  • the sleeve 23 may further have a cavity in its interior which may serve as a reservoir for pharmaceutical solutions.
  • supply channels may be provided in the electrode carrier 3.
  • the feed channels may be formed as grooves in the outer surface of the electrode carrier 3 or as in the interior of the electrode carrier 3 parallel to the lines 5 extending tubular channels. Through the delivery channels, the pharmaceutical solutions can reach the deeper area of the cochlea.

Abstract

L'invention concerne une système à électrode cochléaire comportant un porte-électrodes flexible présentant une pluralité de conducteurs, et une pluralité d'électrodes. Les électrodes sont espacées sur la longueur du porte-électrodes. Dans le porte-électrodes, chaque électrode est électriquement reliée à un conducteur qui lui est associée. L'invention vise à proposer un système d'électrodes chocléaire garantissant un bon contact mécanique entre le porte-électrodes, et donc les électrodes, et l'oreille interne ou la membrane basilaire. A cet effet, le porte-électrodes a une forme hélicoïdale.
PCT/EP2007/001094 2006-02-10 2007-02-08 Électrode cochléaire WO2007090655A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE102006006263.9 2006-02-10
DE102006006263A DE102006006263B3 (de) 2006-02-10 2006-02-10 Cochleaelektrode

Publications (1)

Publication Number Publication Date
WO2007090655A1 true WO2007090655A1 (fr) 2007-08-16

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Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/EP2007/001094 WO2007090655A1 (fr) 2006-02-10 2007-02-08 Électrode cochléaire

Country Status (2)

Country Link
DE (1) DE102006006263B3 (fr)
WO (1) WO2007090655A1 (fr)

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2008031144A1 (fr) * 2006-09-12 2008-03-20 Cochlear Limited Réseau d'électrodes implantable
WO2012154179A1 (fr) * 2011-05-11 2012-11-15 Advanced Bionics Ag Réseau d'électrodes à échelle moyenne
EP2665440B1 (fr) * 2011-01-20 2020-03-11 Acandis GmbH Prothèse auditive

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP4015033A1 (fr) * 2020-12-21 2022-06-22 INBRAIN Neuroelectronics SL Support d'électrode souple

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US4819647A (en) * 1984-05-03 1989-04-11 The Regents Of The University Of California Intracochlear electrode array
US4832051A (en) * 1985-04-29 1989-05-23 Symbion, Inc. Multiple-electrode intracochlear device
WO2001012115A1 (fr) * 1999-08-18 2001-02-22 Epic Biosonics Inc. Reseau d'electrodes epousant la columelle
WO2003024153A1 (fr) * 2001-09-13 2003-03-20 Med-El Elektromedizinische Geräte Ges.m.b.H. Electrode intracochleaire a segment hydrophile partiellement detachable pour positionnement dynamique differe
WO2003072193A1 (fr) * 2002-02-28 2003-09-04 Cochlear Limited Raccord pour systeme de distribution de medicament dans un implant cochleaire
US20040122501A1 (en) * 2000-10-04 2004-06-24 Fysh Dadd Cochlear implant electrode array
US20040127968A1 (en) * 2002-09-19 2004-07-01 Kuzma Janusz A. Cochlear implant electrode and method of making same
US20050033377A1 (en) * 2001-11-09 2005-02-10 Dusan Milojevic Subthreshold stimulation of a cochlea
EP1543863A1 (fr) * 2003-12-19 2005-06-22 W.C. Heraeus GmbH Structure d'életrode, procédés de sa fabrication et son utilisation
EP1604626A2 (fr) * 1999-05-21 2005-12-14 Cochlear Limited Réseau d'électrodes pour implant cochléaire

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CH657984A5 (de) * 1979-09-24 1986-10-15 Ingeborg Johanna Hochmair Deso Anordnung zur elektrischen stimulation eines rezeptors, empfangseinheit fuer die anordnung, uebertragereinheit fuer die anordnung und verfahren zur herstellung derselben.
US5800500A (en) * 1995-08-18 1998-09-01 Pi Medical Corporation Cochlear implant with shape memory material and method for implanting the same
US20030236562A1 (en) * 2000-10-10 2003-12-25 Kuzma Janusz A. Band type multicontact electrode and method of making the same
US6757970B1 (en) * 2000-11-07 2004-07-06 Advanced Bionics Corporation Method of making multi-contact electrode array
AU2002952146A0 (en) * 2002-10-17 2002-10-31 Cochlear Limited Stretchable conducting lead
AU2003900773A0 (en) * 2003-02-21 2003-03-13 Cochlear Limited Telescopic array for a cochlear implant

Patent Citations (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4819647A (en) * 1984-05-03 1989-04-11 The Regents Of The University Of California Intracochlear electrode array
US4832051A (en) * 1985-04-29 1989-05-23 Symbion, Inc. Multiple-electrode intracochlear device
EP1604626A2 (fr) * 1999-05-21 2005-12-14 Cochlear Limited Réseau d'électrodes pour implant cochléaire
WO2001012115A1 (fr) * 1999-08-18 2001-02-22 Epic Biosonics Inc. Reseau d'electrodes epousant la columelle
US20040122501A1 (en) * 2000-10-04 2004-06-24 Fysh Dadd Cochlear implant electrode array
WO2003024153A1 (fr) * 2001-09-13 2003-03-20 Med-El Elektromedizinische Geräte Ges.m.b.H. Electrode intracochleaire a segment hydrophile partiellement detachable pour positionnement dynamique differe
US20050033377A1 (en) * 2001-11-09 2005-02-10 Dusan Milojevic Subthreshold stimulation of a cochlea
WO2003072193A1 (fr) * 2002-02-28 2003-09-04 Cochlear Limited Raccord pour systeme de distribution de medicament dans un implant cochleaire
US20040127968A1 (en) * 2002-09-19 2004-07-01 Kuzma Janusz A. Cochlear implant electrode and method of making same
EP1543863A1 (fr) * 2003-12-19 2005-06-22 W.C. Heraeus GmbH Structure d'életrode, procédés de sa fabrication et son utilisation

Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2008031144A1 (fr) * 2006-09-12 2008-03-20 Cochlear Limited Réseau d'électrodes implantable
EP2665440B1 (fr) * 2011-01-20 2020-03-11 Acandis GmbH Prothèse auditive
WO2012154179A1 (fr) * 2011-05-11 2012-11-15 Advanced Bionics Ag Réseau d'électrodes à échelle moyenne
US9415207B2 (en) 2011-05-11 2016-08-16 Advanced Bionics Ag Mid-scalar electrode array
US10016589B2 (en) 2011-05-11 2018-07-10 Advanced Bionics Ag Mid-scalar electrode array

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