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WO2017034530A1 - Implant cochléaire doté d'une retenue à aimant ancrée à des ancrages de retenue et procédé de fixation d'un aimant - Google Patents

Implant cochléaire doté d'une retenue à aimant ancrée à des ancrages de retenue et procédé de fixation d'un aimant Download PDF

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Publication number
WO2017034530A1
WO2017034530A1 PCT/US2015/046403 US2015046403W WO2017034530A1 WO 2017034530 A1 WO2017034530 A1 WO 2017034530A1 US 2015046403 W US2015046403 W US 2015046403W WO 2017034530 A1 WO2017034530 A1 WO 2017034530A1
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WO
WIPO (PCT)
Prior art keywords
magnet
restraint
cochlear implant
housing
anchors
Prior art date
Application number
PCT/US2015/046403
Other languages
English (en)
Inventor
Melissa PARIS
Uli Gommel
James George Elcoate SMITH
Original Assignee
Advanced Bionics Ag
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 Ag filed Critical Advanced Bionics Ag
Priority to PCT/US2015/046403 priority Critical patent/WO2017034530A1/fr
Publication of WO2017034530A1 publication Critical patent/WO2017034530A1/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
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/36036—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation of the outer, middle or inner ear
    • A61N1/36038—Cochlear stimulation

Definitions

  • the present disclosure relates generally to the implantable portion of implantable cochlear stimulation (or "ICS") systems.
  • ICS implantable cochlear stimulation
  • ICS systems are used to help the profoundly deaf perceive a sensation of sound by directly exciting the intact auditory nerve with controlled impulses of electrical current.
  • Ambient sound pressure waves are picked up by an externally worn microphone and converted to electrical signals.
  • the electrical signals are processed by a sound processor, converted to a pulse sequence having varying pulse widths and/or amplitudes, and transmitted to an implanted receiver circuit of the ICS system.
  • the implanted receiver circuit is connected to an implantable electrode array that has been inserted into the cochlea of the inner ear, and electrical stimulation current is applied to varying electrode combinations to create a perception of sound.
  • the electrode array may, alternatively, be directly inserted into the cochlear nerve without residing in the cochlea.
  • ICS sound processors include, but are not limited to, the Advanced BionicsTM HarmonyTM BTE sound processor, the Advanced BionicsTM NaidaTM BTE sound processor and the Advanced BionicsTM NeptuneTM body worn sound processor.
  • some ICS systems include an implantable cochlear stimulator (or "cochlear implant"), a sound processor unit (e.g., a body worn processor or behind-the-ear processor), and a microphone that is part of, or is in communication with, the sound processor unit.
  • the cochlear implant communicates with the sound processor unit and, some ICS systems include a headpiece that is in communication with both the sound processor unit and the cochlear implant.
  • the headpiece communicates with the cochlear implant by way of a transmitter (e.g., an antenna) on the headpiece and a receiver (e.g., an antenna) on the implant. Optimum communication is achieved when the transmitter and the receiver are aligned with one another.
  • the headpiece and the cochlear implant may include respective positioning magnets that are attracted to one another, and that maintain the position of the headpiece transmitter over the implant receiver.
  • the implant magnet may, for example, be located within a pocket in the cochlear implant housing.
  • the cochlear implant 10 includes a flexible housing 12 formed from a silicone elastomer or other suitable material, a processor assembly 14, a cochlear lead 16 with a flexible body 18 and an electrode array 20, and an antenna 22 that may be used to receive data and power by way of an external antenna that is associated with, for example, a sound processor unit.
  • the positioning magnet 24 is carried within an internal magnet pocket 26 and can be inserted into, and removed from, the housing pocket by way of a magnet aperture 28 that extends through the housing top wall 30.
  • the magnet 22 is larger than the magnet aperture 28, i.e., the outer diameter of the magnet is greater than the diameter of the magnet aperture.
  • the portion of the top wall 30 between the aperture 28 and the outer edge 32 of the magnet 24 forms a retainer 34 that, absent deformation of the aperture and retainer, prevents the magnet from coming out of the housing 12.
  • the aperture 28 and retainer 34 are stretched or otherwise deformed so that the magnet 24 can pass through the aperture 28.
  • the present inventors have determined that conventional cochlear implants are susceptible to improvement.
  • some conventional cochlear implants may not be compatible with magnetic resonance imaging ("MRI") systems.
  • MRI magnetic resonance imaging
  • the implant magnet 24 produces a magnetic field M in a direction that is perpendicular to the patient's skin and parallel to the axis A. This magnetic field direction is not aligned with, and may be perpendicular to (as shown), the direction of the MRI magnetic field B.
  • the misalignment of the interacting magnetic fields M and B is problematic for a number of reasons.
  • the dominant MRI magnetic field B (typically 1 .5 Tesla or more) may generate a significant amount of torque T on the implant magnet 24.
  • the torque T may be sufficient to deform the retainer 34 and dislodge the implant magnet 24 from the pocket 26 by way of the aperture 28 and/or reverse the magnet.
  • One proposed solution involves surgically removing the implant magnet 24 prior to an MRI procedure and then surgically replacing the implant magnet thereafter.
  • the present inventors have determined that a solution which allows an MRI procedure to be performed without magnet removal/replacement surgery, but which also permits magnet removal/replacement if otherwise necessary, would be desirable.
  • a cochlear implant in accordance with one of the present inventions includes a cochlear lead, a housing defining an exterior and including a magnet pocket and a magnet aperture, an antenna within the housing, a stimulation processor within the housing, and a plurality of restraint anchors on the housing.
  • the present inventions also include systems with such a cochlear implant in combination with a headpiece.
  • a method in accordance with one of the present inventions includes the step of securing a magnet within a cochlear implant housing that includes an exterior, a magnet pocket in which the magnet is located, and a magnet aperture that extends from the exterior to the magnet pocket, by anchoring a restraint to restraint anchors on the cochlear implant housing in such a manner that the restraint extends over the magnet aperture.
  • a cochlear implant in accordance with one of the present inventions includes a cochlear lead, a housing defining an exterior and including a magnet pocket and a magnet aperture, an antenna within the housing, a stimulation processor within the housing, and means for securing a restraint to the housing in such a manner that the restraint extends across the magnet aperture.
  • the present inventions also include systems with such a cochlear implant in combination with a headpiece.
  • the torque applied to the implant magnet by a strong magnetic field will not dislodge the implant magnet from the within the housing and/or reverse the magnet.
  • a strong magnetic field such as an MRI magnetic field
  • surgical removal of the cochlear implant magnet prior to an MRI procedure, and then surgical replacement thereafter is not required.
  • the restraints can be cut to permit magnet removal and later re-insertion, and the anchors facilitate replacement of the restraints.
  • FIG. 1 is a plan view of a conventional cochlear implant.
  • FIG. 2 is a section view taken along line 2-2 in FIG. 1 .
  • FIG. 3 is a side view showing a conventional cochlear implant in an MRI magnetic field.
  • FIG. 4 is a plan view of a cochlear implant in accordance with one embodiment of a present invention.
  • FIG. 5 is a perspective view of portion of the cochlear implant illustrated in FIG. 4.
  • FIG. 6 is a section view taken along line 6-6 in FIG. 5.
  • FIG. 7 is a section view similar to FIG. 6 with the magnet removed.
  • FIG. 8 is a plan view of a portion of the cochlear implant illustrated in FIGS. 4-7 with a pair of restraints secured thereto.
  • FIG. 9 is a plan view of a portion of the cochlear implant illustrated in
  • FIGS. 4-7 with a pair of restraints secured thereto.
  • FIG. 10 is a plan view of a portion of the cochlear implant illustrated in FIGS. 4-7 with a single restraint secured thereto.
  • FIG. 1 1 is a plan view of a portion of the cochlear implant illustrated in FIGS. 4-7 with a single restraint and a cover secured thereto.
  • FIG. 12 is a perspective view of a cochlear implant in accordance with one embodiment of a present invention.
  • FIG. 13 is a section view taken along line 13-13 in FIG. 12.
  • FIG. 14 is a plan view of a portion of the cochlear implant illustrated in FIGS. 12-13 with a pair of restraints secured thereto.
  • FIG. 15 is a perspective view of a cochlear implant in accordance with one embodiment of a present invention.
  • FIG. 16 is a section view taken along line 16-16 in FIG. 15.
  • FIG. 17 is a plan view of a portion of the cochlear implant illustrated in FIGS. 15-17 with three restraints secured thereto.
  • FIG. 18 is a block diagram of a cochlear implant system in accordance with one embodiment of a present invention.
  • the exemplary cochlear implant 100 includes a resilient flexible housing 102 formed from a silicone elastomer or other suitable material, a processor assembly 104, a cochlear lead 106, and an antenna 108 that may be used to receive data and power by way of an external antenna that is associated with, for example, a sound processor unit.
  • the cochlear lead 106 may include a flexible body 1 10, an electrode array 1 12 at one end of the flexible body 102, and a plurality of wires (not shown) that extend through the flexible body from the electrodes 1 14 (e.g., platinum electrodes) in the array 1 12 to the other end of the flexible body.
  • the exemplary antenna 108 is a coil antenna with one or more loops (or "turns"), and three loops are shown in the illustrated embodiment.
  • the exemplary processor assembly 104 which is connected to the electrode array 1 12 and antenna 108, includes a printed circuit board 1 16 with a stimulation processor 1 18 that is located within a hermetically sealed case 120.
  • the stimulation processor 1 18 converts stimulation data into stimulation signals that stimulate the electrodes 1 14 of the electrode array 1 12.
  • the hermetically sealed case 120 is located within a processor portion 122 of the housing 102.
  • a positioning magnet 124 is located within an antenna portion 126 housing 102. The magnet 124, which is used to maintain the position of a headpiece transmitter over the antenna 108, is centered relative to the antenna 108.
  • the exemplary housing antenna portion 126 includes a magnet pocket 128 which is surrounded by a bottom wall 130 that is located under the magnet pocket (in the illustrated orientation), a top wall 132 that is located above the magnet pocket (in the illustrated orientation) and a side wall 134 that is lateral of, and extends around, the magnet pocket.
  • the housing bottom wall 130 faces the patient's skull and the outer surface of the bottom wall defines a portion of the bottom surface of the cochlear implant 100, which is the surface of the cochlear implant that faces the patient's skull.
  • the magnet pocket 128 is disk-shaped in the illustrated implementation and, accordingly, the outer perimeter P P of the magnet pocket is circular.
  • the magnet 124 can be inserted into, and removed from, the magnet pocket 128 by way of a magnet aperture 136 that extends through the housing top wall 132.
  • the magnet 124 is larger than the magnet aperture 136, i.e., the outer diameter of the magnet is greater than the diameter of the magnet aperture, and the portion of the top wall 132 between the aperture 136 and the outer edge of the magnet forms a retainer 138.
  • the present implant housing 102 includes a plurality of anchors (or "restraint anchors") to which one or more magnet-holding restraints may be secured.
  • the first set of anchors which includes anchors 140a-140d, is associated with the retainer 138.
  • the anchors 140a-140d may simply be regions of the portion of the top wall 132 that forms the retainer 138 with apertures that extend through each region (as shown). So positioned, the anchors 140a-140d are located within the region of the top wall 132 that is defined by the outer perimeter P P of the magnet pocket 128 (i.e., extends outwardly to the same extent as the outer perimeter P P ) and are adjacent to the magnet aperture 136.
  • the apertures of the exemplary anchors 140a-140d extend from the top surface of the housing 102 to magnet pocket 128 (but not to the bottom surface of the implant 100).
  • the second set of anchors which includes anchors 142a-142d, is associated with the outer perimeter of the housing antenna portion 126.
  • the anchors 142b-142d are located on the housing outer perimeter P H
  • the anchor 142a is located within the outer perimeter P H .
  • the distance between the anchors 142a-142d and the center C of the magnet aperture 136 is greater than the distance between the anchors 140a-140d and the center C.
  • the exemplary anchors 142a-142d each include a base 144 that extends outwardly from the adjacent portion of the housing 102 (e.g., the side wall 134) and an aperture 146 that extends through the base.
  • the apertures 146 of the anchors 142b-142d extend to the bottom surface of the cochlear implant 100, which in the illustrated embodiment includes the bottom surface of the housing 102 and the bottom surfaces of the bases 144 of the anchors 142b-142d, while the aperture 146 of the anchor 142a does not extend to the bottom surface of the cochlear implant 100.
  • the anchors 140a-140d and 142a-142d may be used in conjunction with one or more flexible restraints in, for example, the manner described below with reference to FIGS. 8-1 1 .
  • the anchors in each set are arranged such that a flexible restraint can extend from one anchor to another across the magnet aperture 136.
  • the anchors perform the function of securing a restraint to the housing 102 in such a manner that the restraint extends across the magnet aperture 136.
  • pairs of anchors in each set are diametrically opposed, i.e. are offset from one another by 180° around the center C of the magnet aperture. A restraint associated with a pair of diametrically opposed anchors will pass over the center C of the magnet aperture 136.
  • Other anchor arrangements are discussed below.
  • the flexible restraints may be slender lengths of flexible material such as suture threads, slender chords and the like.
  • the thickness of the flexible restraints should be low enough that the flexible restraints do not substantially increase the distance between the implant magnet 124 and the headpiece magnet.
  • the thickness e.g., diameter where the cross-section is circular
  • Suitable materials include, but are not limited to, biocompatible materials such as nylon, polyester, polyvinylidene fluoride, and polypropylene.
  • the restraints will be secured to the cochlear implant 100 by way of the anchors 140a-140d and/or anchors 142a-142d prior to implantation.
  • the cochlear implant 100 is shown in conjunction with first and second restraints 148 and 150.
  • the restraints 148 and 150 are secured to the anchors 142a-142d, thereby securing the restraints to the housing 102, and simply pass over the anchors 140a-140d.
  • the restraints 148 and 150 pass through the aperture 146 (FIGS. 5-7) in each of the anchors 142a-142d.
  • a knot 152 is formed at the ends of each restraint 148 and 150 (only one visible in FIG. 8), and a short piece 154 of the restraint may extend from each knot.
  • the first and second restraints 148 and 150 may, alternatively, be only secured to the anchors 140a-140d.
  • the restraints 148 and 150 are anchored to (i.e., secured to) a portion of the cochlear implant 100 and not to tissue such as bone or fascia. It should also be noted that, because the width of the restraints 148 and 158 is far less than the size (e.g., diameter) of the magnet aperture 136, the restraints only cover a small portion of the magnet aperture as they pass over the center C. Turning to FIG. 9, the cochlear implant 100 is again shown in conjunction with the first and second restraints 148 and 150.
  • the restraints 148 and 150 pass through the anchors 140a-140d and are secured to the anchors 142a-142d.
  • the restraints 148 and 150 are secured to the anchors 142a-142d with knots 152 (only one visible in FIG. 9), and a short piece 154 of the restraint extends from each knot.
  • a single restraint may be secured to the cochlear implant housing 102.
  • the restraint 148 extends from anchor 140a to anchor 140c, then from anchor 140c to anchor 140d, and then from anchor 140d to anchor 140b.
  • the restraint 148 passes through anchors 140c and 140d and is secured to the anchors 140a and 140b with knots 152.
  • a single restraint may be employed in similar fashion in conjunction with anchors 142a-142d.
  • the present anchors may also be used to secure a cover 156 over the magnet aperture 136.
  • the restraint 148 is stitched through the cover 156 in addition to passing through the anchors 140a-140d and being secured to the anchors 140a and 140b in the manner described above with reference to FIG. 10.
  • the cover 156 may be formed from a flexible material such as a surgical cloth or an implantable mesh (as shown).
  • the anchors 140a-140d and 142a-142d perform the function of connecting one or more restraints to the housing 102 in a manner that prevents the magnet 124 from being partially or completely dislodged from the magnet pocket 128 through the aperture 136.
  • the torque generated by an MRI magnetic field will not dislodge the magnet 124 from the housing 102 and/or reverse the magnet within the housing in the manner described above with reference to FIGS. 1 -3.
  • the magnet 124 may be removed in situ by simply cutting the restraints 148 and 150 and then pulling the restraints out of the anchors (and the patient) in a manner similar to sutures.
  • the magnet 124 may also be replaced in situ, and then new restraints may be passed through and secured to the appropriate anchors using conventional suturing techniques.
  • One example of a device that may be used to remove the magnet 124 after the restraints have been cut and removed, and then to replace the magnet, is disclosed in PCT Pub. No. WO2014/164023.
  • the exemplary magnet 124 includes a magnetic disk 158 (FIG. 6) or magnetic object of some other shape formed from a ferromagnetic material and a thin hermetically sealed housing 160 formed from, for example, biocompatible metals and/or plastics.
  • housing materials may, in some instances, be non-magnetic or paramagnetic.
  • Suitable materials include, but are not limited to, titanium or titanium alloys, polyether ether ketone (PEEK), low-density polyethylene (LDPE), high-density polyethylene (HDPE) and polyamide.
  • exemplary metals include commercially pure titanium (e.g., Grade 2) and the titanium alloy Ti-6AI-4V (Grade 5).
  • the magnet 124 may have an overall size and shape similar to that of conventional cochlear implant magnets.
  • the diameter that may range from 9 mm to 16 mm and the thickness may range from 1 .5 mm to 3.0 mm.
  • the diameter of the magnet 124 is 10.5 mm, and the thickness is 2.2 mm, in the illustrated embodiment.
  • the dimensions of the magnet pocket 128 may be equal to those of the magnet 124.
  • the present anchor configurations are not limited to those illustrated in FIGS. 4-1 1 .
  • either the anchors 140a-140d may be omitted, or the anchors 142a-142d may be omitted.
  • the two sets of anchors may be rotated relative to one another about the center C (FIG. 5) of the magnet aperture 136 so that they are not aligned in the manner shown.
  • the anchors 140a-140d and 142a-142d need not be arranged in diametrically opposed pairs.
  • the number and configuration of the anchors may also be changed.
  • the retainer 138 may be thickened in some implementations.
  • the anchors, including those described below, may be integral with the housing 102 (as shown), may be reinforced, or may be separately manufactured structures that are secured to the housing.
  • the exemplary cochlear implant 100a illustrated in FIGS. 12-14 is substantially similar to cochlear implant 100 and similar elements are represented by similar reference numerals.
  • the cochlear implant 100a includes anchors 160a-160d in place of anchors 140a-140d.
  • the anchors 160a-160d each include a base 162 that extends outwardly from the adjacent portion of the housing 102 (e.g. the retainer 138) and an aperture 164 that extends through the base.
  • the apertures 164 extend in directions that are transverse to, and may be perpendicular to, the axis A that extends through the center C of the magnet aperture 136. Referring more specifically to FIG.
  • first and second restraints 148 and 150 may be secured to the housing 102 by way of the anchors 160a-160d.
  • a knot 152 is formed at each of the ends of each restraint 148 and 150, and a short piece 154 of the restraint may extend from each knot.
  • the anchors 160a-160d are more robust than the anchors 140a-140d, and may also be used (or not used) in conjunction with one or more restraints in, for example, the manner described above with reference to FIGS. 8-1 1 .
  • the exemplary cochlear implant 100b illustrated in FIGS. 15-17 is substantially similar to cochlear implant 100a and similar elements are represented by similar reference numerals.
  • the cochlear implant 100b includes a set of six anchors on the retainer 138, i.e., anchors 160a-160f.
  • first, second and third restraints 148, 150 and 151 may be employed in conjunction with the cochlear implant 100b and secured to the housing 102 by way of the anchors 142a-142d and 160a-160f.
  • the restraints 148 and 150 are secured to the anchors 142a-142d in the manner described above with reference to FIG. 8.
  • the restraint 151 extends from anchor 160e to anchor 160b, then from anchor 160b to anchor 160a, then from anchor 160a to anchor 160d, then from anchor 160d to anchor 160c, and then from anchor 160c to anchor 160f.
  • Knots 152 are formed at anchors 160e and 160f.
  • the restraint 148 passes through anchors 140c and 140d and is secured to the anchors 140a and 140b with knots 152. As a result, restraints 150 and 151 both pass through anchors 160c and 160f.
  • the exemplary cochlear implant system 50 includes the cochlear implant 100 (or one of the other cochlear implants 100a and 100b described above), a sound processor, such as the illustrated body worn sound processor 200 or a behind-the-ear sound processor, and a headpiece 300.
  • the exemplary body worn sound processor 200 in the exemplary ICS system 50 includes a housing 202 in which and/or on which various components are supported. Such components may include, but are not limited to, sound processor circuitry 204, a headpiece port 206, an auxiliary device port 208 for an auxiliary device such as a mobile phone or a music player, a control panel 210, one or microphones 212, and a power supply receptacle 214 for a removable battery or other removable power supply 216 (e.g., rechargeable and disposable batteries or other electrochemical cells).
  • the sound processor circuitry 204 converts electrical signals from the microphone 212 into stimulation data.
  • the exemplary headpiece 300 includes a housing 302 and various components, e.g., a RF connector 304, a microphone 306, an antenna (or other transmitter) 308 and a positioning magnet apparatus 310, that are carried by the housing.
  • the magnet apparatus 310 may consist of a single magnet or may consist of one or more magnets and a shim.
  • the headpiece 300 may be connected to the sound processor headpiece port 206 by a cable 312.
  • the positioning magnet apparatus 310 is attracted to the magnet 124 of the cochlear stimulator 100, thereby aligning the antenna 308 with the antenna 108.
  • the stimulation data and, in many instances power, is supplied to the headpiece 300.
  • the headpiece 300 transcutaneously transmits the stimulation data, and in many instances power, to the cochlear implant 100 by way of a wireless link between the antennas.
  • the stimulation processor 1 18 converts the stimulation data into stimulation signals that stimulate the electrodes 1 14 of the electrode array 1 12.
  • the cable 312 will be configured for forward telemetry and power signals at 49 MHz and back telemetry signals at 10.7 MHz. It should be noted that, in other implementations, communication between a sound processor and a headpiece and/or auxiliary device may be accomplished through wireless communication techniques. Additionally, given the presence of the microphone(s) 212 on the sound processor 200, the microphone 306 may be also be omitted in some instances. The functionality of the sound processor 200 and headpiece 300 may also be combined into a single head wearable sound processor. Examples of head wearable sound processors are illustrated and described in U.S. Patent Nos. 8,81 1 ,643 and 8,983,102, which are incorporated herein by reference in their entirety.

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

Abstract

La présente invention concerne un implant cochléaire (100) qui comprend un fil cochléaire, un boîtier (102) comprenant une poche d'aimant et une ouverture (136) d'aimant, une antenne à l'intérieur du boîtier et adjacente à la poche d'aimant, un processeur de stimulation et une pluralité d'ancrages de retenue (140a-140d, 142a-142d) sur le boîtier.
PCT/US2015/046403 2015-08-21 2015-08-21 Implant cochléaire doté d'une retenue à aimant ancrée à des ancrages de retenue et procédé de fixation d'un aimant WO2017034530A1 (fr)

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PCT/US2015/046403 WO2017034530A1 (fr) 2015-08-21 2015-08-21 Implant cochléaire doté d'une retenue à aimant ancrée à des ancrages de retenue et procédé de fixation d'un aimant

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PCT/US2015/046403 WO2017034530A1 (fr) 2015-08-21 2015-08-21 Implant cochléaire doté d'une retenue à aimant ancrée à des ancrages de retenue et procédé de fixation d'un aimant

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US9919154B2 (en) 2015-12-18 2018-03-20 Advanced Bionics Ag Cochlear implants having MRI-compatible magnet apparatus and associated methods
WO2018190813A1 (fr) * 2017-04-11 2018-10-18 Advanced Bionics Ag Implants cochléaires avec aimants rapportés
US10300276B2 (en) 2015-05-28 2019-05-28 Advanced Bionics Ag Cochlear implants having MRI-compatible magnet apparatus and associated methods
US10532209B2 (en) 2015-12-18 2020-01-14 Advanced Bionics Ag Cochlear implants having MRI-compatible magnet apparatus and associated methods
US10646712B2 (en) 2017-09-13 2020-05-12 Advanced Bionics Ag Cochlear implants having MRI-compatible magnet apparatus
US10646718B2 (en) 2016-11-15 2020-05-12 Advanced Bionics Ag Cochlear implants and magnets for use with same
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US10806936B2 (en) 2015-11-20 2020-10-20 Advanced Bionics Ag Cochlear implants and magnets for use with same
US11287495B2 (en) 2017-05-22 2022-03-29 Advanced Bionics Ag Methods and apparatus for use with cochlear implants having magnet apparatus with magnetic material particles
US11364384B2 (en) 2017-04-25 2022-06-21 Advanced Bionics Ag Cochlear implants having impact resistant MRI-compatible magnet apparatus
US11638823B2 (en) 2018-02-15 2023-05-02 Advanced Bionics Ag Headpieces and implantable cochlear stimulation systems including the same
US12053629B2 (en) 2020-09-09 2024-08-06 Med-El Elektromedizinische Geraete Gmbh Holding magnets and magnet system for implantable systems optimized for MRI

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US20140343626A1 (en) * 2011-09-22 2014-11-20 Advanced Bionics Ag Retention of a magnet in a cochlear implant

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US5290281A (en) * 1992-06-15 1994-03-01 Medicon Eg Surgical system
WO2003092326A1 (fr) * 2002-04-23 2003-11-06 Cochlear Limited Implant cochleaire compatible irm
US20090287278A1 (en) * 2008-05-15 2009-11-19 Neurelec Implantable subcutaneous device
US20140343626A1 (en) * 2011-09-22 2014-11-20 Advanced Bionics Ag Retention of a magnet in a cochlear implant

Cited By (21)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US10300276B2 (en) 2015-05-28 2019-05-28 Advanced Bionics Ag Cochlear implants having MRI-compatible magnet apparatus and associated methods
US10806936B2 (en) 2015-11-20 2020-10-20 Advanced Bionics Ag Cochlear implants and magnets for use with same
US10821279B2 (en) 2015-12-18 2020-11-03 Advanced Bionics Ag Cochlear implants having MRI-compatible magnet apparatus and associated methods
US9919154B2 (en) 2015-12-18 2018-03-20 Advanced Bionics Ag Cochlear implants having MRI-compatible magnet apparatus and associated methods
US10463849B2 (en) 2015-12-18 2019-11-05 Advanced Bionics Ag MRI-compatible magnet apparatus and associated methods
US10532209B2 (en) 2015-12-18 2020-01-14 Advanced Bionics Ag Cochlear implants having MRI-compatible magnet apparatus and associated methods
US11986656B2 (en) 2015-12-18 2024-05-21 Advanced Bionics Ag Cochlear implants having MRI-compatible magnet apparatus and associated methods
US11476025B2 (en) 2015-12-18 2022-10-18 Advanced Bionics Ag MRI-compatible magnet apparatus
US10646718B2 (en) 2016-11-15 2020-05-12 Advanced Bionics Ag Cochlear implants and magnets for use with same
WO2018190813A1 (fr) * 2017-04-11 2018-10-18 Advanced Bionics Ag Implants cochléaires avec aimants rapportés
US11097095B2 (en) 2017-04-11 2021-08-24 Advanced Bionics Ag Cochlear implants, magnets for use with same and magnet retrofit methods
WO2018191314A1 (fr) * 2017-04-11 2018-10-18 Advanced Bionics Ag Implants cochléaires avec aimants rapportés
US11779754B2 (en) 2017-04-11 2023-10-10 Advanced Bionics Ag Cochlear implants, magnets for use with same and magnet retrofit methods
US11364384B2 (en) 2017-04-25 2022-06-21 Advanced Bionics Ag Cochlear implants having impact resistant MRI-compatible magnet apparatus
US11752338B2 (en) 2017-04-25 2023-09-12 Advanced Bionics Ag Cochlear implants having impact resistant MRI-compatible magnet apparatus
US11287495B2 (en) 2017-05-22 2022-03-29 Advanced Bionics Ag Methods and apparatus for use with cochlear implants having magnet apparatus with magnetic material particles
US10646712B2 (en) 2017-09-13 2020-05-12 Advanced Bionics Ag Cochlear implants having MRI-compatible magnet apparatus
CN111344041A (zh) * 2017-10-26 2020-06-26 领先仿生公司 头戴件和包括其的可植入耳蜗刺激系统
US11471679B2 (en) 2017-10-26 2022-10-18 Advanced Bionics Ag Headpieces and implantable cochlear stimulation systems including the same
US11638823B2 (en) 2018-02-15 2023-05-02 Advanced Bionics Ag Headpieces and implantable cochlear stimulation systems including the same
US12053629B2 (en) 2020-09-09 2024-08-06 Med-El Elektromedizinische Geraete Gmbh Holding magnets and magnet system for implantable systems optimized for MRI

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