[go: up one dir, main page]

WO2025233734A1 - Ensemble implantable à membrane souple - Google Patents

Ensemble implantable à membrane souple

Info

Publication number
WO2025233734A1
WO2025233734A1 PCT/IB2025/054266 IB2025054266W WO2025233734A1 WO 2025233734 A1 WO2025233734 A1 WO 2025233734A1 IB 2025054266 W IB2025054266 W IB 2025054266W WO 2025233734 A1 WO2025233734 A1 WO 2025233734A1
Authority
WO
WIPO (PCT)
Prior art keywords
feedthrough
perimeter portion
chassis
membrane
outer perimeter
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Pending
Application number
PCT/IB2025/054266
Other languages
English (en)
Inventor
Peter Schuller
Anne OTIENO
Oleg POZOVSKY
Benjamin Stewart
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Cochlear Ltd
Original Assignee
Cochlear Ltd
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 Cochlear Ltd filed Critical Cochlear Ltd
Publication of WO2025233734A1 publication Critical patent/WO2025233734A1/fr
Pending legal-status Critical Current
Anticipated expiration legal-status Critical

Links

Classifications

    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
    • H04R25/604—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers
    • H04R25/606—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers acting directly on the eardrum, the ossicles or the skull, e.g. mastoid, tooth, maxillary or mandibular bone, or mechanically stimulating the cochlea, e.g. at the oval window
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B81—MICROSTRUCTURAL TECHNOLOGY
    • B81B—MICROSTRUCTURAL DEVICES OR SYSTEMS, e.g. MICROMECHANICAL DEVICES
    • B81B7/00—Microstructural systems; Auxiliary parts of microstructural devices or systems
    • B81B7/02—Microstructural systems; Auxiliary parts of microstructural devices or systems containing distinct electrical or optical devices of particular relevance for their function, e.g. microelectro-mechanical systems [MEMS]
    • 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 application relates generally to implantable devices for stimulation and/or measurement of a recipient’s body and the housings and/or feedthroughs of such devices.
  • Medical devices have provided a wide range of therapeutic benefits to recipients over recent decades.
  • Medical devices can include internal or implantable components/devices, external or wearable components/devices, or combinations thereof (e.g., a device having an external component communicating with an implantable component).
  • Medical devices such as traditional hearing aids, partially or fully-implantable hearing prostheses (e.g., bone conduction devices, mechanical stimulators, cochlear implants, etc.), pacemakers, defibrillators, functional electrical stimulation devices, and other medical devices, have been successful in performing lifesaving and/or lifestyle enhancement functions and/or recipient monitoring for a number of years.
  • implantable medical devices now often include one or more instruments, apparatus, sensors, processors, controllers or other functional mechanical or electrical components that are permanently or temporarily implanted in a recipient. These functional devices are typically used to diagnose, prevent, monitor, treat, or manage a disease/injury or symptom thereof, or to investigate, replace or modify the anatomy or a physiological process. Many of these functional devices utilize power and/or data received from external devices that are part of, or operate in conjunction with, implantable components.
  • an apparatus comprises a chassis, a feedthrough, and a membrane having an outer perimeter portion affixed to the chassis and an inner perimeter portion affixed to the feedthrough.
  • the membrane is configured to flex in response to a first force applied to the chassis and/or a second force applied to the feedthrough.
  • a method comprises applying an impulse to an implanted device comprising a housing, a connector, and at least one flexure having a first portion affixed to the housing and a second portion affixed to the connector.
  • the impulse generates a differential force between the housing and the connector.
  • the method further comprises dampening the differential force by deforming the at least one flexure.
  • an apparatus comprises a chassis, a feedthrough, and a deformable support having a substantially planar outer perimeter portion bonded to the chassis and an inner perimeter portion bonded to the feedthrough.
  • a first region bounded by the chassis, feedthrough, and support is hermetically sealed from a second region outside the chassis, feedthrough, and support.
  • the support comprises a plurality of bends such that one or more portions of the support between the outer perimeter portion and the inner perimeter portion are out-of-plane relative to the outer perimeter portion.
  • FIG. 1A is a perspective view of an example cochlear implant auditory prosthesis implanted in a recipient in accordance with certain implementations described herein;
  • FIG. IB is a perspective view of an example fully implantable middle ear implant auditory prosthesis implanted in a recipient in accordance with certain implementations described herein;
  • FIG. 2A schematically illustrates a plan view of an example apparatus in accordance with certain implementations described herein;
  • FIGs. 2B-2E schematically illustrate cross-sectional views of portions of various example apparatus in accordance with certain implementations described herein;
  • FIG. 3 is a flow diagram of an example method in accordance with certain implementations described herein.
  • Certain implementations described herein provide an implant chassis having a preformed, flexible membrane bonded to a feedthrough and to a wall of the chassis to support the feedthrough.
  • the membrane can comprise a thin sheet of material with a plurality of out-of-plane bends configured to deform (e.g., flex) such that the feedthrough can move or “float” relative to the chassis and the transfer of impact forces from the chassis to the feedthrough are reduced (e.g., minimized).
  • implantable stimulation or measurement system e.g., implantable auditory prosthesis device or system; neurostimulation system; machine-brain interface system; muscle stimulation system.
  • the system e.g., implantable sensor prostheses; implantable stimulation system; implantable medicament administration system
  • the system can be configured to provide a portion of the recipient’s body with stimulation signals and/or medicament dosages from an implanted portion of the system in response to received information and/or control signals from an external portion of the system.
  • the system e.g., implantable sensing system
  • Implementations can include any type of medical device that can utilize the teachings detailed herein and/or variations thereof. Furthermore, while certain implementations are described herein in the context of auditory prosthesis devices, certain other implementations are compatible in the context of other types of devices or systems that provide a wide range of therapeutic benefits to recipients, patients, or other users.
  • an implantable transducer assembly including but not limited to: electro-acoustic electrical/acoustic systems, cochlear implant devices, implantable hearing aid devices, middle ear implant devices, bone conduction devices (e.g., active bone conduction devices; passive bone conduction devices, percutaneous bone conduction devices; transcutaneous bone conduction devices), Direct Acoustic Cochlear Implant (DACI), middle ear transducer (MET), electro-acoustic implant devices, other types of auditory prosthesis devices, and/or combinations or variations thereof, or any other suitable hearing prosthesis system with or without one or more external components.
  • DACI Direct Acoustic Cochlear Implant
  • MET middle ear transducer
  • electro-acoustic implant devices other types of auditory prosthesis devices, and/or combinations or variations thereof, or any other suitable hearing prosthesis system with or without one or more external components.
  • Implementations can include any type of auditory prosthesis that can utilize the teachings detailed herein and/or variations thereof. Certain such implementations can be referred to as “partially implantable,” “semi-implantable,” “mostly implantable,” “fully implantable,” or “totally implantable” auditory prostheses. In some implementations, the teachings detailed herein and/or variations thereof can be utilized in other types of prostheses beyond auditory prostheses.
  • vestibular devices e.g., vestibular implants
  • tinnitus treatment devices e.g., tinnitus treatment devices
  • visual devices e.g., bionic eyes
  • visual prostheses e.g., retinal implants
  • neurostimulators e.g., brain implants, somatosensory implants, and chemosensory implants.
  • Certain other implementations are compatible with other types of medical devices that can utilize the teachings detailed herein and/or variations thereof to provide a wide range of therapeutic benefits to recipients, patients, or other users (e.g., epilepsy monitoring or treatment systems; pain control systems; bladder control systems; sleep apnea control systems; neurostimulators; cardiac pacemakers; drug delivery systems; defibrillators; functional electrical stimulation devices; electroporation devices), to perform monitoring or measuring functionalities (e.g., sensors; electroencephalogram monitoring of brain function; electrocardiogram monitoring of heart function), seizure devices (e.g., devices for monitoring and/or treating epileptic events); swallowing treatment devices (e.g., devices for treating difficulties with the hyoglossus and/or thyrohyoid muscles); dysphagia treatment devices; devices for treating dry mouth (e.g., xerostomia or hyposalivation), devices for treating excessive or absence of muscle movement due to stroke, Parkinson’s disease, or other brain disorders, devices for treating hyper
  • FIG. 1A is a perspective view of an example cochlear implant auditory prosthesis 100 implanted in a recipient in accordance with certain implementations described herein.
  • the example auditory prosthesis 100 is shown in FIG. 1 A as comprising an implanted stimulator unit 120 and a microphone assembly 124 that is external to the recipient (e.g., a partially implantable cochlear implant).
  • An example auditory prosthesis 100 e.g., a totally implantable cochlear implant; a mostly implantable cochlear implant
  • the example cochlear implant auditory prosthesis 100 of FIG. 1 A can be in conjunction with a reservoir of liquid medicament as described herein.
  • the recipient has an outer ear 101, a middle ear 105, and an inner ear 107.
  • the outer ear 101 comprises an auricle 110 and an ear canal 102.
  • An acoustic pressure or sound wave 103 is collected by the auricle 110 and is channeled into and through the ear canal 102.
  • a tympanic membrane 104 Disposed across the distal end of the ear canal 102 is a tympanic membrane 104 which vibrates in response to the sound wave 103.
  • This vibration is coupled to oval window or fenestra ovalis 112 through three bones of middle ear 105, collectively referred to as the ossicles 106 and comprising the malleus 108, the incus 109, and the stapes 111.
  • the bones 108, 109, and 111 of the middle ear 105 serve to filter and amplify the sound wave 103, causing the oval window 112 to articulate, or vibrate in response to vibration of the tympanic membrane 104.
  • This vibration sets up waves of fluid motion of the perilymph within cochlea 140.
  • Such fluid motion activates tiny hair cells (not shown) inside the cochlea 140. Activation of the hair cells causes appropriate nerve impulses to be generated and transferred through the spiral ganglion cells (not shown) and auditory nerve 114 to the brain (also not shown) where they are perceived as sound.
  • the example auditory prosthesis 100 comprises one or more components which are temporarily or permanently implanted in the recipient.
  • the example auditory prosthesis 100 is shown in FIG. 1A with an external component 142 which is directly or indirectly attached to the recipient’s body, and an internal component 144 which is temporarily or permanently implanted in the recipient (e.g., positioned in a recess of the temporal bone adjacent auricle 110 of the recipient).
  • the external component 142 typically comprises one or more sound input elements (e.g., an external microphone 124) for detecting sound, a sound processing unit 126 (e.g., disposed in a Behind- The-Ear unit), a power source (not shown), and an external transmitter unit 128.
  • the external transmitter unit 128 comprises an external coil 130 (e.g., a wire antenna coil comprising multiple turns of electrically insulated single-strand or multi-strand platinum or gold wire) and, preferably, a magnet (not shown) secured directly or indirectly to the external coil 130.
  • the external coil 130 of the external transmitter unit 128 is part of an inductive radio frequency (RF) communication link with the internal component 144.
  • the sound processing unit 126 processes the output of the microphone 124 that is positioned externally to the recipient’s body, in the depicted implementation, by the recipient’s auricle 110.
  • the sound processing unit 126 processes the output of the microphone 124 and generates encoded signals, sometimes referred to herein as encoded data signals, which are provided to the external transmitter unit 128 (e.g., via a cable).
  • the sound processing unit 126 can utilize digital processing techniques to provide frequency shaping, amplification, compression, and other signal conditioning, including conditioning based on recipient-specific fitting parameters.
  • the power source of the external component 142 is configured to provide power to the auditory prosthesis 100, where the auditory prosthesis 100 includes a battery (e.g., located in the internal component 144, or disposed in a separate implanted location) that is recharged by the power provided from the external component 142 (e.g., via a transcutaneous energy transfer link).
  • the transcutaneous energy transfer link is used to transfer power and/or data to the internal component 144 of the auditory prosthesis 100.
  • Various types of energy transfer such as infrared (IR), electromagnetic, capacitive, and inductive transfer, may be used to transfer the power and/or data from the external component 142 to the internal component 144.
  • the internal component 144 comprises an internal receiver unit 132, a stimulator unit 120, and an elongate electrode assembly 118.
  • the internal receiver unit 132 and the stimulator unit 120 are hermetically sealed within a biocompatible housing.
  • the internal receiver unit 132 comprises an internal coil 136 (e.g., a wire antenna coil comprising multiple turns of electrically insulated single-strand or multistrand platinum or gold wire), and preferably, a magnet (also not shown) fixed relative to the internal coil 136.
  • the internal receiver unit 132 and the stimulator unit 120 are hermetically sealed within a biocompatible housing, sometimes collectively referred to as a stimulator/receiver unit.
  • the internal coil 136 receives power and/or data signals from the external coil 130 via a transcutaneous energy transfer link (e.g., an inductive RF link).
  • the stimulator unit 120 generates electrical stimulation signals based on the data signals, and the stimulation signals are delivered to the recipient via the elongate electrode assembly 118.
  • the elongate electrode assembly 118 has a proximal end connected to the stimulator unit 120, and a distal end implanted in the cochlea 140.
  • the electrode assembly 118 extends from the stimulator unit 120 to the cochlea 140 through the mastoid bone 119.
  • the electrode assembly 118 may be implanted at least in the basal region 116, and sometimes further.
  • the electrode assembly 118 may extend towards apical end of cochlea 140, referred to as cochlea apex 134.
  • the electrode assembly 118 may be inserted into the cochlea 140 via a cochleostomy 122.
  • a cochleostomy may be formed through the round window 121, the oval window 112, the promontory 123, or through an apical turn 147 of the cochlea 140.
  • the elongate electrode assembly 118 comprises a longitudinally aligned and distally extending array 146 of contacts or electrodes 148, sometimes referred to as electrode or contact array 146 herein, disposed along a length thereof.
  • the electrode array 146 can be disposed on the electrode assembly 118, in most practical applications, the electrode array 146 is integrated into the electrode assembly 118 (e.g., the electrode array 146 is disposed in the electrode assembly 118).
  • the stimulator unit 120 generates stimulation signals which are applied by the electrodes 148 to the cochlea 140, thereby stimulating the auditory nerve 114.
  • FIG. 1A schematically illustrates an auditory prosthesis 100 utilizing an external component 142 comprising an external microphone 124, an external sound processing unit 126, and an external power source
  • one or more of the microphone 124, sound processing unit 126, and power source are implantable on or within the recipient (e.g., within the internal component 144).
  • the auditory prosthesis 100 can have each of the microphone 124, sound processing unit 126, and power source implantable on or within the recipient (e.g., encapsulated within a biocompatible assembly located subcutaneously), and can be referred to as a totally implantable cochlear implant (“HQ”).
  • HQ totally implantable cochlear implant
  • the auditory prosthesis 100 can have most components of the cochlear implant (e.g., excluding the microphone, which can be an in-the-ear-canal microphone) implantable on or within the recipient, and can be referred to as a mostly implantable cochlear implant (“MIQ”).
  • MIQ implantable cochlear implant
  • FIG. IB schematically illustrates a perspective view of an example fully implantable auditory prosthesis 200 (e.g., fully implantable middle ear implant or totally implantable acoustic system), implanted in a recipient, utilizing an acoustic actuator in accordance with certain implementations described herein.
  • IB comprises a biocompatible implantable assembly 202 (e.g., comprising an implantable capsule) located subcutaneously (e.g., beneath the recipient’s skin and on a recipient's skull). While FIG. IB schematically illustrates an example implantable assembly 202 comprising a microphone, in other example auditory prostheses 200, a pendant microphone can be used (e.g., connected to the implantable assembly 202 by a cable).
  • a biocompatible implantable assembly 202 e.g., comprising an implantable capsule located subcutaneously (e.g., beneath the recipient’s skin and on a recipient's skull).
  • FIG. IB schematically illustrates an example implantable assembly 202 comprising a microphone
  • a pendant microphone can be used (e.g., connected to the implantable assembly 202 by a cable).
  • the implantable assembly 202 includes a signal receiver 204 (e.g., comprising a coil element) and an acoustic transducer 206 (e.g., a microphone comprising a diaphragm and an electret or piezoelectric transducer) that is positioned to receive acoustic signals through the recipient’s overlying tissue.
  • the implantable assembly 202 may further be utilized to house a number of components of the fully implantable auditory prosthesis 200.
  • the implantable assembly 202 can include an energy storage device and a signal processor (e.g., a sound processing unit).
  • Various additional processing logic and/or circuitry components can also be included in the implantable assembly 202 as a matter of design choice.
  • the signal processor of the implantable assembly 202 is in operative communication (e.g., electrically interconnected via a wire 208) with an actuator 210 (e.g., comprising a transducer configured to generate mechanical vibrations in response to electrical signals from the signal processor).
  • the example auditory prosthesis 100, 200 shown in FIGs. 1A and IB can comprise an implantable microphone assembly, such as the microphone assembly 206 shown in FIG. IB.
  • the signal processor of the implantable assembly 202 can be in operative communication (e.g., electrically interconnected via a wire) with the microphone assembly 206 and the stimulator unit 120 of the main implantable component.
  • at least one of the microphone assembly 206 and the signal processor e.g., a sound processing unit
  • the actuator 210 of the example auditory prosthesis 200 shown in FIG. IB is supportably connected to a positioning system 212, which in turn, is connected to a bone anchor 214 mounted in the recipient's mastoid bone (e.g., via a hole drilled through the skull).
  • the actuator 210 includes a connection apparatus 216 for connecting the actuator 210 to the ossicles 106 of the recipient. In a connected state, the connection apparatus 216 provides a communication path for acoustic stimulation of the ossicles 106 (e.g., through transmission of vibrations from the actuator 210 to the incus 109).
  • ambient acoustic signals e.g., ambient sound
  • a signal processor within the implantable assembly 202 processes the signals to provide a processed audio drive signal via wire 208 to the actuator 210.
  • the signal processor may utilize digital processing techniques to provide frequency shaping, amplification, compression, and other signal conditioning, including conditioning based on recipient-specific fitting parameters.
  • the audio drive signal causes the actuator 210 to transmit vibrations at acoustic frequencies to the connection apparatus 216 to affect the desired sound sensation via mechanical stimulation of the incus 109 of the recipient.
  • the subcutaneously implantable microphone assembly 202 is configured to respond to auditory signals (e.g., sound; pressure variations in an audible frequency range) by generating output signals (e.g., electrical signals; optical signals; electromagnetic signals) indicative of the auditory signals received by the microphone assembly 202, and these output signals are used by the auditory prosthesis 100, 200 to generate stimulation signals which are provided to the recipient’s auditory system.
  • auditory signals e.g., sound; pressure variations in an audible frequency range
  • output signals e.g., electrical signals; optical signals; electromagnetic signals
  • the diaphragm of an implantable microphone assembly 202 can be configured to provide higher sensitivity than are external non-implantable microphone assemblies.
  • the diaphragm of an implantable microphone assembly 202 can be configured to be more robust and/or larger than diaphragms for external non-implantable microphone assemblies.
  • the example auditory prostheses 100 shown in FIG. 1 A utilizes an external microphone 124 and the auditory prosthesis 200 shown in FIG. IB utilizes an implantable microphone assembly 206 comprising a subcutaneously implantable acoustic transducer.
  • the auditory prosthesis 100 utilizes one or more implanted microphone assemblies on or within the recipient.
  • the auditory prosthesis 200 utilizes one or more microphone assemblies that are positioned external to the recipient and/or that are implanted on or within the recipient, and utilizes one or more acoustic transducers (e.g., actuator 210) that are implanted on or within the recipient.
  • an external microphone assembly can be used to supplement an implantable microphone assembly of the auditory prosthesis 100, 200.
  • teachings detailed herein and/or variations thereof can be utilized with any type of external or implantable microphone arrangement, and the acoustic transducers shown in FIGs. 1 A and IB are merely illustrative.
  • FIG. 2A schematically illustrates a plan view of an example apparatus 300 in accordance with certain implementations described herein.
  • FIGs. 2B-2E schematically illustrate cross-sectional views of portions of various example apparatus 300 in accordance with certain implementations described herein.
  • the apparatus 300 comprises a chassis 310 (e.g., housing; casing; can), a feedthrough 320 (e.g., connector; electrical connector; optical connector; fluidic connector), and a membrane 330 (e.g., contoured sheet; support).
  • the membrane 330 has an outer perimeter portion 332 affixed to the chassis 310 and an inner perimeter portion 334 affixed to the feedthrough 320.
  • the membrane 330 is configured to flex in response to a first force Fj applied to the chassis 310 and/or a second force F2 applied to the feedthrough 320 (e.g., a differential force F between the chassis 310 and the feedthrough 320, the differential force F equal to the absolute value of the difference ⁇ Fi - F2I between the first force Fi and the second force F2).
  • a first force Fj applied to the chassis 310 and/or a second force F2 applied to the feedthrough 320 e.g., a differential force F between the chassis 310 and the feedthrough 320, the differential force F equal to the absolute value of the difference ⁇ Fi - F2I between the first force Fi and the second force F2.
  • each of the chassis 310 and the feedthrough 320 can comprise at least one biocompatible material (e.g., titanium; titanium alloy; plastic; ceramic; glass) configured to contact tissue and/or fluid of the recipient’s body.
  • biocompatible material e.g., titanium; titanium alloy; plastic; ceramic; glass
  • the chassis 310, the feedthrough 320, and the membrane 330 hermetically seal a first region 340 within the apparatus 300 from a second region 342 surrounding the apparatus 300.
  • the first region 340 can be configured to contain one or more transducers (e.g., acoustic transducers; mechanical - electrical transducers; microphone assembly 124, 202; actuator 210) and electronic circuitry (e.g., electronic circuit elements, including but not limited to one or more microprocessors, electrical insulation, electrical shielding; stimulation electronics; sound processing electronics) in operable communication with the feedthrough 320.
  • transducers e.g., acoustic transducers; mechanical - electrical transducers; microphone assembly 124, 202; actuator 2
  • electronic circuitry e.g., electronic circuit elements, including but not limited to one or more microprocessors, electrical insulation, electrical shielding; stimulation electronics; sound processing electronics
  • the chassis 310 can comprise a plurality of walls 312 at least partially bounding the first region 340 and that are substantially impenetrable to air and/or fluids from the second region 342.
  • the plurality of walls 312 can comprise a biocompatible material (e.g., metal; stainless steel; titanium; titanium-based alloy; cobalt-based alloy; magnesium-based alloy; tantalum-based alloy; non-metal; plastic; polymer; ceramic) or a non-biocompatible material coated with a biocompatible material.
  • the plurality of walls 312 can be unitary (e.g., integral; monolithic) with one another with the plurality of walls 312 defining a periphery of the first region 340, or can have joint seams between at the edges of adjoined walls.
  • the feedthrough 320 and the membrane 330 can also be substantially impenetrable to air and/or fluids from the second region 342.
  • the apparatus 300 comprises an implantable portion of an auditory prosthesis (e.g., auditory prosthesis 100, 200; cochlear implant auditory prosthesis; middle ear auditory prosthesis; bone conduction auditory prosthesis) used by the recipient.
  • the apparatus 300 can comprise an acoustic transducer (e.g., external microphone; subcutaneously implantable microphone; microphone assembly 124) configured to detect acoustic vibrations and/or pressure changes from the second region 342 outside the apparatus 300 and to convert the detected vibrations and/or pressure changes into electrical signals.
  • the apparatus 300 can comprise an implantable actuator (e.g., actuator 210) configured to be mechanically coupled to a portion of the recipient’s auditory system, to detect acoustic vibrations and/or pressure changes from at least a partially functional portion of the recipient’s auditory system (e.g., middle ear structures and/or cavities; inner ear structures and/or cavities) and to convert the detected vibrations and/or pressure changes into electrical signals.
  • Circuitry within the apparatus 300 can be configured to receive the electrical signals from the acoustic transducer and/or the actuator (e.g., via the feedthrough 320) and to generate stimulation signals (e.g., acoustical vibrations; electrical stimulation signals) in response to the received electrical signals.
  • stimulation signals e.g., acoustical vibrations; electrical stimulation signals
  • the apparatus 300 can be configured to provide the electrical stimulation signals to the recipient’s body via the feedthrough 320.
  • FIG. 2A schematically illustrates an example chassis 310 that has a substantially parallelepiped shape (e.g., rectangular cuboid; rhombohedron)
  • the chassis 310 can have any shape, including but not limited to: tubular; non-tubular; cylindrical; non- cylindrical; disc-shaped; geometric cross-sectional shapes (e.g., circular; elliptical; rectangular; square; polygonal); irregular cross-sectional shapes.
  • FIG. 2A schematically illustrates an example chassis 310 that has a substantially parallelepiped shape (e.g., rectangular cuboid; rhombohedron)
  • the chassis 310 can have any shape, including but not limited to: tubular; non-tubular; cylindrical; non- cylindrical; disc-shaped; geometric cross-sectional shapes (e.g., circular; elliptical; rectangular; square; polygonal); irregular cross-section
  • FIG. 2A schematically illustrates the example chassis 310 as having a plurality of substantially planar walls 312, in certain other implementations, one or more of the walls 312 can be non-planar (e.g., curved; bowed; concave; convex; bent; angled) and/or can have one or more protrusions or recesses. While FIG. 2A schematically illustrates the example chassis 310 having corners (e.g., 90 degrees) at edges of adjoined wall portions, in certain other implementations, the chassis 310 has a smooth contour (e.g., no corner) at the edges of adjoined wall portions.
  • a smooth contour e.g., no corner
  • the feedthrough 320 comprises a body 322, at least one conduit 324 extending through the body 322, and a flange 326 (e.g., metallic portion) bonded to and extending around the body 322.
  • the flange 326 is affixed to the inner perimeter portion of the membrane 330, and the at least one conduit 324 extends from the first region 340 to the second region 342.
  • the feedthrough 320 can be an electrical feedthrough in which the body 322 comprises an electrically insulative portion and the at least one conduit 324 comprises at least one electrical conductor 324 (e.g., wire; rod) extending through the electrically insulative portion from the first region 340 to the second region 342 and configured to transmit electrical signals between the first region 340 and the second region 342.
  • the feedthrough 320 can be an optical feedthrough in which the body 322 comprises an optically opaque portion and the at least one conduit 324 comprises at least one optically transparent conduit (e.g., optical fiber; optical rod) extending through the optically opaque portion from the first region 340 to the second region 342 and configured to transmit optical signals between the first region 340 and the second region 342.
  • the feedthrough 320 can be a fluidic (e.g., hydraulic; pneumatic) feedthrough in which the body 322 comprises a portion impermeable to at least one fluid and the at least one conduit 324 comprises at least one portion (e.g., tube; hole) permeable to the at least one fluid, extending through the impermeable portion from the first region 340 to the second region 342, and configured to transmit the at least one fluid between the first region 340 and the second region 342 (e.g., a medicament from the first region 340 to the second region 342; a body fluid sample from the second region 342 to the first region 340).
  • a fluidic e.g., hydraulic; pneumatic
  • the at least one conduit 324 comprises at least one portion (e.g., tube; hole) permeable to the at least one fluid, extending through the impermeable portion from the first region 340 to the second region 342, and configured to transmit the at least one fluid between the first region 340 and the second region 342 (e.g
  • FIG. 2A schematically illustrates an example feedthrough 320 that has a substantially circular outer perimeter
  • the outer perimeter of the feedthrough 320 can have any shape, including but not limited to: oval; elliptical; rectangular; square; polygonal; symmetric; asymmetric; geometric; irregular.
  • FIG. 2A schematically illustrates the example feedthrough 320 as being substantially planar
  • the feedthrough 320 e.g., the body 322 and/or the flange 326) can be non-planar (e.g., curved; bowed; concave; convex; bent; angled) and/or can have one or more protrusions or recesses.
  • FIG. 1 schematically illustrates an example feedthrough 320 that has a substantially circular outer perimeter
  • the outer perimeter of the feedthrough 320 can have any shape, including but not limited to: oval; elliptical; rectangular; square; polygonal; symmetric; asymmetric; geometric; irregular.
  • FIG. 2A schematically illustrates the example feedthrough
  • the at least one conduit 324 can have any shape, including but not limited to, cylindrical with other cross-sectional shapes (e.g., oval; elliptical; rectangular; square; polygonal); non-cylindrical. While FIG. 2A schematically illustrates the example at least one conduit 324 comprising four conduits 324, in certain other implementations, the at least one conduit 324 can comprise 1, 2, 3, 5, 6 or more conduits 324. While FIG. 2A schematically illustrates the example conduits 324 arranged to be substantially equidistant from one another, in certain other implementations, different pairs of the conduits 324 can have different distances between the two conduits 324 of the pair.
  • the membrane 330 comprises a sheet of biocompatible material (e.g., metal; stainless steel; titanium; titanium-based alloy; cobaltbased alloy; magnesium-based alloy; tantalum-based alloy; non-metal; plastic; polymer) or a sheet of material coated with a biocompatible material.
  • a biocompatible material e.g., metal; stainless steel; titanium; titanium-based alloy; cobaltbased alloy; magnesium-based alloy; tantalum-based alloy; non-metal; plastic; polymer
  • the membrane 330 can be affixed to a first wall 312a of the chassis 310 (e.g., welded; laser welded; soldered; brazed; held by adhesive; crimped; bonded) and affixed to the flange 326 of the feedthrough 320 (e.g., welded; laser welded; soldered; brazed; held by adhesive; crimped; bonded).
  • the membrane 330 can comprise the same material as does the flange 326 of the feedthrough 320 and/or the same material as does the first wall 312a of the chassis 310 (e.g., to avoid galvanic corrosion), or the membrane 330 can comprise a different material than does the flange 326 and/or the first wall 312a.
  • the outer perimeter portion 332 of the membrane 330 can be affixed to an outer surface of the first wall 312a (e.g., a surface facing the second region 342 outside the apparatus 300; see, e.g., FIGs. 2B-2E), to an inner surface of the first wall 312a (e.g., a surface facing the first region 340 within the apparatus 300), and/or a side surface within an orifice extending through the first wall 312a.
  • the inner perimeter portion 334 of the membrane 330 can be affixed to an outer surface of the flange 326 (e.g., a surface facing the second region 342 outside the apparatus 300; see, e.g., FIGs.
  • the feedthrough 320 can be substantially coplanar with the first wall 312a (see, e.g., FIGs. 2B-2E), while in certain other implementations, the feedthrough 320 is substantially above or below the first wall 312a.
  • the membrane 330 is contoured (e.g., preformed) and/or has a thickness such that the membrane 330 is more flexible than either the first wall 312a of the chassis 310 or the body 322 of the feedthrough 320.
  • the membrane 330 can have a sheet thickness that is less than a wall thickness of the first wall 312a of the chassis 310.
  • the sheet thickness of the membrane 330 can be in a range less than 150 microns (e.g., in a range of 10 microns to 100 microns; in a range of 50 microns to 100 microns) and the first wall 312a can have a wall thickness in a range greater than or equal to 150 microns.
  • the membrane 330 can comprise titanium with a sheet thickness in a range of 50 microns to 100 microns and can be affixed to the first wall 312a of the chassis 310, the first wall 312a comprising titanium with a wall thickness greater than 150 microns. While the membrane 330 of FIGs. 2B-2E has a substantially uniform thickness across the area of the membrane 330, in certain other implementations, the membrane 330 has a non-uniform thickness between the outer perimeter portion 332 and the inner perimeter portion 334.
  • the membrane 330 comprises one or more angled and/or curved portions 336 (e.g., at least one flexure) configured to flex (e.g., elastically deform) in response to the first force and/or the second force such that the feedthrough 320 moves in at least one direction relative to the chassis 310.
  • the one or more angled and/or curved portions 336 can be between the outer perimeter portion 332 and the inner perimeter portion 334. For example, as shown in FIGs.
  • the outer perimeter portion 332 can be substantially planar and bonded to the first wall 312a of the chassis 310
  • the inner perimeter portion 334 can be substantially planar and bonded to the flange 326 of the feedthrough 320
  • the one or more angled and/or curved portions 336 can extend from the outer perimeter portion 332 to the inner perimeter portion 334.
  • the membrane 330 is substantially symmetric (e.g., circularly symmetric about an axis at a center of the membrane 330 and extending in a direction substantially perpendicular to the membrane 330; see, e.g., FIG. 2A), while in certain other implementations, the membrane 330 is asymmetric (e.g., having different contours in different radial directions substantially parallel to the membrane 330).
  • the one or more angled and/or curved portions 336 have a single corrugation (e.g., local extremum) between the outer perimeter portion 332 and the inner perimeter portion 334, the corrugation extending in a direction substantially perpendicular to the outer perimeter portion 332 (e.g., substantially perpendicular to the first wall 312a).
  • corrugation e.g., local extremum
  • the one or more angled and/or curved portions 336 have multiple corrugations (e.g., local extrema) between the outer perimeter portion 332 and the inner perimeter portion 334, the corrugations extending in a direction substantially perpendicular to the outer perimeter portion 332 (e.g., substantially perpendicular to the first wall 312a).
  • the one or more angled and/or curved portions 336 comprise multiple angles which give the membrane 330 a cross-sectional shape in a plane substantially perpendicular to the outer perimeter portion 332 (e.g., substantially perpendicular to the first wall 312a) that is monotonic between the outer perimeter portion 332 and the inner perimeter portion 334.
  • FIG. 2D the one or more angled and/or curved portions 336 have multiple corrugations (e.g., local extrema) between the outer perimeter portion 332 and the inner perimeter portion 334, the corrugations extending in a direction substantially perpendicular to the outer perimeter portion 332 (e.g., substantially perpendicular
  • the one or more angled and/or curved portions 336 have multiple corrugations (e.g., local extrema) between the outer perimeter portion 332 and the inner perimeter portion 334, the corrugations extending in a direction substantially parallel to the outer perimeter portion 332 (e.g., substantially parallel to the first wall 312a).
  • the membrane 330 allows the feedthrough 320 to move relative to the chassis 310 in at least one direction in which the differential force AF has a non-zero component.
  • the membrane 330 can allow the feedthrough 320 to move relative to the chassis 310 in a first direction substantially parallel to the outer perimeter portion 332 (e.g., substantially parallel to the first wall 312a) in response to a non-zero differential force component AF between the chassis 310 and the feedthrough 320 in the first direction and/or to move relative to the chassis 310 in a second direction substantially perpendicular to the outer perimeter portion 332 (e.g., substantially perpendicular to the first wall 312a) in response to a non- zero differential force component AF between the chassis 310 and the feedthrough 320 in the second direction.
  • FIG. 3 is a flow diagram of an example method 400 in accordance with certain implementations described herein. While the example method 400 is described herein by referring to the example apparatus 300 of FIGs. 2A-2E, other apparatuses are also compatible with the example method 400 in accordance with certain implementations described herein.
  • the method 400 comprises applying an impulse (e.g., force applied over a time period) to an implanted device (e.g., apparatus 300; implanted portion of an auditory prosthesis system) comprising a housing (e.g., chassis 310), a connector (e.g., electrical connector; optical connector; fluidic connector; feedthrough 320), and at least one flexure (e.g., one or more bends of a preformed, deformable membrane 330).
  • the at least one flexure has a first portion (e.g., outer perimeter portion 332) affixed to the housing and a second portion (e.g., inner perimeter portion 334) affixed to the connector.
  • the impulse generates a differential force A F between the housing and the connector.
  • the impulse is applied to the housing (e.g., via an external force impacting the housing), while in certain other implementations, the impulse is applied to the connector (e.g., via an external force impacting the connector).
  • applying the impulse can comprise, over a time period, applying a first force to the housing and applying a second force to the connector, the second force different from the first force (e.g., one of the first and second forces is non-zero and the other of the first and second forces is substantially equal to zero; both the first and second forces are non-zero and having different magnitudes and/or directions).
  • the housing and/or the connector move relative to one another (e.g., the housing moving relative to the connector which remains substantially stationary due to inertia; the connector moving relative to the housing which remains substantially stationary due to inertia).
  • the method 400 further comprises dampening the differential force by deforming the at least one flexure.
  • the dampening of the differential force can comprise reducing the differential force to maintain structural integrity of the connector and/or the housing.
  • the deforming can comprise elastic bending such that the differential force is dampened by other forces (e.g., friction) occurring as a result of the elastic bending.
  • the bending can comprise plastic bending or other deformations such that the differential force is dampened by forces occurring within the at least one flexure (e.g., the at least one flexure acting as a “crumple zone” to absorb at least some of the differential force).
  • the method 400 further comprises allowing the connector to move relative to the housing in response to the impulse.
  • the at least one flexure can be more flexible than the housing and the connector, and the flexibility of the at least one flexure can be sufficient to allow the connector to “float” relative to the housing (e.g., to move with at least one motion component substantially parallel to the wall 312a and/or with a motion component substantially perpendicular to the wall 312a). Due to the at least one flexure, impact forces applied to the housing are not transferred from the housing to the connector or from the connector to the housing.
  • the housing, connector, and at least one flexure are resistant to impacts up to 2.5 Joules (e.g., up to 3 Joules; up to 4 Joules; up to 5 Joules).
  • the implanted device can be exposed to differential forces between the housing and the connector (e.g., having a brittle ceramic portion).
  • the at least one flexure can be configured to dissipate the differential forces (e.g., tensile or compressive forces from impacts on the housing and/or inertia and impulses applied to the housing and/or connector), thereby protecting the connector from forces that would otherwise cause damage (e.g., breakage) and/or cause detachment of the connector from components within the housing.
  • the differential forces e.g., tensile or compressive forces from impacts on the housing and/or inertia and impulses applied to the housing and/or connector
  • the terms “generally parallel” and “substantially parallel” refer to a value, amount, or characteristic that departs from exactly parallel by ⁇ 10 degrees, by ⁇ 5 degrees, by ⁇ 2 degrees, by ⁇ 1 degree, or by ⁇ 0.1 degree
  • the terms “generally perpendicular” and “substantially perpendicular” refer to a value, amount, or characteristic that departs from exactly perpendicular by ⁇ 10 degrees, by ⁇ 5 degrees, by ⁇ 2 degrees, by ⁇ 1 degree, or by ⁇ 0.1 degree.
  • the ranges disclosed herein also encompass any and all overlap, sub-ranges, and combinations thereof. Language such as “up to,” “at least,” “greater than,” less than,” “between,” and the like includes the number recited.

Landscapes

  • Engineering & Computer Science (AREA)
  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Otolaryngology (AREA)
  • Computer Hardware Design (AREA)
  • Microelectronics & Electronic Packaging (AREA)
  • Neurosurgery (AREA)
  • Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Prostheses (AREA)

Abstract

Appareil comprenant un châssis, une traversée et une membrane présentant une partie de périmètre externe fixée au châssis et une partie de périmètre interne fixée à la traversée. La membrane est conçue pour fléchir en réponse à une première force appliquée au châssis et/ou à une seconde force appliquée à la traversée.
PCT/IB2025/054266 2024-05-06 2025-04-24 Ensemble implantable à membrane souple Pending WO2025233734A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US202463643229P 2024-05-06 2024-05-06
US63/643,229 2024-05-06

Publications (1)

Publication Number Publication Date
WO2025233734A1 true WO2025233734A1 (fr) 2025-11-13

Family

ID=97674556

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/IB2025/054266 Pending WO2025233734A1 (fr) 2024-05-06 2025-04-24 Ensemble implantable à membrane souple

Country Status (1)

Country Link
WO (1) WO2025233734A1 (fr)

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20090034769A1 (en) * 2005-01-27 2009-02-05 Cochlear Limited Implantable medical device
US20180115842A1 (en) * 2016-10-21 2018-04-26 Jan Vermeiren Implantable transducer system
KR20180090229A (ko) * 2018-07-23 2018-08-10 조성재 이중 변환기를 구비한 보청기용 이어피스
US20180288539A1 (en) * 2013-11-29 2018-10-04 Wim Bervoets Medical device having an impulse force-resistant component
WO2023052876A1 (fr) * 2021-09-29 2023-04-06 Cochlear Limited Actionneur piézoélectrique à coupleur coulissant

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20090034769A1 (en) * 2005-01-27 2009-02-05 Cochlear Limited Implantable medical device
US20180288539A1 (en) * 2013-11-29 2018-10-04 Wim Bervoets Medical device having an impulse force-resistant component
US20180115842A1 (en) * 2016-10-21 2018-04-26 Jan Vermeiren Implantable transducer system
KR20180090229A (ko) * 2018-07-23 2018-08-10 조성재 이중 변환기를 구비한 보청기용 이어피스
WO2023052876A1 (fr) * 2021-09-29 2023-04-06 Cochlear Limited Actionneur piézoélectrique à coupleur coulissant

Similar Documents

Publication Publication Date Title
US9999770B2 (en) Cochlear implant electrode array including receptor and sensor
US8200339B2 (en) Implantable microphone for an implantable hearing prothesis
EP2296750B1 (fr) Capteur de son implantable pour prothèses auditives
AU778131B2 (en) At least partially implantable system for rehabilitation of hearing disorder
US20240196577A1 (en) Electromagnetic interference shielding of mems sensor via printed circuit board
US20250183712A1 (en) Implant with magnetic induction antenna
US20120215055A1 (en) Double diaphragm transducer
WO2025233734A1 (fr) Ensemble implantable à membrane souple
US20240408400A1 (en) Self-locking fixation system for medical implant
US20250229091A1 (en) External portion of medical implant with compliant skin-contacting surface
US20240214753A1 (en) Rotatably adjustable fixation system for medical implant
WO2024089490A1 (fr) Implant médical à stimulation électrique et vibratoire intégrée
WO2024052754A1 (fr) Transducteur avec mode de sécurité intégrée pour implant médical
US12101602B2 (en) Implantable sound sensors with non-uniform diaphragms
WO2025068826A1 (fr) Implant avec capteur intégré à une bobine d'induction
US20210195350A1 (en) Subcutaneous microphone having a central pillar
WO2025012712A1 (fr) Coupleur pour transmettre des vibrations entre un transducteur et une partie de corps
WO2024189441A1 (fr) Réceptacle adhésif pour implant médical
WO2025224541A1 (fr) Enceinte articulée à aimants répulsifs
WO2025027503A1 (fr) Partie externe d'un implant médical avec une surface anatomique en contact avec la peau
WO2024127123A1 (fr) Appareil et procédé d'évaluation de la fonction de dispositif d'un système sensoriel bilatéral