US20110029031A1 - Bimodal hearing prosthesis - Google Patents

Bimodal hearing prosthesis Download PDF

Info

Publication number
US20110029031A1
US20110029031A1 US12/935,650 US93565009A US2011029031A1 US 20110029031 A1 US20110029031 A1 US 20110029031A1 US 93565009 A US93565009 A US 93565009A US 2011029031 A1 US2011029031 A1 US 2011029031A1
Authority
US
United States
Prior art keywords
recipient
prosthesis
actuator
configured
sound signal
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.)
Abandoned
Application number
US12/935,650
Inventor
John Parker
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
John Parker
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
Priority to US4118508P priority Critical
Application filed by John Parker filed Critical John Parker
Priority to US12/935,650 priority patent/US20110029031A1/en
Priority to PCT/US2009/038937 priority patent/WO2009124038A1/en
Publication of US20110029031A1 publication Critical patent/US20110029031A1/en
Assigned to COCHLEAR LIMITED reassignment COCHLEAR LIMITED ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: PARKER, JOHN L.
Application status is Abandoned legal-status Critical

Links

Images

Classifications

    • HELECTRICITY
    • H04ELECTRIC COMMUNICATION TECHNIQUE
    • H04RLOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • HELECTRICITY
    • H04ELECTRIC COMMUNICATION TECHNIQUE
    • H04RLOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/60Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
    • H04R25/604Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers
    • H04R25/606Mounting 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
    • HELECTRICITY
    • H04ELECTRIC COMMUNICATION TECHNIQUE
    • H04RLOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/70Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00General characteristics of the apparatus
    • A61M2205/05General characteristics of the apparatus combined with other kinds of therapy
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2210/00Anatomical parts of the body
    • A61M2210/06Head
    • A61M2210/0662Ears
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/142Pressure infusion, e.g. using pumps
    • A61M5/14244Pressure infusion, e.g. using pumps adapted to be carried by the patient, e.g. portable on the body
    • A61M5/14276Pressure infusion, e.g. using pumps adapted to be carried by the patient, e.g. portable on the body specially adapted for implantation
    • HELECTRICITY
    • H04ELECTRIC COMMUNICATION TECHNIQUE
    • H04RLOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2460/00Details of hearing devices, i.e. of ear- or headphones covered by H04R1/10 or H04R5/033 but not provided for in any of their subgroups, or of hearing aids covered by H04R25/00 but not provided for in any of its subgroups
    • H04R2460/13Hearing devices using bone conduction transducers
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10TTECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T29/00Metal working
    • Y10T29/49Method of mechanical manufacture
    • Y10T29/4957Sound device making
    • Y10T29/49572Hearing aid component making

Abstract

A bimodal hearing prosthesis for rehabilitating the hearing of a recipient. The hearing prosthesis comprises: a sound processing unit configured to process a received sound signal; and an implantable bimodal stimulation system, comprising: a mechanical stimulation arrangement configured to generate waves of fluid motion in a recipient's inner ear fluid based on the processed sound signal; an electrode assembly configured to deliver electrical stimulation signals generated based on the processed sound signal to a recipient's cochlea.

Description

    CROSS-REFERENCE TO RELATED APPLICATIONS
  • The present application is a National Stage Application of International Application No. PCT/US2009/038937, filed Mar. 31, 2009, and claims the benefit of U.S. Provisional Patent Application 61/041,185; filed Mar. 31, 2008. The contents of these applications are hereby incorporated by reference herein.
  • BACKGROUND
  • 1. Field of the Invention
  • The present invention is generally directed to a hearing prosthesis, and more particularly, to a bimodal hearing prosthesis.
  • 2. Related Art
  • Hearing loss, which may be due to many different causes, is generally of two types, conductive and sensorineural. In some cases, an individual may have hearing loss of both types. In many people who are profoundly deaf, however, the reason for their deafness is sensorineural hearing loss. Sensorineural hearing loss occurs when there is damage to the inner ear, or to the nerve pathways from the inner ear to the brain. As such, those suffering from sensorineural hearing loss are thus unable to derive suitable benefit from conventional acoustic hearing aids. As a result, hearing prostheses that deliver electrical stimulation to nerve cells of the recipient's auditory system have been developed to provide persons having sensorineural hearing loss with the ability to perceive sound. Such electrically-stimulating hearing prostheses deliver electrical stimulation to nerve cells of the recipient's auditory system.
  • As used herein, the recipient's auditory system includes all sensory system components used to perceive a sound signal, such as hearing sensation receptors, neural pathways, including the auditory nerve and spiral ganglion, and parts of the brain used to sense sounds. Electrically-stimulating hearing prostheses include, for example, auditory brain stimulators and cochlear™ prostheses (commonly referred to as cochlear prosthetic devices, cochlear implants, cochlear devices, and the like; simply “cochlear implants” herein.)
  • Most sensorineural hearing loss is due to the absence or destruction of the cochlea hair cells which transduce acoustic signals into nerve impulses. It is for this purpose that cochlear implants have been developed. Cochlear implants electrically stimulate a recipient's cochlea by directly delivering direct electrical stimulation signals to the auditory nerve cells, thereby bypassing absent or defective hair cells that normally transduce acoustic vibrations into neural activity. Such devices generally use an electrode array implanted in the cochlea so that the electrodes may differentially activate auditory neurons that normally encode differential pitches of sound.
  • In contrast to sensorineural hearing loss, conductive hearing loss occurs when the normal mechanical pathways used to provide sound to hair cells in the cochlea are impeded, for example, by damage to the ossicular chain or to the ear canal. Individuals who suffer from conductive hearing loss typically have some form of residual hearing because the hair cells in the cochlea are undamaged. As a result, individuals suffering from conductive hearing loss typically receive an acoustic hearing aid. Acoustic hearing aids stimulate an individual's cochlea by providing an amplified sound to the cochlea, where the amplified sound causes mechanical motion of the cochlear fluid.
  • Unfortunately, not all individuals who suffer from conductive hearing loss are able to derive suitable benefit from hearing aids. For example, some individuals are prone to chronic inflammation or infection of the ear canal and cannot wear hearing aids. Similarly, hearing aids are typically unsuitable for individuals who have malformed, damaged or absent outer ears, ear canals and/or ossicular chains.
  • SUMMARY
  • In one aspect of the invention, a bimodal hearing prosthesis for rehabilitating the hearing of a recipient is provided. The hearing prosthesis comprises: a sound processing unit configured to process a received sound signal; and an implantable bimodal stimulation system, comprising: a mechanical stimulation arrangement configured to generate waves motion in a recipient's inner ear fluid based on the processed sound signal; an electrode assembly configured to deliver to the recipient's cochlea electrical stimulation signals generated based on the processed sound signal.
  • In another aspect of the invention, a method for rehabilitating the hearing of a recipient with a bimodal hearing prosthesis comprising an implantable electrode assembly configured to electrically stimulate a recipient and an implantable mechanical stimulation arrangement configured to directly mechanically stimulate the recipient's inner ear by generating waves of fluid motion in the recipient's inner ear fluid is provided. The method comprises: receiving an acoustic sound signal; processing the acoustic sound signal; generating one or more of electrical stimulation signals and mechanical stimulation signals, based on the processed acoustic sound signal; and stimulating the recipient's inner ear using the generated stimulation signals.
  • In a still other aspect of the present invention, a bimodal hearing prosthesis for rehabilitating the hearing of a recipient is provided. The prosthesis comprises: means for receiving an acoustic sound signal; means for processing the acoustic sound signal; means for generating one or more of electrical stimulation signals and mechanical stimulation signals, based on the processed acoustic sound signal; and means for stimulating the recipient's inner ear based on the generated stimulation signals
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • Illustrative embodiments of the present invention are described herein with reference to the accompanying drawings, in which:
  • FIG. 1A is a partial cross-sectional view of an individual's head in which embodiments of the present invention may be implemented;
  • FIG. 1B is a perspective, partially cut-away view of a cochlea exposing the canals and nerve fibers of the cochlea;
  • FIG. 1C is a cross-sectional view of one turn of the canals of a human cochlea;
  • FIG. 2 is a perspective view of an implanted bimodal hearing prosthesis in accordance with embodiments of the present invention;
  • FIG. 3 is a functional block diagram of a bimodal hearing prosthesis in accordance with embodiments of the present invention;
  • FIG. 4 is a perspective view of a mechanical stimulation arrangement, in accordance with embodiments of the present invention;
  • FIG. 5 is a perspective view of a mechanical stimulation arrangement, in accordance with embodiments of the present invention;
  • FIG. 6 is a simplified side view of cochlea having an electrode assembly in accordance with embodiments of the present invention implanted therein; and
  • FIG. 7 is flowchart illustrating the operations performed by a bimodal hearing prosthesis.
  • DETAILED DESCRIPTION
  • Aspects of the present invention are generally directed to a hearing prosthesis configured to selectively electrically and/or mechanically stimulate a recipient's cochlea. Such a hearing prosthesis, referred to herein as a bimodal hearing prosthesis, comprises an electrode assembly configured to be implanted in a recipient's cochlea, and a mechanical stimulation arrangement. The electrode assembly delivers electrical stimulation signals to the cochlea, while the mechanical stimulation arrangement bypasses the recipient's outer and middle ears to directly generate waves of fluid motion in the recipient's inner ear. In certain embodiments, the mechanical stimulation arrangement is configured to be positioned adjacent the inner ear and may comprise, for example, a middle ear or inner ear mechanical stimulator. In other embodiments, the mechanical stimulation arrangement is a bone conduction device.
  • FIG. 1A is perspective view of an individual's head 100 in which embodiments of a bimodal hearing prosthesis in accordance with embodiments of the present invention may be implemented. As shown in FIG. 1A, the individual's hearing system comprises an outer ear 101, a middle ear 105 and an inner ear 107. In a fully functional ear, outer ear 101 comprises an auricle 110 and an ear canal 102. An acoustic pressure or sound wave 103 is collected by auricle 110 and channeled into and through ear canal 102. Disposed across the distal end of ear cannel 102 is a tympanic membrane 104 which vibrates in response to 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. Bones 108, 109 and 111 of middle ear 105 are disposed within mastoid bone 119 and serve to filter and amplify sound wave 103, causing oval window 112 to articulate, or vibrate in response to vibration of tympanic membrane 104. This vibration sets up waves of fluid motion of the perilymph within cochlea 140. Such fluid motion, in turn, activates tiny hair cells (not shown) inside of 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.
  • Also shown in FIG. 1A are semicircular canals 125. Semicircular canals 125 are three half-circular, interconnected tubes located adjacent cochlea 140. The three canals are the horizontal semicircular canal 126, the posterior semicircular canal 127, and the superior semicircular canal 128, all of which are aligned approximately orthogonally to one another. Specifically, horizontal canal 126 is aligned roughly horizontally in the head, while the superior 128 and posterior canals 127 are aligned roughly at a 45 degree angle to a vertical through the center of the individual's head 100.
  • Each of the semicircular canals 125 is filled with a fluid known as endolymph, and contains a tiny hairs (not shown) whose ends are embedded in a gelatinous structure known as the cupula (also not shown). As the individual's head 100 twists in various directions, the endolymph moves into different sections of semicircular canals 125. The hairs detect when the endolymph passes thereby, and a signal is then sent to the brain. Therefore, using the hair cells, horizontal canal 126 is able to detect horizontal head movements, while the superior 128 and posterior 127 canals are able to detect vertical head movements.
  • The details of cochlea 140 are described next below with reference to FIGS. 1B and 1C. FIG. 1B is a perspective view of cochlea 140 partially cut-away to display the canals and nerve fibers of the cochlea, while FIG. 1C is a cross-sectional view of one turn of the canals of cochlea 140.
  • Referring to FIG. 1B, cochlea 140 is a conical spiral structure comprising three parallel fluid-filled canals or ducts, collectively and generally referred to herein as canals 132. Canals 132 comprise the tympanic canal 138, also referred to as the scala tympani 138, the vestibular canal 134, also referred to as the scala vestibuli 134, and the median canal 136, also referred to as the cochlear duct 136. Cochlea 140 has a conical shaped central axis, the modiolus 154, that forms the inner wall of scala vestibuli 134 and scala tympani 138. The base of scala vestibuli 134 comprises oval window 112 (FIG. 1A), while the base of scala tympani 138 terminates in round window 121 (FIG. 1A). Tympanic and vestibular canals 138, 134 transmit pressure waves received at oval window 112, while medial canal 136 contains the organ of Corti 150 which detects pressure impulses and responds with electrical impulses which travel along auditory nerve 114 to the brain (not shown).
  • Cochlea 140 spirals about modiolus 154 several times and terminates at cochlea apex 146. Modiolus 154 is largest near its base where it corresponds to first turn 151 of cochlea 140. The size of modiolus 154 decreases in the regions corresponding to medial 152 and apical turns 156 of cochlea 140.
  • Referring now to FIG. 1C, separating canals 132 of cochlear 140 are various membranes and other tissue. The ossicous spiral lamina 182 projects from modiolus 154 to separate scala vestibuli 134 from scala tympani 138. Toward lateral side 172 of scala tympani 138, a basilar membrane 158 separates scala tympani 138 from cochlear duct 136. Similarly, toward lateral side 172 of scala vestibuli 134, a vestibular membrane 166, also referred to as the Reissner's membrane 166, separates scala vestibuli 134 from cochlear duct 136.
  • Portions of cochlea 140 are encased in a bony capsule 170. Bony capsule 170 resides on lateral side 172 (the right side as drawn in FIG. 1C), of cochlea 140. Spiral ganglion cells 180 reside on the opposing medial side 174 (the left side as drawn in FIG. 1C) of cochlea 140. A spiral ligament membrane 164 is located between lateral side 172 of spiral tympani 138 and bony capsule 170, and between lateral side 172 of cochlear duct 136 and bony capsule 170. Spiral ligament 164 also typically extends around at least a portion of lateral side 172 of scala vestibuli 134.
  • Sound entering auricle 110 causes pressure changes in cochlea 140 to travel through the fluid-filled tympanic and vestibular canals 138, 134. As noted, organ of Corti 150 is situated on basilar membrane 158 in cochlear duct 136. It contains rows of 16,000-20,000 hair cells (not shown) which protrude from its surface. Above them is the tectoral membrane 162 which moves in response to pressure variations in the fluid-filled tympanic and vestibular canals 138, 134. Small relative movements of the layers of membrane 162 are sufficient to cause the hair cells to send a voltage pulse or action potential down the associated nerve fiber 178. Nerve fibers 178, embedded within spiral lamina 182, connect the hair cells with the spiral ganglion cells 180 which form auditory nerve 114. Auditory nerve 114 relays the impulses to the auditory areas of the brain (not shown) for processing.
  • The place along basilar membrane 158 where maximum excitation of the hair cells occurs determines the perception of pitch and loudness according to the place theory. Due to this anatomical arrangement, cochlea 140 has characteristically been referred to as being “tonotopically mapped.” That is, regions of cochlea 140 toward basal region 116 (FIG. 1) are responsive to high frequency signals, while regions of cochlea 140 toward apex 146 are responsive to low frequency signals. As discussed in greater detail below, these tonotopical properties of cochlea 140 are exploited in a cochlear implant by delivering stimulation signals within a predetermined frequency range to a region of the cochlea that is most sensitive to that frequency range.
  • The fluid in tympanic and vestibular canals 138, 134, referred to as perilymph, has different properties than that of the fluid which fills cochlear duct 136 and which surrounds organ of Corti 150, referred to as endolymph. As described above with reference to FIG. 1A, semicircular canals 125 are also filled with endolymph. The vestibule 129 (FIG. 1A) provides fluid communication between the endolymph in semicircular canals 125 and the endolymph in cochlear duct 136.
  • FIG. 2 is a perspective view of bimodal hearing prosthesis 200 in accordance with embodiments of the present invention. Bimodal hearing prosthesis 200 comprises an external component 242 which is directly or indirectly attached to the body of the recipient, and an internal component 244 which is temporarily or permanently implanted in the recipient. External component 242 typically comprises one or more sound input elements, such as microphone 224 for detecting sound, a sound processing unit 226, a power source (not shown), and an external transmitter unit 228. External transmitter unit 228 comprises an external coil 230 and, preferably, a magnet (not shown) secured directly or indirectly to external coil 230. Sound processing unit 226 processes the output of microphone 224 that is positioned, in the depicted embodiment, by auricle 110 of the recipient. Sound processing unit 226 generates encoded signals, sometimes referred to herein as encoded data signals, which are provided to external transmitter unit 228 via a cable (not shown).
  • Internal component 244 comprises an internal receiver unit 232, a stimulator unit 220, and a bimodal stimulation system 280. Bimodal stimulation system 280 comprises an elongate electrode assembly 248 and a mechanical stimulation arrangement 215. Internal receiver unit 232 comprises an internal coil 236, and preferably, a magnet (also not shown) fixed relative to the internal coil. Internal receiver unit 232 and stimulator unit 220 are hermetically sealed within a biocompatible housing, sometimes collectively referred to as a stimulator/receiver unit.
  • In the illustrative embodiment of FIG. 2, external coil 230 transmits electrical signals (i.e., power and stimulation data) to internal coil 236 via a radio frequency (RF) link. Internal coil 236 is typically a wire antenna coil comprised of multiple turns of electrically insulated single-strand or multi-strand platinum or gold wire. The electrical insulation of internal coil 236 is provided by a flexible silicone molding (not shown). In use, implantable receiver unit 232 may be positioned in a recess of the temporal bone adjacent auricle 110 of the recipient.
  • As noted, internal component 244 further includes a bimodal stimulation system 280. As shown, bimodal stimulation system 280 comprises an electrode assembly 248 which is configured to be implanted in cochlea 140. Electrode assembly 248 comprises a longitudinally aligned and distally extending array 245 of electrodes 246, sometimes referred to as electrode array 245 herein, disposed along a length thereof. Although electrode array 245 may be disposed on electrode assembly 248, in most practical applications, electrode array 245 is integrated into electrode assembly 248. As such, electrode array 245 is referred to herein as being disposed in electrode assembly 248. The proximal end of electrode assembly 248 is electrically connected to a lead 262 extending from stimulator unit 220. As described below, in embodiments of the present invention, stimulator unit 220 generates, based on data signals received at receiver unit 232, electrical stimulation signals which are delivered to electrode assembly 248 via lead 262. The stimulation signals are applied by electrodes 246 to cochlea 140, thereby stimulating auditory nerve 114.
  • As described in greater detail below, in embodiments of the present invention, electrode assembly 248 is implanted at least in basal region 116 of cochlea 140, and sometimes further. For example, electrode assembly 248 may extend towards apical end of cochlea 140, referred to as cochlea apex 134. In certain circumstances, electrode assembly 248 may be inserted into cochlea 140 via a cochleostomy 122. In other circumstances, a cochleostomy may be formed through round window 121, oval window 112 (FIG. 1A), the promontory 123 or through an apical turn 147 of cochlea 140.
  • Electrode assembly 248 may comprise a perimodiolar electrode assembly which is configured to adopt a curved configuration during and or after implantation into the recipient's cochlea. In one such embodiment, electrode assembly 248 is pre-curved to the same general curvature of a cochlea. Electrode assembly 248 is held straight by, for example, a stiffening stylet (not shown) which is removed during implantation so that the assembly adopts the curved configuration. Other methods of implantation, as well as other electrode assemblies which adopt a curved configuration may be used in alternative embodiments of the present invention.
  • In other embodiments, electrode assembly 248 comprises a non-perimodiolar electrode assembly which does not adopt a curved configuration. For example, electrode assembly 248 may comprise a straight assembly or a mid-scala assembly which assumes a mid-scala position during or following implantation.
  • As shown in FIG. 2, bimodal stimulation system 280 further comprises mechanical stimulation arrangement 215. As previously noted, a mechanical stimulation arrangement in accordance with embodiments of the present invention may comprise a middle ear or inner ear mechanical stimulator, or a bone conduction device. Details of exemplary bone conduction devices that may utilized with embodiments of the present invention are described in U.S. Provisional Patent Application 61/041,185. For ease of illustration, embodiments of the present invention will be described with reference to a mechanical stimulation arrangement that stimulates the recipient's inner ear. However, this exemplary illustration should not be considered to limit the present invention.
  • In the illustrative embodiment of FIG. 2, ossicles 106 have been omitted from FIG. 2 to illustrate an exemplary location of the inner ear mechanical stimulation arrangement 215. It should be appreciated that stimulation arrangement 215 may be implanted without disturbing ossicles 106.
  • Stimulation arrangement 215 comprises an actuator 240 electrically connected to stimulator unit 220 by lead 264, a stapes prosthesis 254 and a coupling element 253. As described in greater detail below with reference to FIG. 5, in this illustrative embodiment, coupling element 253 connects actuator 240 to stapes prosthesis 254 which abuts round window 121 (FIG. 1A). In certain embodiments of the present invention, based on data signals received at receiver unit 232, stimulator unit 220 generates actuator drive signals which cause vibration of actuator 240. This vibration is transferred to the inner ear fluid (perilymph) in the recipient's scala tympani via coupling element 253 and stapes prosthesis 254, thereby evoking a hearing percept by the recipient.
  • Although the embodiments of FIG. 2 have been described with reference to a bimodal hearing prosthesis 200 having an external component, it should be appreciated that in alternative embodiments bimodal hearing prosthesis 200 is a totally implantable device. In such embodiments, sound processing unit 226 is implanted in a recipient in the mastoid bone and the sound processing unit communicates directly with stimulator unit 220, thereby eliminating the need for transmitter unit 228 and receiver unit 232.
  • FIG. 3 is a functional block diagram illustrating an embodiment of bimodal hearing prosthesis 200, referred to herein as bimodal hearing prosthesis 300. In the illustrated embodiment, bimodal hearing prosthesis 300 comprises an external component 342, and an internal component 344. External component 342 comprises one or more sound input elements 324 for detecting sound, a sound processing unit 326, a power source (not shown), and an external transmitter unit 328.
  • Sound input element 324 receives a sound signal 301 and generates an electrical output signal 303 representing the sound. Electrical signal 303 is provided to sound processing unit 326 which converts the signal into encoded data signals which may be transmitted to internal component 344. More specifically, in the illustrative embodiment of FIG. 3, electrical signal 303 is provided to a preprocessor 350. In embodiments of the present invention, preprocessor 350 filters signal 303 and provides a signal component 305 in a first frequency band to an electrical stimulation processor 352, and provides a signal component 307 in a second frequency band to a mechanical stimulation processor 354. The first frequency band comprises a high frequency portion of the audible frequency spectrum, which, as described above, is perceivable by the basal region of a cochlea. The second frequency band comprises a low frequency portion of the audible frequency spectrum, which is perceivable by apical regions of a cochlea. In other words, in the illustrative embodiments of FIG. 3, preprocessor 350 performs a frequency analysis of sound 301 and/or signal 303, and allocates certain frequency portions to signals 305 and 307.
  • Electrical stimulation processor 352 processes signal component 305 to generate a processed electrical signal 309 representing the high frequency components of sound signal 301. Similarly, mechanical stimulation processor 354 processes signal component 307 to generate a processed electrical signal 311 representing the low frequency components of sound signal 301. Signals 309, 311 are then provided to transmitter unit 328 where the signals are encoded and transmitted to receiver unit 332 in internal component 344. Internal receiver unit decodes the transmitted signals, and provides electrical signals 309, 311 to stimulator unit 320.
  • Based on electrical signals 309, 311, stimulator unit 320 generates stimulation signals which are provided to one or more components of bimodal stimulation system 380. As shown, bimodal stimulation system 380 comprises an electrode assembly 318 and a mechanical stimulation arrangement 315. Stimulator unit 320 comprises an electrical stimulation signal generator 356 configured to generate electrical stimulation signals 319 based on electrical signals 309. Electrical stimulation signals 319 are provided to electrode assembly 318 for delivery to the recipient, thereby stimulating auditory nerve 114 (FIG. 1).
  • Stimulator unit 320 further comprises actuator drive components 358. Based on signal 311, actuator drive components 358 generate stimulation signals 321 which are provided to mechanical stimulation arrangement 315. Stimulation signals 321, sometimes referred to herein as actuator drive signals 321, cause vibration of an actuator within mechanical stimulation arrangement 315. As described above, in certain embodiments the actuator is coupled to the recipient's inner ear, the vibration is transferred to the inner ear fluid, thereby evoking a hearing percept by the recipient. In other embodiments, the actuator is a positioned to deliver vibration to the recipient's skull. For example, the actuator may be part of an externally worn bone conduction device, or an implanted bone conduction device.
  • Although the embodiments of FIG. 3 have been described with reference to a bimodal hearing prosthesis 300 having an external component, it should be appreciated that in alternative embodiments bimodal hearing prosthesis 300 is a totally implantable device. In such embodiments, sound processing unit 326 is implanted in a recipient in the mastoid bone and the sound processing unit communicates directly with stimulator unit 320, thereby eliminating the need for transmitter unit 328 and receiver unit 332.
  • Similarly, bimodal hearing prosthesis 300 has been described above with reference to a preprocessor 350 which filters electrical signal 303 based on the frequency of received sound signal 301. It should be appreciated that preprocessor 350 may also filter electrical signal 303 using alternative criteria, signal characteristics, etc. For example, in certain embodiments, preprocessor 350 may allocate the entirety of electrical signal 303 to electrical stimulation processor 352 or mechanical stimulation processor 354.
  • FIG. 4 illustrates an exemplary mechanical stimulation arrangement 415 which may be implemented in a bimodal hearing prosthesis in accordance with embodiments of the present invention. As previously noted, mechanical stimulation arrangement may comprise a middle ear or inner ear stimulator, or a bone conduction device. In the illustrative embodiment of FIG. 4, stimulation arrangement 415 is a inner ear stimulator configured to generate wave(s) of fluid motion of the endolymph contained in a recipient's semicircular canal 126. Because, as noted above, vestibule 129 (FIG. 1A) provides fluid communication between the semicircular canal 126 and the cochlear duct 136 (FIG. 1B), a generated wave of fluid motion continues into cochlear duct 136, thereby activating the hair cells of the organ of Corti 150 (FIG. 1C). Activation of the hair cells causes appropriate nerve impulses to be generated and transferred through the spiral ganglion cells (FIG. 1C) and auditory nerve (FIG. 1A) to the recipient's brain where they are perceived as sound.
  • Stimulation arrangement 415 comprises an actuator 440 coupled to a stimulator unit (not shown) by a lead or cable 428. Actuator 440 may be positioned and secured to the recipient by a fixation system. Exemplary fixation systems that may be used to secure actuator 440 to the recipient are described in commonly owned and co-pending U.S. patent application Ser. No. 12/349,495 entitled “MECHANICAL SEMICIRCULAR CANAL STIMULATOR,” and commonly owned and co-pending U.S. patent application Ser. No. 12/349,502 entitled “MECHANICAL SCALA TYMPANI CANAL STIMULATOR,” the contents of both are hereby incorporated by reference herein in their entirety.
  • In the embodiments of FIG. 4, stimulation arrangement 415 comprises a stapes prosthesis 452. Stapes prosthesis 452 is a substantially cylindrical member having a first end 460 abutting an opening 405 in the recipient's horizontal semicircular canal 126. Connecting actuator 440 and stapes prosthesis 452 is a coupler 409. Coupler 409 comprises a first elongate component 404 extending longitudinally from actuator 440. Disposed at the distal portion of first component 404 is a second component 406. Second component is oriented such that the component extends away first component 404 at an angle and connects to stapes prosthesis 452. In other words, an axis 411 extending through the center of second component 406 along the direction of orientation is at an angle from the longitudinal axis 407 of first component 404. In certain embodiments, second component 406 is oriented such that axis 411 is positioned at an angle of approximately 125 degrees from longitudinal axis 407.
  • To implant stimulation arrangement 415, a surgeon may drill or form a passageway in the mastoid of the skull. This passageway is preferably constructed and arranged such that it provides direct access to the cochlea. In this embodiment, the surgeon then drills or forms an opening in one of the recipient's semicircular canals 125 (FIG. 1). In the illustrative embodiment of FIG. 4, this opening is created in horizontal semicircular canal 126, however it would be appreciated that an opening created in posterior semicircular canal 127 (FIG. 1A) or superior semicircular canal 128 (FIG. 1A) may also be used.
  • FIG. 5 illustrates an alternative stimulation arrangement 515 which may be implemented in a bimodal hearing prosthesis in accordance with embodiments of the present invention. In the illustrative embodiment of FIG. 5, stimulation arrangement 515 is configured to generate fluid motion of the perilymph contained in a recipient's scala tympani 138 (FIG. 1B). As discussed above, fluid motion of the perilymph activates the hair cells of the organ of Corti 150 (FIG. 1C). Activation of the hair cells causes appropriate nerve impulses to be generated and transferred through the spiral ganglion cells (FIG. 1C) and auditory nerve (FIG. 1A) to the recipient's brain where they are perceived as sound.
  • Stimulation arrangement 515 comprises an actuator 540 coupled to a stimulator unit (not shown) by a lead or cable (not shown). Actuator 540 may be positioned and secured to the recipient by a fixation system. Exemplary fixation systems that may be used to secure actuator 540 to the recipient are described in commonly owned and co-pending U.S. patent application Ser. No. 12/349,495 entitled “MECHANICAL SEMICIRCULAR CANAL STIMULATOR,” and commonly owned and co-pending U.S. patent application Ser. No. 12/349,502 entitled “MECHANICAL SCALA TYMPANI CANAL STIMULATOR,” the contents of both are hereby incorporated by reference herein in their entirety.
  • Stimulation arrangement 515 further comprises a stapes prosthesis 554. As shown in FIG. 5, stapes prosthesis 554 is a substantially cylindrical member having a first end 560 and a second end 514. As shown, first and second ends 560 and 514 have cross-sectional diameters which exceed the cross-sectional diameter of the remainder of prosthesis 554. Distal end 560 is configured to be positioned abutting the membrane of round window 121 in the recipient's cochlea.
  • Connecting actuator 540 and stapes prosthesis 554 is a coupler 509. In the illustrative embodiment, coupler 509 comprises an elongate rod extending longitudinally from actuator 540 along axis 507. The distal portion of rod 508 is connected to stapes prosthesis 554. In the illustrative embodiment of FIG. 5A, stapes prosthesis 554 is aligned along, and is substantially symmetrical about axis 507. In other words, the surface of first end 560 is positioned orthogonal to axis 507. As described in commonly owned and co-pending U.S. patent application Ser. No. 12/349,502 entitled “MECHANICAL SCALA TYMPANI CANAL STIMULATOR,” various embodiments of coupler 509 are possible. Similarly, various different mechanisms may be used to connect coupler 509 to stapes prosthesis 554.
  • FIGS. 4 and 5 illustrate embodiments of mechanical stimulation arrangements 415, 515, which may be implemented in a bimodal hearing prosthesis in accordance with embodiments of the present invention. Further features of stimulation arrangements which may be implemented in embodiments of the present invention are described in commonly owned and co-pending U.S. patent application Ser. No. 12/349,495 entitled “MECHANICAL SEMICIRCULAR CANAL STIMULATOR,” and commonly owned and co-pending U.S. patent application Ser. No. 12/349,502 entitled “MECHANICAL SCALA TYMPANI CANAL STIMULATOR,” the contents of both are hereby incorporated by reference herein in their entirety.
  • As noted above, various electrode assemblies may be used in embodiments of the present invention. For example, in embodiments of the present invention an electrode assembly may be implanted in basal region 116 (FIG. 1) of cochlea 140 (FIG. 1), or the electrode assembly may extend towards apical end of cochlea 140, referred to as cochlea apex 134. FIG. 6 is a simplified side view of a recipient's cochlea 140 having implanted therein an electrode assembly 646 utilized in embodiments of the present invention. In the illustrative embodiment of FIG. 6, electrode assembly 646 is implanted only in the basal region of cochlea 140. Such an electrode assembly is sometimes referred to herein as a short electrode assembly. For ease of illustration, a simplified view of cochlea 140 is shown. As such, the scala tympani and the scala vestibule have not been differentiated in FIG. 6. It would be appreciated that short electrode assembly 646 may be inserted into either the scala tympani or the scala vestibuli of cochlea 140.
  • As noted above, cochlea 140 is “tonotopically mapped.” That is, regions of cochlea 140 in basal region 116 are responsive to high frequency signals, while regions of cochlea 140 toward apex 146 are responsive to low frequency signals. As a result of this tonotopic arrangement, individuals may suffer sensorineural hearing loss only in certain frequency ranges. For example, certain individuals may loss the ability to perceive high frequency signals (ie. suffer sensorineual hearing loss in the basal regions of the cochlea), while retaining the ability to perceive low frequency signals. Such individuals maintain the ability to perceive middle to lower frequency sounds naturally, but have limited or no ability to perceive high frequency sounds. Short electrode assembly 646 of FIG. 6 may be advantageously implemented in such individuals.
  • In the embodiment of FIG. 6, when short electrode assembly 646 is fully implanted, distal end 636 of the electrode assembly is positioned at or near distal end 639 of basal region 116. As used herein, basal region 116 of cochlea 140 is the portion of the scala tympani and the scala vestibuli extending from the round window and oval window, respectively, to the first turn 641 of cochlea 140. Therefore, when short electrode assembly 646 is fully implanted in cochlea 140, distal end 636 of the short electrode assembly is positioned at, in, or proximate to the region of cochlea 140 at which the first turn 641 of cochlea 140 begins. As used herein, the positioning of distal end 636 in this region of cochlea 140 includes positioning the distal end in basal region 116 or in first turn 641.
  • As shown, short electrode assembly 646 includes an array of electrodes 648. Electrodes 648 are configured to apply electrical stimulation signals (not shown) to basal region 116 of cochlea 140. In certain embodiments, electrode assembly 646 comprises a perimodiolar electrode assembly configured to adopt a curved configuration during and or after implantation into the recipient's cochlea. In one such embodiment, distal portion 618 of electrode assembly 646 is pre-curved so as to be positioned in first turn 641. Electrode assembly 646 is held straight by, for example, a stiffening stylet (not shown) which is removed during implantation so that distal end 636 adopts the curved configuration. Other methods of implantation, as well as other electrode assemblies which adopt a curved configuration may be used in alternative embodiments of the present invention. In other embodiments, electrode assembly 646 comprises a non-perimodiolar electrode assembly which does not adopt a curved configuration.
  • Although the embodiments of FIG. 6 have been described with reference to a short electrode assembly 646, it should be appreciated that other electrode assemblies may be implemented in certain embodiments of the present invention. For example, in some embodiments, an electrode assembly that extends into medial region 643 and or apical region 645 may be used.
  • FIG. 7 is a flowchart illustrating the operations performed in a method 700 implemented by a bimodal hearing prosthesis in accordance with embodiments of the present invention. During the implemented method, a sound signal is received at block 702, by, for example, a sound input element such as a microphone, telecoil, electrical input, etc.
  • As previously noted, a bimodal hearing prosthesis in accordance with embodiments of the present invention may be configured to electrically and/or mechanically stimulate a recipient's cochlea. As such, at block 704, the bimodal hearing prosthesis selects which of these mode or modes of stimulation will be used to stimulate the recipient's cochlea. At block 706 the bimodal hearing prosthesis generates stimulation signals in accordance with the modes selected at block 704. At block 708, the recipient's inner ear is stimulated using the stimulation signals.
  • The invention described and claimed herein is not to be limited in scope by the specific preferred embodiments herein disclosed, since these embodiments are intended as illustrations, and not limitations, of several aspects of the invention. Any equivalent embodiments are intended to be within the scope of this invention.

Claims (27)

1. A bimodal hearing prosthesis for rehabilitating the hearing of a recipient, comprising:
a sound processing unit configured to process a received sound signal; and
an implantable bimodal stimulation system, comprising:
a mechanical stimulation arrangement configured to generate waves of fluid motion in the recipient's inner ear fluid based on the processed sound signal;
an electrode assembly configured to deliver to the recipient's cochlea electrical stimulation signals generated based on the processed sound signal.
2. The prosthesis of claim 1, wherein the mechanical stimulation arrangement comprises:
a stapes prosthesis having a first end configured to be positioned so as to abut an opening in one of the recipient's semicircular canals;
an actuator configured to receive electrical signals representing the processed sound configured to vibrate in response to the electrical signals; and
a coupler connecting the actuator to the stapes prosthesis such that vibration of the actuator results in the direct generation of waves of fluid motion in the semicircular canal.
3. The prosthesis of claim 1, wherein the mechanical stimulation arrangement comprises:
an actuator configured to receive electrical signals representing the processed sound signal and configured to vibrate in response to the electrical signals;
a stapes prosthesis having first and second ends, the first end having a surface configured to be positioned abutting the round window in the recipient's cochlea, and wherein the first end surface is substantially orthogonal to a longitudinal axis extending through the actuator; and
an elongate rod connecting the actuator to the stapes prosthesis such that vibration of the actuator results in the direction generation of waves of fluid motion in the recipient's scala tympani.
4. The prosthesis of claim 2, wherein the coupler comprises:
a first elongate component extending longitudinally from the actuator, and
a second component attached to, and extending from the distal portion of the first component at an angle.
5. The prosthesis of claim 2, wherein the first elongate component comprises:
an elongate rod having an adjustable length.
6. The prosthesis of claim 4, wherein the second component is attached to the first component by a pivot joint configured to permit adjustment of the angle at which the second component extends from the first component.
7. The prosthesis of claim 1, wherein the mechanical stimulation arrangement comprises an actuator configured to vibrate the recipient's skull.
8-14. (canceled)
15. The prosthesis of claim 1, further comprising:
a preprocessor configured to evaluate the processed sound signal and to select which one or more of the mechanical stimulation arrangement and the electrode assembly is to be used to stimulate the recipient's cochlea based on the processed sound signal.
16. The prosthesis of claim 15, wherein the preprocessor is configured to perform a frequency analysis of the received sound signal to select which one or more of the mechanical stimulation arrangement and the electrode assembly is to be used to stimulate the recipient's cochlea
17. A method for rehabilitating the hearing of a recipient with a bimodal hearing prosthesis the prosthesis comprising an implantable electrode assembly configured to electrically stimulate a recipient and an implantable mechanical stimulation arrangement configured to mechanically stimulate the recipient's inner ear by generating waves of fluid motion in the recipient's inner ear fluid, the method comprising:
receiving an acoustic sound signal;
processing the acoustic sound signal;
generating one or more of electrical stimulation signals and mechanical stimulation signals, based on the processed acoustic sound signal; and
stimulating the recipient's inner ear based on the generated stimulation signals.
18. The method of claim 17, wherein generating one or more of electrical stimulation signals and mechanical stimulation signals, comprises:
generating electrical stimulation signals, and
simultaneously generating mechanical stimulation signals.
19. The method of claim 17, further comprising:
directly generating waves of fluid motion in one of the recipient's semicircular canals.
20. The method of 17, further comprising:
directly generating waves of fluid motion in the recipient's scala tympani.
21. The method of claim 19, wherein the mechanical stimulation arrangement comprises a stapes prosthesis having a first end configured to be positioned abutting an opening in the semicircular canal, an actuator and a coupler connecting the actuator to the stapes prosthesis, wherein generating the fluid motion comprises:
receiving at the actuator electrical signals representing the processed sound signals;
generating vibration with the actuator based on the electrical signals; and
delivering the vibration to the fluid in the semicircular canal with the stapes prosthesis.
22. The method of claim 21, wherein the coupler comprises a first elongate component extending from the actuator, and a second component extending from the distal portion of the first component at an angle, wherein delivering the vibration to the fluid in the semicircular canal with the stapes prosthesis comprises:
actuating the first component to exert a force on the fluid in the semicircular canal.
23. The method of 17, further comprising:
delivering the mechanical stimulation signals to an actuator configured to generate vibration of the recipient's skull.
24. The method of claim 20, wherein the mechanical stimulation arrangement comprises a stapes prosthesis having a first end configured to be positioned abutting the round window in a recipient's cochlea, an actuator, and an elongate rod connecting the actuator to the stapes prosthesis, wherein generating the fluid motion further comprises:
receiving at the actuator electrical signals representing the processed sound signals;
generating vibration with the actuator based on the electrical signals; and
delivering with the stapes prosthesis the vibration to round window.
25. (canceled)
26. The method of claim 17, further comprising:
performing a frequency analysis of the received sound signal.
27-32. (canceled)
33. A bimodal hearing prosthesis for rehabilitating the hearing of a recipient, comprising:
means for receiving an acoustic sound signal;
means for processing the acoustic sound signal;
means for generating one or more of electrical stimulation signals and mechanical stimulation signals, based on the processed acoustic sound signal; and
means for stimulating the recipient's inner ear based on the generated stimulation signals.
34. The prosthesis of claim 33, wherein generating one or more of electrical stimulation signals and mechanical stimulation signals, comprises:
means for generating electrical stimulation signals, and
means for simultaneously generating mechanical stimulation signals.
35. The prosthesis of claim 33, further comprising:
means for directly generating fluid motion in one of the recipient's semicircular canals.
36. The prosthesis of claim 33, further comprising:
means for directly generating fluid motion in the recipient's scala tympani.
37. The prosthesis of claim 33, further comprising:
means for delivering the mechanical stimulation signals to an actuator configured to generate vibration of the recipient's skull.
38. The prosthesis of claim 33, further comprising:
means for performing a frequency analysis of the received sound signal.
US12/935,650 2008-03-31 2009-03-31 Bimodal hearing prosthesis Abandoned US20110029031A1 (en)

Priority Applications (3)

Application Number Priority Date Filing Date Title
US4118508P true 2008-03-31 2008-03-31
US12/935,650 US20110029031A1 (en) 2008-03-31 2009-03-31 Bimodal hearing prosthesis
PCT/US2009/038937 WO2009124038A1 (en) 2008-03-31 2009-03-31 A bimodal hearing prosthesis

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
US12/935,650 US20110029031A1 (en) 2008-03-31 2009-03-31 Bimodal hearing prosthesis

Publications (1)

Publication Number Publication Date
US20110029031A1 true US20110029031A1 (en) 2011-02-03

Family

ID=41117259

Family Applications (27)

Application Number Title Priority Date Filing Date
US12/167,825 Abandoned US20090248085A1 (en) 2008-03-31 2008-07-03 Tissue injection fixation system for a prosthetic device
US12/167,668 Active 2031-08-08 US8363871B2 (en) 2008-03-31 2008-07-03 Alternative mass arrangements for bone conduction devices
US12/167,851 Expired - Fee Related US8216287B2 (en) 2008-03-31 2008-07-03 Tangential force resistant coupling for a prosthetic device
US12/167,871 Expired - Fee Related US8852251B2 (en) 2008-03-31 2008-07-03 Mechanical fixation system for a prosthetic device
US12/167,796 Active 2031-10-13 US8401213B2 (en) 2008-03-31 2008-07-03 Snap-lock coupling system for a prosthetic device
US12/167,728 Expired - Fee Related US8526641B2 (en) 2008-03-31 2008-07-03 Customizable mass arrangements for bone conduction devices
US12/168,636 Abandoned US20090248155A1 (en) 2008-03-31 2008-07-07 Transcutaneous magnetic bone conduction device
US12/168,620 Active 2031-09-25 US8655002B2 (en) 2008-03-31 2008-07-07 Piercing conducted bone conduction device
US12/168,603 Active 2030-11-25 US8532321B2 (en) 2008-03-31 2008-07-07 Hearing device having one or more in-the-canal vibrating extensions
US12/168,653 Expired - Fee Related US8170252B2 (en) 2008-03-31 2008-07-07 Dual percutaneous anchors bone conduction device
US12/168,529 Active 2031-01-17 US8150083B2 (en) 2008-03-31 2008-07-07 Piezoelectric bone conduction device having enhanced transducer stroke
US12/168,572 Expired - Fee Related US8154173B2 (en) 2008-03-31 2008-07-07 Mechanically amplified piezoelectric transducer
US12/251,437 Abandoned US20090247813A1 (en) 2008-03-31 2008-10-14 Bone conduction hearing device having acoustic feedback reduction system
US12/251,443 Active 2031-05-28 US8831260B2 (en) 2008-03-31 2008-10-14 Bone conduction hearing device having acoustic feedback reduction system
US12/398,586 Active 2031-09-02 US8433081B2 (en) 2008-03-31 2009-03-05 Bone conduction devices generating tangentially-directed mechanical force using a linearly moving mass
US12/935,906 Active 2030-09-07 US8657734B2 (en) 2008-03-31 2009-03-31 Implantable universal docking station for prosthetic hearing devices
US12/935,887 Active 2031-09-22 US9955270B2 (en) 2008-03-31 2009-03-31 Bone conduction device fitting
US12/935,909 Abandoned US20110112462A1 (en) 2008-03-31 2009-03-31 Pharmaceutical agent delivery in a stimulating medical device
US12/935,901 Active 2032-02-14 US8945216B2 (en) 2008-03-31 2009-03-31 Objective fitting of a hearing prosthesis
US12/935,905 Active 2031-06-02 US8731205B2 (en) 2008-03-31 2009-03-31 Bone conduction device fitting
US12/935,650 Abandoned US20110029031A1 (en) 2008-03-31 2009-03-31 Bimodal hearing prosthesis
US12/935,895 Active 2029-09-01 US8532322B2 (en) 2008-03-31 2009-03-31 Bone conduction device for a single sided deaf recipient
US12/688,491 Active 2030-07-06 US8509461B2 (en) 2008-03-31 2010-01-15 Bone conduction devices generating tangentially-directed mechanical force using a rotationally moving mass
US13/965,718 Abandoned US20130345496A1 (en) 2008-03-31 2013-08-13 Bone Conduction Devices Generating Tangentially-Directed Mechanical Force Using a Rotationally Moving Mass
US14/072,398 Active US9602931B2 (en) 2008-03-31 2013-11-05 Bone conduction device
US15/464,090 Pending US20170257710A1 (en) 2008-03-31 2017-03-20 Bone conduction device
US15/958,212 Pending US20180376255A1 (en) 2008-03-31 2018-04-20 Bone conduction device fitting

Family Applications Before (20)

Application Number Title Priority Date Filing Date
US12/167,825 Abandoned US20090248085A1 (en) 2008-03-31 2008-07-03 Tissue injection fixation system for a prosthetic device
US12/167,668 Active 2031-08-08 US8363871B2 (en) 2008-03-31 2008-07-03 Alternative mass arrangements for bone conduction devices
US12/167,851 Expired - Fee Related US8216287B2 (en) 2008-03-31 2008-07-03 Tangential force resistant coupling for a prosthetic device
US12/167,871 Expired - Fee Related US8852251B2 (en) 2008-03-31 2008-07-03 Mechanical fixation system for a prosthetic device
US12/167,796 Active 2031-10-13 US8401213B2 (en) 2008-03-31 2008-07-03 Snap-lock coupling system for a prosthetic device
US12/167,728 Expired - Fee Related US8526641B2 (en) 2008-03-31 2008-07-03 Customizable mass arrangements for bone conduction devices
US12/168,636 Abandoned US20090248155A1 (en) 2008-03-31 2008-07-07 Transcutaneous magnetic bone conduction device
US12/168,620 Active 2031-09-25 US8655002B2 (en) 2008-03-31 2008-07-07 Piercing conducted bone conduction device
US12/168,603 Active 2030-11-25 US8532321B2 (en) 2008-03-31 2008-07-07 Hearing device having one or more in-the-canal vibrating extensions
US12/168,653 Expired - Fee Related US8170252B2 (en) 2008-03-31 2008-07-07 Dual percutaneous anchors bone conduction device
US12/168,529 Active 2031-01-17 US8150083B2 (en) 2008-03-31 2008-07-07 Piezoelectric bone conduction device having enhanced transducer stroke
US12/168,572 Expired - Fee Related US8154173B2 (en) 2008-03-31 2008-07-07 Mechanically amplified piezoelectric transducer
US12/251,437 Abandoned US20090247813A1 (en) 2008-03-31 2008-10-14 Bone conduction hearing device having acoustic feedback reduction system
US12/251,443 Active 2031-05-28 US8831260B2 (en) 2008-03-31 2008-10-14 Bone conduction hearing device having acoustic feedback reduction system
US12/398,586 Active 2031-09-02 US8433081B2 (en) 2008-03-31 2009-03-05 Bone conduction devices generating tangentially-directed mechanical force using a linearly moving mass
US12/935,906 Active 2030-09-07 US8657734B2 (en) 2008-03-31 2009-03-31 Implantable universal docking station for prosthetic hearing devices
US12/935,887 Active 2031-09-22 US9955270B2 (en) 2008-03-31 2009-03-31 Bone conduction device fitting
US12/935,909 Abandoned US20110112462A1 (en) 2008-03-31 2009-03-31 Pharmaceutical agent delivery in a stimulating medical device
US12/935,901 Active 2032-02-14 US8945216B2 (en) 2008-03-31 2009-03-31 Objective fitting of a hearing prosthesis
US12/935,905 Active 2031-06-02 US8731205B2 (en) 2008-03-31 2009-03-31 Bone conduction device fitting

Family Applications After (6)

Application Number Title Priority Date Filing Date
US12/935,895 Active 2029-09-01 US8532322B2 (en) 2008-03-31 2009-03-31 Bone conduction device for a single sided deaf recipient
US12/688,491 Active 2030-07-06 US8509461B2 (en) 2008-03-31 2010-01-15 Bone conduction devices generating tangentially-directed mechanical force using a rotationally moving mass
US13/965,718 Abandoned US20130345496A1 (en) 2008-03-31 2013-08-13 Bone Conduction Devices Generating Tangentially-Directed Mechanical Force Using a Rotationally Moving Mass
US14/072,398 Active US9602931B2 (en) 2008-03-31 2013-11-05 Bone conduction device
US15/464,090 Pending US20170257710A1 (en) 2008-03-31 2017-03-20 Bone conduction device
US15/958,212 Pending US20180376255A1 (en) 2008-03-31 2018-04-20 Bone conduction device fitting

Country Status (4)

Country Link
US (27) US20090248085A1 (en)
EP (6) EP2269241A1 (en)
CN (1) CN102047692B (en)
WO (23) WO2009121097A1 (en)

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20140105434A1 (en) * 2012-10-11 2014-04-17 Michael Goorevich Audio processing pipeline for auditory prosthesis having a common, and two or more stimulator-specific, frequency-analysis stages
WO2018154397A1 (en) * 2017-02-23 2018-08-30 Cochlear Limited Transducer placement for growth accommodation

Families Citing this family (122)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
AUPS318202A0 (en) 2002-06-26 2002-07-18 Cochlear Limited Parametric fitting of a cochlear implant
WO2005097255A1 (en) 2004-04-02 2005-10-20 Advanced Bionics Corporation Electric and acoustic stimulation fitting systems and methods
JP5548336B2 (en) 2004-06-15 2014-07-16 コクレア リミテッドCochlear Limited Automatic determination of evoked neural response threshold
US7801617B2 (en) 2005-10-31 2010-09-21 Cochlear Limited Automatic measurement of neural response concurrent with psychophysics measurement of stimulating device recipient
US8571675B2 (en) 2006-04-21 2013-10-29 Cochlear Limited Determining operating parameters for a stimulating medical device
WO2008014498A2 (en) * 2006-07-27 2008-01-31 Cochlear Americas Hearing device having a non-occluding in the-canal vibrating component
US7841446B2 (en) * 2007-04-30 2010-11-30 Kimberly-Clark Worldwide, Inc. Bandless hearing protector and method
SE0701242L (en) * 2007-05-24 2008-12-02 Cochlear Ltd Vibrator
DE102007031872B4 (en) * 2007-07-09 2009-11-19 Siemens Audiologische Technik Gmbh Hearing aid
US20090082817A1 (en) * 2007-07-20 2009-03-26 Cochlear Limited Coupling apparatus for a bone anchored hearing device
US8271101B2 (en) 2007-08-29 2012-09-18 Advanced Bionics Modular drug delivery system for minimizing trauma during and after insertion of a cochlear lead
WO2009029866A2 (en) 2007-08-29 2009-03-05 Advanced Bionics, Llc Minimizing trauma during and after insertion of a cochlear lead
EP2208367B1 (en) 2007-10-12 2017-09-27 Earlens Corporation Multifunction system and method for integrated hearing and communiction with noise cancellation and feedback management
US20090248085A1 (en) * 2008-03-31 2009-10-01 Cochlear Limited Tissue injection fixation system for a prosthetic device
US8144909B2 (en) * 2008-08-12 2012-03-27 Cochlear Limited Customization of bone conduction hearing devices
US9497555B2 (en) * 2008-08-16 2016-11-15 Envoy Medical Corporation Implantable middle ear transducer having improved frequency response
BRPI0919266A2 (en) 2008-09-22 2017-05-30 SoundBeam LLC device and method for transmitting an audio signal to a user, methods for manufacturing a device for transmitting an audio signal to the user, and for providing an audio device for a user, and device and method for transmitting a sound for a user. user having a tympanic membrane
DE102009014770A1 (en) * 2009-03-25 2010-09-30 Cochlear Ltd., Lane Cove vibrator
EP2252079A1 (en) * 2009-05-14 2010-11-17 Oticon A/S Bone anchored bone conductive hearing aid
WO2010138911A1 (en) 2009-05-29 2010-12-02 Otologics, Llc Implantable auditory stimulation system and method with offset implanted microphones
US8965021B2 (en) * 2009-06-09 2015-02-24 Dalhousie University Subcutaneous piezoelectric bone conduction hearing aid actuator and system
CN102458323B (en) * 2009-06-09 2015-05-06 达尔豪西大学 Subcutaneous piezoelectric bone conduction hearing aid actuator and system
US20120253105A1 (en) * 2009-10-21 2012-10-04 Woodwelding Ag Method of anchoring an acoustic element in a bone of the craniomaxillofacial region and acoustic element
WO2011059956A2 (en) * 2009-11-10 2011-05-19 Massachusetts Institute Of Technology Phased array buckling actuator
AU2010200485A1 (en) * 2010-02-10 2011-08-25 Cochlear Limited Percutaneous implant
US8594356B2 (en) * 2010-04-29 2013-11-26 Cochlear Limited Bone conduction device having limited range of travel
US8625828B2 (en) * 2010-04-30 2014-01-07 Cochlear Limited Hearing prosthesis having an on-board fitting system
EP2393309B1 (en) * 2010-06-07 2019-10-09 Oticon Medical A/S Device and method for applying a vibration signal to a human skull bone
EP2577996B1 (en) 2010-06-07 2014-08-13 Phonak AG Bone conduction hearing aid system
US8260430B2 (en) 2010-07-01 2012-09-04 Cochlear Limited Stimulation channel selection for a stimulating medical device
US8564080B2 (en) 2010-07-16 2013-10-22 Qualcomm Incorporated Magnetic storage element utilizing improved pinned layer stack
US9056204B2 (en) * 2010-10-29 2015-06-16 Cochlear Limited Universal implant
WO2012088187A2 (en) 2010-12-20 2012-06-28 SoundBeam LLC Anatomically customized ear canal hearing apparatus
US9313306B2 (en) 2010-12-27 2016-04-12 Rohm Co., Ltd. Mobile telephone cartilage conduction unit for making contact with the ear cartilage
WO2012090944A1 (en) * 2010-12-27 2012-07-05 ローム株式会社 Mobile telephone
JP5783352B2 (en) 2011-02-25 2015-09-24 株式会社ファインウェル Conversation system, conversation system ring, mobile phone ring, ring-type mobile phone, and voice listening method
US9479879B2 (en) 2011-03-23 2016-10-25 Cochlear Limited Fitting of hearing devices
US9107013B2 (en) 2011-04-01 2015-08-11 Cochlear Limited Hearing prosthesis with a piezoelectric actuator
US20120294466A1 (en) * 2011-05-18 2012-11-22 Stefan Kristo Temporary anchor for a hearing prosthesis
US10419861B2 (en) * 2011-05-24 2019-09-17 Cochlear Limited Convertibility of a bone conduction device
US8787608B2 (en) 2011-05-24 2014-07-22 Cochlear Limited Vibration isolation in a bone conduction device
WO2013179274A2 (en) * 2012-05-31 2013-12-05 Cochlear Limited Convertibility of a bone conduction device
US9313589B2 (en) 2011-07-01 2016-04-12 Cochlear Limited Method and system for configuration of a medical device that stimulates a human physiological system
US9210521B2 (en) * 2012-07-16 2015-12-08 Sophono, Inc. Abutment attachment systems, mechanisms, devices, components and methods for bone conduction hearing aids
US20130018218A1 (en) * 2011-07-14 2013-01-17 Sophono, Inc. Systems, Devices, Components and Methods for Bone Conduction Hearing Aids
US9258656B2 (en) 2011-12-09 2016-02-09 Sophono, Inc. Sound acquisition and analysis systems, devices and components for magnetic hearing aids
US9022917B2 (en) 2012-07-16 2015-05-05 Sophono, Inc. Magnetic spacer systems, devices, components and methods for bone conduction hearing aids
US9119010B2 (en) 2011-12-09 2015-08-25 Sophono, Inc. Implantable sound transmission device for magnetic hearing aid, and corresponding systems, devices and components
US20140121447A1 (en) * 2012-07-16 2014-05-01 Sophono, Inc Cover for Magnetic Implant in a Bone Conduction Hearing Aid System, and Corresponding Devices, Components and Methods
US9526810B2 (en) 2011-12-09 2016-12-27 Sophono, Inc. Systems, devices, components and methods for improved acoustic coupling between a bone conduction hearing device and a patient's head or skull
US9736601B2 (en) 2012-07-16 2017-08-15 Sophono, Inc. Adjustable magnetic systems, devices, components and methods for bone conduction hearing aids
US9179228B2 (en) 2011-12-09 2015-11-03 Sophono, Inc. Systems devices, components and methods for providing acoustic isolation between microphones and transducers in bone conduction magnetic hearing aids
US20130030242A1 (en) * 2011-07-26 2013-01-31 Michael R. Ruehring Dog anxiety relief bone conduction audio device, system
US20130090518A1 (en) * 2011-10-11 2013-04-11 Göran Björn Bone conduction implant
US9301068B2 (en) 2011-10-19 2016-03-29 Cochlear Limited Acoustic prescription rule based on an in situ measured dynamic range
US9167361B2 (en) * 2011-11-22 2015-10-20 Cochlear Limited Smoothing power consumption of an active medical device
AU2015267319B2 (en) * 2014-05-27 2018-03-22 Sophono, Inc. Systems, devices, components and methods for reducing feedback between microphones and transducers in bone conduction magnetic hearing devices
EP2795927B1 (en) * 2011-12-22 2016-04-06 Vibrant Med-el Hearing Technology GmbH Magnet arrangement for bone conduction hearing implant
US9241205B2 (en) * 2011-12-27 2016-01-19 Kyocera Corporation Vibration device, sound generator, speaker system, and electronic device
CN106879080A (en) 2012-01-20 2017-06-20 罗姆股份有限公司 Mobile phone, cartilage conduction vibration source device, listening device, communicator
US8891795B2 (en) * 2012-01-31 2014-11-18 Cochlear Limited Transcutaneous bone conduction device vibrator having movable magnetic mass
US9339649B2 (en) 2012-03-12 2016-05-17 The Hospital For Sick Children Implantable cochlear systems with intracochlear electrode array for balance stabilization
US9462365B1 (en) 2012-03-14 2016-10-04 Google Inc. Structure and manufacture of bone-conduction transducer
JP5812926B2 (en) * 2012-04-12 2015-11-17 京セラ株式会社 electronics
US20130281764A1 (en) * 2012-04-19 2013-10-24 Göran Björn Transcutaneous bone conduction device
JP6017828B2 (en) * 2012-05-02 2016-11-02 京セラ株式会社 Electronic device, control method, and control program
WO2014003160A1 (en) 2012-06-29 2014-01-03 ローム株式会社 Stereo earphone
DK2870781T3 (en) * 2012-07-09 2019-07-22 Med El Elektromedizinische Geraete Gmbh Electromagnetic bone cord hearing device
US9049527B2 (en) * 2012-08-28 2015-06-02 Cochlear Limited Removable attachment of a passive transcutaneous bone conduction device with limited skin deformation
US9031274B2 (en) 2012-09-06 2015-05-12 Sophono, Inc. Adhesive bone conduction hearing device
US9049515B2 (en) * 2012-10-08 2015-06-02 Keith Allen Clow Wireless communication device
CN104798382B (en) * 2012-12-21 2017-11-07 唯听助听器公司 The method of hearing aid assembly system and assembling hearing aid device system
US20140179985A1 (en) * 2012-12-21 2014-06-26 Marcus ANDERSSON Prosthesis adapter
US20140270291A1 (en) * 2013-03-15 2014-09-18 Mark C. Flynn Fitting a Bilateral Hearing Prosthesis System
US9516434B2 (en) 2013-05-09 2016-12-06 Cochlear Limited Medical device coupling arrangement
US9895097B2 (en) 2013-05-13 2018-02-20 Ear and Skull Base Center, P.C. Systems and methods for delivering bone conduction stimuli to and for measuring gravitation receptor functions of the inner ear
CA2911559C (en) * 2013-05-13 2018-08-21 Ear and Skull Base Center, P.C. Systems and methods for delivering bone conduction stimuli to and for measuring gravitation receptor functions of the inner ear
CN105307719B (en) 2013-05-30 2018-05-29 格雷厄姆·H.·克雷西 Local nerve stimulation instrument
EP3036917A1 (en) * 2013-08-19 2016-06-29 Advanced Bionics AG Device and method for neural cochlea stimulation
WO2015025829A1 (en) 2013-08-23 2015-02-26 ローム株式会社 Portable telephone
US9554223B2 (en) 2013-08-28 2017-01-24 Cochlear Limited Devices for enhancing transmissions of stimuli in auditory prostheses
US9949712B1 (en) * 2013-09-06 2018-04-24 John William Millard Apparatus and method for measuring the sound transmission characteristics of the central nervous system volume of humans
US10455336B2 (en) * 2013-10-11 2019-10-22 Cochlear Limited Devices for enhancing transmissions of stimuli in auditory prostheses
US20150110322A1 (en) * 2013-10-23 2015-04-23 Marcus ANDERSSON Contralateral sound capture with respect to stimulation energy source
EP3062491B1 (en) 2013-10-24 2019-02-20 FINEWELL Co., Ltd. Bracelet-type transmission/reception device and bracelet-type notification device
DE102013112319A1 (en) * 2013-11-08 2015-05-13 Cortec Gmbh Holding device for the body-external transmitter unit
EP3085109B1 (en) * 2013-12-16 2018-10-31 Sonova AG Method and apparatus for fitting a hearing device
EP2897378A1 (en) * 2014-01-21 2015-07-22 Oticon Medical A/S Hearing aid device using dual electromechanical vibrator
EP3110501B1 (en) 2014-02-28 2019-06-19 Advanced Bionics AG Systems for facilitating post-implant acoustic-only operation of an electro-acoustic stimulation ("eas") sound processor
US10034103B2 (en) 2014-03-18 2018-07-24 Earlens Corporation High fidelity and reduced feedback contact hearing apparatus and methods
EP3550857A1 (en) * 2014-03-28 2019-10-09 Oticon Medical A/S Magnetic means assembly for bone conducting hearing aid
JP2017513066A (en) 2014-04-07 2017-05-25 ベーリンガー インゲルハイム インターナショナル ゲゼルシャフト ミット ベシュレンクテル ハフツング Method, electronic device, inhalation training system and information storage medium for training and / or controlling the inhalation process of a patient
EA033261B1 (en) * 2014-04-07 2019-09-30 Бёрингер Ингельхайм Интернациональ Гмбх Inhalation training device and system for practicing an inhalation process
US9998837B2 (en) 2014-04-29 2018-06-12 Cochlear Limited Percutaneous vibration conductor
GB201409547D0 (en) * 2014-05-29 2014-07-16 Gill Instr Ltd An electroacoustic transducer
US9800982B2 (en) * 2014-06-18 2017-10-24 Cochlear Limited Electromagnetic transducer with expanded magnetic flux functionality
US20150382114A1 (en) * 2014-06-25 2015-12-31 Marcus ANDERSSON System for adjusting magnetic retention force in auditory prostheses
US9960340B2 (en) 2014-08-15 2018-05-01 Thorlabs, Inc. Amplified piezo actuator with coarse adjustment
JP6551919B2 (en) 2014-08-20 2019-07-31 株式会社ファインウェル Watch system, watch detection device and watch notification device
US10469963B2 (en) * 2014-08-28 2019-11-05 Cochlear Limited Suspended components in auditory prostheses
WO2016063133A1 (en) * 2014-10-20 2016-04-28 Cochlear Limited Control button configurations for auditory prostheses
KR20190045397A (en) * 2014-12-18 2019-05-02 파인웰 씨오., 엘티디 Cartilage conduction hearing device using an electromagnetic vibration unit, and electromagnetic vibration unit
CN105310826B (en) * 2015-03-12 2017-10-24 汪勇 A kind of skin listens acoustic device and its listens method for acoustic
TWI609589B (en) * 2015-05-14 2017-12-21 陳光超 Hearing auxiliary device and hearing auxiliary processing method
CN107683162B (en) 2015-05-28 2019-03-29 领先仿生公司 Cochlear implant and the method for keeping its MRI compatible, cochlear implant system
US9992584B2 (en) * 2015-06-09 2018-06-05 Cochlear Limited Hearing prostheses for single-sided deafness
CN108028997A (en) * 2015-09-18 2018-05-11 Med-El电气医疗器械有限公司 Osteoacusis transducer system with adjustable retentivity
US10412510B2 (en) 2015-09-25 2019-09-10 Cochlear Limited Bone conduction devices utilizing multiple actuators
WO2017059240A1 (en) 2015-10-02 2017-04-06 Earlens Corporation Drug delivery customized ear canal apparatus
WO2017086968A1 (en) 2015-11-19 2017-05-26 Halliburton Energy Services, Inc. Downhole piezoelectric acoustic transducer
US9967685B2 (en) * 2015-12-16 2018-05-08 Cochlear Limited Bone conduction skin interface
US10009698B2 (en) * 2015-12-16 2018-06-26 Cochlear Limited Bone conduction device having magnets integrated with housing
WO2017105511A1 (en) 2015-12-18 2017-06-22 Advanced Bionics Ag Cochlear implants having mri-compatible magnet apparatus
WO2017116791A1 (en) 2015-12-30 2017-07-06 Earlens Corporation Light based hearing systems, apparatus and methods
US10123138B2 (en) 2016-07-26 2018-11-06 Cochlear Limited Microphone isolation in a bone conduction device
EP3293985A1 (en) * 2016-09-12 2018-03-14 Sonion Nederland B.V. Receiver with integrated membrane movement detection
US20180124530A1 (en) * 2016-10-28 2018-05-03 Tommy BERGS Passive integrity management of an implantable device
DE102017105529A1 (en) * 2017-03-15 2018-09-20 Epcos Ag Garment and use of the garment
US10419843B1 (en) * 2017-04-18 2019-09-17 Facebook Technologies, Llc Bone conduction transducer array for providing audio
WO2019058330A1 (en) * 2017-09-22 2019-03-28 Cochlear Limited Trans middle ear-inner ear fluid flow implementations
WO2019155374A1 (en) * 2018-02-06 2019-08-15 Cochlear Limited Prosthetic cognitive ability increaser
WO2019159037A1 (en) * 2018-02-13 2019-08-22 Cochlear Limited Intra-operative determination of vibratory coupling efficiency

Citations (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5047994A (en) * 1989-05-30 1991-09-10 Center For Innovative Technology Supersonic bone conduction hearing aid and method
US6099462A (en) * 1998-02-16 2000-08-08 Awengen; Daniel F. Implantable hearing aid and method for implanting the same
US6537199B1 (en) * 1999-07-26 2003-03-25 Phonak Ag Arrangement for mechanical coupling of a driver to a coupling site of the ossicular chain
US6554861B2 (en) * 1999-01-19 2003-04-29 Gyrus Ent L.L.C. Otologic prosthesis
US20040039244A1 (en) * 2001-09-06 2004-02-26 Kai Kroll Method for creating a coupling between a device and an ear structure in an implantable hearing assistance device
US6754537B1 (en) * 1999-05-14 2004-06-22 Advanced Bionics Corporation Hybrid implantable cochlear stimulator hearing aid system
US20050020873A1 (en) * 2003-07-23 2005-01-27 Epic Biosonics Inc. Totally implantable hearing prosthesis
US6942696B1 (en) * 2004-04-28 2005-09-13 Clarity Corporation Ossicular prosthesis adjusting device
US20060161255A1 (en) * 2002-12-30 2006-07-20 Andrej Zarowski Implantable hearing system
US20060233409A1 (en) * 2005-04-15 2006-10-19 Siemens Audiologische Technik Gmbh Hearing aid
US20060287690A1 (en) * 2004-05-10 2006-12-21 Cochlear Limited Simultaneous delivery of electrical and acoustical stimulation in a hearing prosthesis
US20070083078A1 (en) * 2005-10-06 2007-04-12 Easter James R Implantable transducer with transverse force application
US20070213788A1 (en) * 2003-09-19 2007-09-13 Osberger Mary J Electrical stimulation of the inner ear in patients with unilateral hearing loss
US20080188707A1 (en) * 2004-11-30 2008-08-07 Hans Bernard Implantable Actuator For Hearing Aid Applications
US7651460B2 (en) * 2004-03-22 2010-01-26 The Board Of Regents Of The University Of Oklahoma Totally implantable hearing system

Family Cites Families (251)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US245555A (en) 1881-08-09 Ohaeles h
US41595A (en) 1864-02-16 Improvement in vyagon-brakes
US2045427A (en) * 1933-05-24 1936-06-23 Sonotone Corp Bone-conduction hearing-aid
US2045404A (en) * 1933-05-24 1936-06-23 Sonotone Corp Piezoelectric vibrator device
US2045403A (en) * 1933-05-24 1936-06-23 Sonotone Corp Piezoelectric device
US2239550A (en) * 1939-11-20 1941-04-22 Aurex Corp Bone conduction hearing device
US3104049A (en) * 1959-12-30 1963-09-17 Ibm High purity vacuum systems
US3733445A (en) * 1967-07-03 1973-05-15 Dyna Magnetic Devices Inc Inertial reaction transducers
US3594514A (en) * 1970-01-02 1971-07-20 Medtronic Inc Hearing aid with piezoelectric ceramic element
US3809829A (en) 1973-01-16 1974-05-07 Sonotone Corp Acoustic cros hearing aid
US4006321A (en) * 1974-02-20 1977-02-01 Industrial Research Products, Inc. Transducer coupling system
US4025964A (en) * 1976-07-30 1977-05-31 The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration Magnetic electrical connectors for biomedical percutaneous implants
US4291203A (en) * 1979-09-11 1981-09-22 Gaspare Bellafiore Hearing aid device
US4352960A (en) * 1980-09-30 1982-10-05 Baptist Medical Center Of Oklahoma, Inc. Magnetic transcutaneous mount for external device of an associated implant
US4407389A (en) * 1981-01-19 1983-10-04 Johnson Rubein V Vented acoustic ear mold for hearing aids
JPH0312000Y2 (en) * 1981-04-20 1991-03-22
US4419995A (en) * 1981-09-18 1983-12-13 Hochmair Ingeborg Single channel auditory stimulation system
SE431705B (en) * 1981-12-01 1984-02-20 Bo Hakansson Coupling, foretredesvis intended for mechanical transmission of audio data to be the leg of a hearing-impaired person
US4504967A (en) * 1982-12-16 1985-03-12 The Marmon Group, Inc. Method and apparatus for damping spurious vibration in spring reverberation units
JPS59178986A (en) 1983-03-28 1984-10-11 Nec Corp Mechanical amplifying mechanism
US4628907A (en) * 1984-03-22 1986-12-16 Epley John M Direct contact hearing aid apparatus
SE447947B (en) * 1985-05-10 1986-12-22 Bo Hakansson A device for a hearing aid
US5015225A (en) * 1985-05-22 1991-05-14 Xomed, Inc. Implantable electromagnetic middle-ear bone-conduction hearing aid device
US4606329A (en) * 1985-05-22 1986-08-19 Xomed, Inc. Implantable electromagnetic middle-ear bone-conduction hearing aid device
US4612915A (en) * 1985-05-23 1986-09-23 Xomed, Inc. Direct bone conduction hearing aid device
US4791673A (en) * 1986-12-04 1988-12-13 Schreiber Simeon B Bone conduction audio listening device and method
JP2592615B2 (en) * 1987-09-16 1997-03-19 日本特殊陶業株式会社 Electrostrictive drive unit
DE3735137A1 (en) * 1987-10-16 1989-05-03 Siemens Ag Arrangement for post of drugs in an implantable medical geraet
JPH01290272A (en) 1988-05-18 1989-11-22 Tsuin Denki Kk Displacement magnifying device of laminated piezoelectric actuator
US4944301A (en) * 1988-06-16 1990-07-31 Cochlear Corporation Method for determining absolute current density through an implanted electrode
US4952835A (en) * 1988-12-27 1990-08-28 Ford Aerospace Corporation Double saggital push stroke amplifier
US4964106A (en) * 1989-04-14 1990-10-16 Edo Corporation, Western Division Flextensional sonar transducer assembly
DE3918086C1 (en) * 1989-06-02 1990-09-27 Hortmann Gmbh, 7449 Neckartenzlingen, De
US5052930A (en) * 1989-11-22 1991-10-01 Lodde Jean Pierre Dental implant and method of implantation
FR2659009A1 (en) 1990-03-02 1991-09-06 Tari Roger An assistive listening device comprising a hearing aid implanted, self-contained direct bone conduction.
JPH0456531A (en) * 1990-06-26 1992-02-24 Matsushita Electric Ind Co Ltd Voice input device
DE4104358C2 (en) * 1991-02-13 1992-11-19 Implex Gmbh, 7449 Neckartenzlingen, De
EP0587649A1 (en) * 1991-06-06 1994-03-23 Cochlear Pty. Ltd. Percutaneous connector
DE4133000C2 (en) * 1991-10-04 1993-11-18 Siegfried Dipl Ing Kipke Piezo-hydraulic module for conversion of tactile information
US5338287A (en) * 1991-12-23 1994-08-16 Miller Gale W Electromagnetic induction hearing aid device
JP3056866B2 (en) * 1992-02-17 2000-06-26 アルパイン株式会社 Automatic volume control system
US5245245A (en) * 1992-05-04 1993-09-14 Motorola, Inc. Mass-loaded cantilever vibrator
US5323468A (en) 1992-06-30 1994-06-21 Bottesch H Werner Bone-conductive stereo headphones
US5344494A (en) * 1993-01-21 1994-09-06 Smith & Nephew Richards, Inc. Method for cleaning porous and roughened surfaces on medical implants
US5471721A (en) * 1993-02-23 1995-12-05 Research Corporation Technologies, Inc. Method for making monolithic prestressed ceramic devices
US5909498A (en) * 1993-03-25 1999-06-01 Smith; Jerry R. Transducer device for use with communication apparatus
US5913815A (en) * 1993-07-01 1999-06-22 Symphonix Devices, Inc. Bone conducting floating mass transducers
US5800336A (en) * 1993-07-01 1998-09-01 Symphonix Devices, Inc. Advanced designs of floating mass transducers
US5554096A (en) * 1993-07-01 1996-09-10 Symphonix Implantable electromagnetic hearing transducer
US5460593A (en) * 1993-08-25 1995-10-24 Audiodontics, Inc. Method and apparatus for imparting low amplitude vibrations to bone and similar hard tissue
US5430801A (en) * 1993-12-14 1995-07-04 Hill; Frank C. Hearing aid
US5843093A (en) * 1994-02-09 1998-12-01 University Of Iowa Research Foundation Stereotactic electrode assembly
US5444324A (en) * 1994-07-25 1995-08-22 Western Atlas International, Inc. Mechanically amplified piezoelectric acoustic transducer
US5825894A (en) * 1994-08-17 1998-10-20 Decibel Instruments, Inc. Spatialization for hearing evaluation
SE503790C2 (en) * 1994-12-02 1996-09-02 P & B Res Ab Disengagement for implant coupling at hearing
SE503791C2 (en) * 1994-12-02 1996-09-02 P & B Res Ab Apparatus in hearing aid
US5683249A (en) * 1995-03-22 1997-11-04 Den-Mat Corporation Dental implant process and treated prosthetic
FR2734711B1 (en) 1995-05-31 1997-08-29 Bertin & Cie hearing aid comprising a cochlear implant
US5606621A (en) * 1995-06-14 1997-02-25 Siemens Hearing Instruments, Inc. Hybrid behind-the-ear and completely-in-canal hearing aid
US5949895A (en) * 1995-09-07 1999-09-07 Symphonix Devices, Inc. Disposable audio processor for use with implanted hearing devices
US5772575A (en) * 1995-09-22 1998-06-30 S. George Lesinski Implantable hearing aid
FR2740276B1 (en) 1995-10-20 1997-12-26 Cedrat Rech piezoactive actuator amplifies a stiffness HIGH
FR2740349B1 (en) * 1995-10-30 1997-11-21 Dynastar Skis Sa A vibration damping device intended to be mounted on a sports article
DE29724567U1 (en) * 1996-02-14 2003-01-16 Walter Lorenz Surgical Inc Bone fastener and instrument for inserting the bone fastener
US5805571A (en) 1996-03-19 1998-09-08 Zwan; Bryan J. Dynamic communication line analyzer apparatus and method
DE19618964C2 (en) * 1996-05-10 1999-12-16 Implex Hear Tech Ag Implantable positioning and fixing system for actuator and sensor implants
WO1997044987A1 (en) * 1996-05-24 1997-11-27 Lesinski S George Improved microphones for an implantable hearing aid
JP3680891B2 (en) * 1996-07-01 2005-08-10 セイコーエプソン株式会社 Optical scanning device
US6325755B1 (en) * 1997-08-07 2001-12-04 St. Croix Medical, Inc. Mountable transducer assembly with removable sleeve
US6001129A (en) 1996-08-07 1999-12-14 St. Croix Medical, Inc. Hearing aid transducer support
US5899847A (en) * 1996-08-07 1999-05-04 St. Croix Medical, Inc. Implantable middle-ear hearing assist system using piezoelectric transducer film
DK0836363T3 (en) 1996-10-01 2003-12-15 Phonak Ag Limits for sound impressions
AT403867B (en) * 1996-10-11 1998-06-25 Resound Viennatone Hoertechnol hearing Aid
US6010532A (en) * 1996-11-25 2000-01-04 St. Croix Medical, Inc. Dual path implantable hearing assistance device
US5771298A (en) * 1997-01-13 1998-06-23 Larson-Davis, Inc. Apparatus and method for simulating a human mastoid
US5999856A (en) * 1997-02-21 1999-12-07 St. Croix Medical, Inc. Implantable hearing assistance system with calibration and auditory response testing
US6033440A (en) * 1997-03-13 2000-03-07 Prosthetic Design, Inc. Adjustable pyramidal link plate assembly for a prosthetic limb
US5991419A (en) * 1997-04-29 1999-11-23 Beltone Electronics Corporation Bilateral signal processing prosthesis
US5781646A (en) * 1997-05-09 1998-07-14 Face; Samuel A. Multi-segmented high deformation piezoelectric array
SE514631C2 (en) 1997-06-06 2001-03-26 P & B Res Ab A device at implants for anchoring and energy transfer
US6315710B1 (en) * 1997-07-21 2001-11-13 St. Croix Medical, Inc. Hearing system with middle ear transducer mount
US6309410B1 (en) * 1998-08-26 2001-10-30 Advanced Bionics Corporation Cochlear electrode with drug delivery channel and method of making same
DE19739594C2 (en) * 1997-09-10 2001-09-06 Daimler Chrysler Ag Electrostrictive actuator
US6674867B2 (en) * 1997-10-15 2004-01-06 Belltone Electronics Corporation Neurofuzzy based device for programmable hearing aids
US6068590A (en) * 1997-10-24 2000-05-30 Hearing Innovations, Inc. Device for diagnosing and treating hearing disorders
SE513670C2 (en) * 1997-12-18 2000-10-16 Grogrunden Ab Nr 444 Bone anchored percutaneous penetration device
US6366863B1 (en) * 1998-01-09 2002-04-02 Micro Ear Technology Inc. Portable hearing-related analysis system
US6631295B2 (en) * 1998-02-13 2003-10-07 University Of Iowa Research Foundation System and method for diagnosing and/or reducing tinnitus
EP1057367B1 (en) * 1998-02-18 2008-01-09 Widex A/S A binaural digital hearing aid system
US6137889A (en) * 1998-05-27 2000-10-24 Insonus Medical, Inc. Direct tympanic membrane excitation via vibrationally conductive assembly
EP1308068A4 (en) * 1998-06-05 2007-05-02 St Croix Medical Inc Method and apparatus for reduced feedback in implantable hearing assistance systems
US6681022B1 (en) * 1998-07-22 2004-01-20 Gn Resound North Amerca Corporation Two-way communication earpiece
US6217508B1 (en) * 1998-08-14 2001-04-17 Symphonix Devices, Inc. Ultrasonic hearing system
DE19840211C1 (en) * 1998-09-03 1999-12-30 Implex Hear Tech Ag Transducer for partially or fully implantable hearing aid
US6039685A (en) * 1998-09-14 2000-03-21 St. Croix Medical, Inc. Ventable connector with seals
US6022509A (en) * 1998-09-18 2000-02-08 Johnson & Johnson Professional, Inc. Precision powder injection molded implant with preferentially leached texture surface and method of manufacture
SE516866C2 (en) * 1998-09-24 2002-03-12 Nobel Biocare Ab Bone anchor, has lateral support for absorbing lateral forces so that it can be stressed immediately after anchoring into position
US6463157B1 (en) * 1998-10-06 2002-10-08 Analytical Engineering, Inc. Bone conduction speaker and microphone
US6735318B2 (en) * 1998-12-30 2004-05-11 Kyungpook National University Industrial Collaboration Foundation Middle ear hearing aid transducer
JP2002534933A (en) * 1999-01-07 2002-10-15 サーノフ コーポレイション Hearing aid with a large diaphragm microphone element having a printed circuit board
US6496585B1 (en) * 1999-01-27 2002-12-17 Robert H. Margolis Adaptive apparatus and method for testing auditory sensitivity
JP3004644B1 (en) * 1999-03-03 2000-01-31 株式会社コミュータヘリコプタ先進技術研究所 Russia - Tablet - de of the flap drive unit
AU4712900A (en) * 1999-05-14 2000-12-05 Advanced Bionics Corporation Hybrid implantable cochlear stimulator hearing aid system
DE19948375B4 (en) 1999-10-07 2004-04-01 Phonak Ag Arrangement for mechanical coupling of a driver to a coupling site of the ossicular chain
US20020172386A1 (en) * 2000-06-02 2002-11-21 Erich Bayer Otoplasty for behind-the-ear hearing aids
US6554761B1 (en) * 1999-10-29 2003-04-29 Soundport Corporation Flextensional microphones for implantable hearing devices
US6629922B1 (en) * 1999-10-29 2003-10-07 Soundport Corporation Flextensional output actuators for surgically implantable hearing aids
US6231410B1 (en) * 1999-11-01 2001-05-15 Arctic Cat Inc. Controlled thrust steering system for watercraft
DE19961068C1 (en) * 1999-12-17 2001-01-25 Daimler Chrysler Ag Piezoelectric actuator system has two piezoelectric actuators connected in one half of clocked amplifier bridge circuit controlled via pulse-width modulated signal
CN1230224C (en) 1999-12-27 2005-12-07 阿尔萨公司 Osmotic beneficial agent delivery system
US6436028B1 (en) * 1999-12-28 2002-08-20 Soundtec, Inc. Direct drive movement of body constituent
US6940989B1 (en) * 1999-12-30 2005-09-06 Insound Medical, Inc. Direct tympanic drive via a floating filament assembly
US7266209B1 (en) * 2000-01-05 2007-09-04 David William House Cochlear implants with a stimulus in the human ultrasonic range and method for stimulating a cochlea
US6885753B2 (en) * 2000-01-27 2005-04-26 New Transducers Limited Communication device using bone conduction
TW511391B (en) * 2000-01-24 2002-11-21 New Transducers Ltd Transducer
SE516270C2 (en) * 2000-03-09 2001-12-10 Osseofon Ab Electromagnetic vibrator
DE20004499U1 (en) * 2000-03-14 2000-12-07 Daimler Chrysler Ag An aerodynamic airfoil having leading edge flap
DE10017332C2 (en) * 2000-04-07 2002-04-18 Daimler Chrysler Ag Piezoelectric operating device for controlling flaps on rotor blades of a helicopter
US7399282B2 (en) * 2000-05-19 2008-07-15 Baycrest Center For Geriatric Care System and method for objective evaluation of hearing using auditory steady-state responses
AU6194601A (en) * 2000-05-19 2001-11-26 Michael Sasha John System and method for objective evaluation of hearing using auditory steady-state responses
US6517476B1 (en) 2000-05-30 2003-02-11 Otologics Llc Connector for implantable hearing aid
AUPQ787500A0 (en) 2000-05-31 2000-06-22 Enersave Environmental Services Pty Ltd A power supply altering means
SE523123C2 (en) * 2000-06-02 2004-03-30 P & B Res Ab Hearing that works with the principle of bone conduction
SE514929C2 (en) 2000-06-02 2001-05-21 P & B Res Ab Vibrator for bone conduction and benledningshörapparater
SE0002072L (en) 2000-06-02 2001-05-21 P & B Res Ab Vibrator for bone conduction and benledningshörapparater
DE10031832C2 (en) * 2000-06-30 2003-04-30 Cochlear Ltd Hearing aid for rehabilitation of a hearing disorder
SE523765C2 (en) 2000-07-12 2004-05-18 Entific Medical Systems Ab Screw-shaped anchoring element for permanent anchoring of bone anchored hearing aid and ear and eye prostheses in the skull bone
US6631197B1 (en) * 2000-07-24 2003-10-07 Gn Resound North America Corporation Wide audio bandwidth transduction method and device
JP3745602B2 (en) * 2000-07-27 2006-02-15 インターナショナル・ビジネス・マシーンズ・コーポレーションInternational Business Maschines Corporation Body set type speaker device
DE10041726C1 (en) * 2000-08-25 2002-05-23 Implex Ag Hearing Technology I Implantable hearing system with means for measuring the coupling quality
US20020039427A1 (en) * 2000-10-04 2002-04-04 Timothy Whitwell Audio apparatus
CA2323983A1 (en) * 2000-10-19 2002-04-19 Universite De Sherbrooke Programmable neurostimulator
US7068793B2 (en) * 2000-11-02 2006-06-27 Yoon Joo Shim Method of automatically fitting hearing aid
AUPR148400A0 (en) * 2000-11-14 2000-12-07 Cochlear Limited Apparatus for delivery of pharmaceuticals to the cochlea
US6505076B2 (en) * 2000-12-08 2003-01-07 Advanced Bionics Corporation Water-resistant, wideband microphone subassembly
DE10062236C2 (en) * 2000-12-14 2003-11-27 Phonak Ag Staefa Fixation element for an implantable microphone
US6643378B2 (en) * 2001-03-02 2003-11-04 Daniel R. Schumaier Bone conduction hearing aid
US7166953B2 (en) * 2001-03-02 2007-01-23 Jon Heim Electroactive polymer rotary clutch motors
DE10114838A1 (en) * 2001-03-26 2002-10-10 Implex Ag Hearing Technology I Fully implantable hearing
US7616771B2 (en) * 2001-04-27 2009-11-10 Virginia Commonwealth University Acoustic coupler for skin contact hearing enhancement devices
SE523124C2 (en) 2001-06-21 2004-03-30 P & B Res Ab Coupling device for a two bone-anchored hearing aid
SE523125C2 (en) * 2001-06-21 2004-03-30 P & B Res Ab Vibrator for vibrationsalstring of bone-anchored hearing aids
SE523100C2 (en) * 2001-06-21 2004-03-30 P & B Res Ab Bone anchored hearing aid intended for the conduction of sound
AUPR604801A0 (en) * 2001-06-29 2001-07-26 Cochlear Limited Multi-electrode cochlear implant system with distributed electronics
US6775389B2 (en) * 2001-08-10 2004-08-10 Advanced Bionics Corporation Ear auxiliary microphone for behind the ear hearing prosthetic
GB0119652D0 (en) * 2001-08-11 2001-10-03 Stanmore Implants Worldwide Surgical implant
US20060018488A1 (en) * 2003-08-07 2006-01-26 Roar Viala Bone conduction systems and methods
US6786860B2 (en) * 2001-10-03 2004-09-07 Advanced Bionics Corporation Hearing aid design
US7127078B2 (en) * 2001-10-03 2006-10-24 Advanced Bionics Corporation Implanted outer ear canal hearing aid
US6879695B2 (en) * 2001-10-03 2005-04-12 Advanced Bionics Corporation Personal sound link module
US6840908B2 (en) 2001-10-12 2005-01-11 Sound Id System and method for remotely administered, interactive hearing tests
US20050171579A1 (en) * 2001-11-09 2005-08-04 Claudia Tasche Stimulating device
US20030112992A1 (en) * 2001-12-14 2003-06-19 Rapps Gary M. Self-retaining element for a behind-the-ear communication device
US7630507B2 (en) * 2002-01-28 2009-12-08 Gn Resound A/S Binaural compression system
US6879693B2 (en) * 2002-02-26 2005-04-12 Otologics, Llc. Method and system for external assessment of hearing aids that include implanted actuators
FR2836536B1 (en) * 2002-02-26 2004-05-14 Cedrat Technologies piezoelectric valve
US6626909B2 (en) * 2002-02-27 2003-09-30 Kingsley Richard Chin Apparatus and method for spine fixation
US7765005B2 (en) * 2004-02-12 2010-07-27 Greatbatch Ltd. Apparatus and process for reducing the susceptability of active implantable medical devices to medical procedures such as magnetic resonance imaging
US6838963B2 (en) * 2002-04-01 2005-01-04 Med-El Elektromedizinische Geraete Gmbh Reducing effects of magnetic and electromagnetic fields on an implant's magnet and/or electronics
SE522164C2 (en) 2002-05-10 2004-01-20 Osseofon Ab Arrangement for electromagnetic rapper
US7465277B2 (en) * 2002-05-23 2008-12-16 Tympany, Llc System and methods for conducting multiple diagnostic hearing tests
FR2841429B1 (en) * 2002-06-21 2005-11-11 Mxm Hearing aid device for the rehabilitation of patients with partial neurosensory deaths
WO2004024212A2 (en) 2002-09-10 2004-03-25 Vibrant Med-El Hearing Technology Gmbh Implantable medical devices with multiple transducers
JP2004166174A (en) 2002-09-20 2004-06-10 Junichi Suzuki External auditory meatus insertion type bone conduction receiver, and external auditory meatus insertion type bone conduction hearing aid
KR100390003B1 (en) 2002-10-02 2003-06-20 Joo Bae Kim Bone-conduction speaker using vibration plate and mobile telephone using the same
WO2004030572A2 (en) * 2002-10-02 2004-04-15 Otologics Llc Retention apparatus for an external portion of a semi-implantable hearing aid
FR2845440B1 (en) * 2002-10-03 2006-03-31 Sagem Device for controlling valves
AU2003284018A1 (en) * 2002-10-04 2004-05-04 Microchips, Inc. Medical device for neural stimulation and controlled drug delivery
WO2004033036A2 (en) * 2002-10-04 2004-04-22 Microchips, Inc. Medical device for controlled drug delivery and cardiac monitoring and/or stimulation
US7331961B2 (en) * 2003-01-10 2008-02-19 Abdou M Samy Plating system for bone fixation and subsidence and method of implantation
WO2004034934A2 (en) * 2002-10-15 2004-04-29 Ludwig Arwed Implant for implanting under the scalp for the magnetic fixing of a prosthesis
WO2004050056A1 (en) 2002-11-29 2004-06-17 Cochlear Limited Cochlear implant drug delivery device
US7033313B2 (en) * 2002-12-11 2006-04-25 No. 182 Corporate Ventures Ltd. Surgically implantable hearing aid
FR2850217A1 (en) * 2003-01-17 2004-07-23 Cedrat Technologies piezoactive actuator displacement is amplified amortized
GB2398969B (en) 2003-02-27 2006-07-05 Ericsson Telefon Ab L M Message management
US7045932B2 (en) * 2003-03-04 2006-05-16 Exfo Burleigh Prod Group Inc Electromechanical translation apparatus
JP2004274593A (en) * 2003-03-11 2004-09-30 Temuko Japan:Kk Bone conduction speaker
US7486798B2 (en) * 2003-04-08 2009-02-03 Mayur Technologies, Inc. Method and apparatus for tooth bone conduction microphone
US6787860B1 (en) * 2003-05-01 2004-09-07 Macronix International Co., Ltd. Apparatus and method for inhibiting dummy cell over erase
US7599508B1 (en) * 2003-05-08 2009-10-06 Advanced Bionics, Llc Listening device cap
US6999818B2 (en) * 2003-05-23 2006-02-14 Greatbatch-Sierra, Inc. Inductor capacitor EMI filter for human implant applications
SE526548C2 (en) 2003-05-30 2005-10-04 Entific Medical Systems Ab A device at implants
JP4939935B2 (en) * 2003-06-24 2012-05-30 ジーエヌ リザウンド エー/エスGn Resound A/S Binaural hearing aid system with matched acoustic processing
SE526099C2 (en) 2003-06-30 2005-07-05 Entific Medical Systems Ab Device for wireless signal and energy transmission for medical implants
DE10331956C5 (en) * 2003-07-16 2010-11-18 Siemens Audiologische Technik Gmbh Hearing aid and method for operating a hearing aid with a microphone system, in which different Richtcharaktistiken are adjustable
GB0321617D0 (en) * 2003-09-10 2003-10-15 New Transducers Ltd Audio apparatus
US20050059970A1 (en) * 2003-09-17 2005-03-17 Eric Kolb Bone fixation systems
SE525631C2 (en) * 2003-09-19 2005-03-22 P & B Res Ab Method and device for reducing the resonant frequency
SE527006C2 (en) 2003-10-22 2005-12-06 Entific Medical Systems Ab Device to cure or reduce stuttering
US7214179B2 (en) * 2004-04-01 2007-05-08 Otologics, Llc Low acceleration sensitivity microphone
US20050101830A1 (en) * 2003-11-07 2005-05-12 Easter James R. Implantable hearing aid transducer interface
US7241258B2 (en) * 2003-11-07 2007-07-10 Otologics, Llc Passive vibration isolation of implanted microphone
US7840020B1 (en) * 2004-04-01 2010-11-23 Otologics, Llc Low acceleration sensitivity microphone
US7021676B2 (en) * 2004-05-10 2006-04-04 Patrik Westerkull Connector system
US7160244B2 (en) * 2004-05-10 2007-01-09 Patrik Westerkull Arrangement for a hearing aid
US20060098833A1 (en) * 2004-05-28 2006-05-11 Juneau Roger P Self forming in-the-ear hearing aid
US7344564B2 (en) 2004-06-08 2008-03-18 Spinal Generations, Llc Expandable spinal stabilization device
JP5548336B2 (en) 2004-06-15 2014-07-16 コクレア リミテッドCochlear Limited Automatic determination of evoked neural response threshold
US7421087B2 (en) * 2004-07-28 2008-09-02 Earlens Corporation Transducer for electromagnetic hearing devices
US20060041318A1 (en) * 2004-08-19 2006-02-23 Shannon Donald T Laminar skin-bone fixation transcutaneous implant and method for use thereof
US7376237B2 (en) * 2004-09-02 2008-05-20 Oticon A/S Vibrator for bone-conduction hearing
US7065223B2 (en) * 2004-09-09 2006-06-20 Patrik Westerkull Hearing-aid interconnection system
US7302071B2 (en) * 2004-09-15 2007-11-27 Schumaier Daniel R Bone conduction hearing assistance device
US7867160B2 (en) * 2004-10-12 2011-01-11 Earlens Corporation Systems and methods for photo-mechanical hearing transduction
US20060082158A1 (en) * 2004-10-15 2006-04-20 Schrader Jeffrey L Method and device for supplying power from acoustic energy
KR100610192B1 (en) * 2004-10-27 2006-08-09 경북대학교 산학협력단 piezoelectric oscillator
US7116794B2 (en) * 2004-11-04 2006-10-03 Patrik Westerkull Hearing-aid anchoring element
FI20041625A (en) * 2004-12-17 2006-06-18 Nokia Corp A method for converting an ear canal signal, an ear canal converter, and a headset
US8885837B2 (en) 2005-01-27 2014-11-11 Cochlear Limited Implantable medical device
SE528279C2 (en) 2005-02-21 2006-10-10 Entific Medical Systems Ab Vibrator for bone conduction hearing aid
EP1858457B1 (en) * 2005-02-24 2011-11-02 Morphogeny, LLC Linked slideable and interlockable rotatable components
WO2006091808A2 (en) * 2005-02-25 2006-08-31 Medical Research Products-B, Inc. Fully implantable hearing aid system
US8241224B2 (en) * 2005-03-16 2012-08-14 Sonicom, Inc. Test battery system and method for assessment of auditory function
US20060211910A1 (en) * 2005-03-18 2006-09-21 Patrik Westerkull Microphone system for bone anchored bone conduction hearing aids
US8021526B2 (en) 2005-04-05 2011-09-20 G.B.D. Corp Household appliances which utilize an electrolyzer and electrolyzer that may be used therein
DE102006026288A1 (en) * 2005-06-09 2007-01-04 Siegert, Ralf, Prof. Dr. Dr.med. Bone conduction hearing aid is held by U arranged magnet pair with open end facing magnets implanted in skull
DE102005031249A1 (en) * 2005-07-04 2007-04-05 Schäfer, Günter Willy Dental full or partial implant, has jaw anchorages with head area supporting implant, where implant is held in jaw bone by anchorages and retains movement path axially in direction of jaw bone in mounted condition
US7822215B2 (en) * 2005-07-07 2010-10-26 Face International Corp Bone-conduction hearing-aid transducer having improved frequency response
DE102005061150A1 (en) 2005-07-23 2007-02-01 Kurz, Hans-Rainer Device and method for configuring a hearing aid
US8184840B2 (en) * 2005-08-22 2012-05-22 3Win N.V. Combined set comprising a vibrator actuator and an implantable device
US20070053536A1 (en) * 2005-08-24 2007-03-08 Patrik Westerkull Hearing aid system
US7796771B2 (en) * 2005-09-28 2010-09-14 Roberta A. Calhoun Bone conduction hearing aid fastening device
WO2007052251A2 (en) 2005-10-31 2007-05-10 Audiodent Israel Ltd. Miniature bio-compatible piezoelectric transducer apparatus
US8005247B2 (en) * 2005-11-14 2011-08-23 Oticon A/S Power direct bone conduction hearing aid system
US7869610B2 (en) * 2005-11-30 2011-01-11 Knowles Electronics, Llc Balanced armature bone conduction shaker
US7670278B2 (en) * 2006-01-02 2010-03-02 Oticon A/S Hearing aid system
US8246532B2 (en) * 2006-02-14 2012-08-21 Vibrant Med-El Hearing Technology Gmbh Bone conductive devices for improving hearing
TWI318539B (en) * 2006-05-24 2009-12-11 Univ Chung Yuan Christian Implant bone conduction hearing aids
US9026205B2 (en) * 2006-05-25 2015-05-05 Cochlear Limited Stimulating device
US7796769B2 (en) 2006-05-30 2010-09-14 Sonitus Medical, Inc. Methods and apparatus for processing audio signals
AR062036A1 (en) * 2006-07-24 2008-08-10 Med El Elektromed Geraete Gmbh Moving coil actuator for middle ear implants
WO2008014498A2 (en) 2006-07-27 2008-01-31 Cochlear Americas Hearing device having a non-occluding in the-canal vibrating component
WO2008121944A1 (en) * 2007-03-29 2008-10-09 Vibrant Med-El Hearing Technology Gmbh Implantable auditory stimulation systems having a transducer and a transduction medium
SE0701242L (en) * 2007-05-24 2008-12-02 Cochlear Ltd Vibrator
US20090082817A1 (en) * 2007-07-20 2009-03-26 Cochlear Limited Coupling apparatus for a bone anchored hearing device
US9071914B2 (en) * 2007-08-14 2015-06-30 Insound Medical, Inc. Combined microphone and receiver assembly for extended wear canal hearing devices
US8433080B2 (en) * 2007-08-22 2013-04-30 Sonitus Medical, Inc. Bone conduction hearing device with open-ear microphone
EP2201621A1 (en) * 2007-10-25 2010-06-30 Massachusetts Institute of Technology Strain amplification devices and methods
DK2066140T3 (en) * 2007-11-28 2016-04-18 Oticon Medical As Method of mounting a bone anchored hearing aid for a user and bone anchored bone conducting hearing system.
EP2083582B1 (en) * 2008-01-28 2013-08-21 Oticon Medical A/S Bone conducting hearing aid with connection
SE533430C2 (en) * 2008-02-20 2010-09-28 Osseofon Ab implantable vibrator
WO2009117767A1 (en) 2008-03-25 2009-10-01 Cochlear Limited Electronic component configuration
US20100137675A1 (en) * 2008-03-31 2010-06-03 Cochlear Limited Bone conduction devices generating tangentially-directed mechanical force using a rotationally moving mass
US20090248085A1 (en) * 2008-03-31 2009-10-01 Cochlear Limited Tissue injection fixation system for a prosthetic device
US9445213B2 (en) * 2008-06-10 2016-09-13 Qualcomm Incorporated Systems and methods for providing surround sound using speakers and headphones
US8396239B2 (en) * 2008-06-17 2013-03-12 Earlens Corporation Optical electro-mechanical hearing devices with combined power and signal architectures
US8144909B2 (en) 2008-08-12 2012-03-27 Cochlear Limited Customization of bone conduction hearing devices
DE102009014770A1 (en) * 2009-03-25 2010-09-30 Cochlear Ltd., Lane Cove vibrator
EP2252079A1 (en) * 2009-05-14 2010-11-17 Oticon A/S Bone anchored bone conductive hearing aid
US8594356B2 (en) 2010-04-29 2013-11-26 Cochlear Limited Bone conduction device having limited range of travel
DE102010028460B4 (en) * 2010-04-30 2014-01-23 Globalfoundries Dresden Module One Limited Liability Company & Co. Kg A method of fabricating a semiconductor device having a reduced defect rate in contacts, comprising replacement gate electrode structures using an intermediate cladding layer

Patent Citations (16)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5047994A (en) * 1989-05-30 1991-09-10 Center For Innovative Technology Supersonic bone conduction hearing aid and method
US6099462A (en) * 1998-02-16 2000-08-08 Awengen; Daniel F. Implantable hearing aid and method for implanting the same
US6554861B2 (en) * 1999-01-19 2003-04-29 Gyrus Ent L.L.C. Otologic prosthesis
US20040230254A1 (en) * 1999-05-14 2004-11-18 Harrison William Vanbrooks Hybrid implantable cochlear stimulator hearing aid system
US6754537B1 (en) * 1999-05-14 2004-06-22 Advanced Bionics Corporation Hybrid implantable cochlear stimulator hearing aid system
US6537199B1 (en) * 1999-07-26 2003-03-25 Phonak Ag Arrangement for mechanical coupling of a driver to a coupling site of the ossicular chain
US20040039244A1 (en) * 2001-09-06 2004-02-26 Kai Kroll Method for creating a coupling between a device and an ear structure in an implantable hearing assistance device
US20060161255A1 (en) * 2002-12-30 2006-07-20 Andrej Zarowski Implantable hearing system
US20050020873A1 (en) * 2003-07-23 2005-01-27 Epic Biosonics Inc. Totally implantable hearing prosthesis
US20070213788A1 (en) * 2003-09-19 2007-09-13 Osberger Mary J Electrical stimulation of the inner ear in patients with unilateral hearing loss
US7651460B2 (en) * 2004-03-22 2010-01-26 The Board Of Regents Of The University Of Oklahoma Totally implantable hearing system
US6942696B1 (en) * 2004-04-28 2005-09-13 Clarity Corporation Ossicular prosthesis adjusting device
US20060287690A1 (en) * 2004-05-10 2006-12-21 Cochlear Limited Simultaneous delivery of electrical and acoustical stimulation in a hearing prosthesis
US20080188707A1 (en) * 2004-11-30 2008-08-07 Hans Bernard Implantable Actuator For Hearing Aid Applications
US20060233409A1 (en) * 2005-04-15 2006-10-19 Siemens Audiologische Technik Gmbh Hearing aid
US20070083078A1 (en) * 2005-10-06 2007-04-12 Easter James R Implantable transducer with transverse force application

Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20140105434A1 (en) * 2012-10-11 2014-04-17 Michael Goorevich Audio processing pipeline for auditory prosthesis having a common, and two or more stimulator-specific, frequency-analysis stages
US8873770B2 (en) * 2012-10-11 2014-10-28 Cochlear Limited Audio processing pipeline for auditory prosthesis having a common, and two or more stimulator-specific, frequency-analysis stages
US20150172836A1 (en) * 2012-10-11 2015-06-18 Cochlear Limited Audio processing pipeline for auditory prosthesis having a common, and two or more stimulator-specific, frequency-analysis stages
US9510114B2 (en) * 2012-10-11 2016-11-29 Cochlear Limited Audio processing pipeline for auditory prosthesis having a common, and two or more stimulator-specific, frequency-analysis stages
US9949042B2 (en) 2012-10-11 2018-04-17 Cochlear Limited Audio processing pipeline for auditory prosthesis having a common, and two or more stimulator-specific, frequency-analysis stages
WO2018154397A1 (en) * 2017-02-23 2018-08-30 Cochlear Limited Transducer placement for growth accommodation

Also Published As

Publication number Publication date
WO2009124035A3 (en) 2009-12-30
WO2009121101A9 (en) 2009-11-05
US8433081B2 (en) 2013-04-30
US20090247811A1 (en) 2009-10-01
WO2009121101A1 (en) 2009-10-08
US20090245557A1 (en) 2009-10-01
WO2009121106A1 (en) 2009-10-08
WO2009124042A2 (en) 2009-10-08
WO2009121114A1 (en) 2009-10-08
CN102047692A (en) 2011-05-04
US20100121134A1 (en) 2010-05-13
US20110026721A1 (en) 2011-02-03
EP2269388A4 (en) 2011-06-29
US8731205B2 (en) 2014-05-20
WO2009121111A1 (en) 2009-10-08
WO2009121098A1 (en) 2009-10-08
EP2271282A2 (en) 2011-01-12
WO2009124005A2 (en) 2009-10-08
US8945216B2 (en) 2015-02-03
US20170257710A1 (en) 2017-09-07
WO2009121104A1 (en) 2009-10-08
EP2272260A1 (en) 2011-01-12
WO2009124010A2 (en) 2009-10-08
WO2009121105A1 (en) 2009-10-08
EP2269386A4 (en) 2012-12-12
WO2009121116A9 (en) 2009-11-05
WO2009121117A1 (en) 2009-10-08
US20090248085A1 (en) 2009-10-01
US20090248086A1 (en) 2009-10-01
WO2009121111A9 (en) 2009-11-05
WO2009124008A1 (en) 2009-10-08
US20090245553A1 (en) 2009-10-01
WO2009124038A1 (en) 2009-10-08
EP2265318A4 (en) 2011-06-29
WO2009121105A9 (en) 2009-11-05
WO2009124036A2 (en) 2009-10-08
WO2009121114A9 (en) 2009-11-05
US20090245555A1 (en) 2009-10-01
US20140193011A1 (en) 2014-07-10
WO2009121113A1 (en) 2009-10-08
WO2009121115A9 (en) 2009-11-05
US8655002B2 (en) 2014-02-18
US8150083B2 (en) 2012-04-03
WO2009121108A9 (en) 2009-11-05
US20110026748A1 (en) 2011-02-03
US8154173B2 (en) 2012-04-10
WO2009124010A3 (en) 2009-12-30
EP2269241A1 (en) 2011-01-05
WO2009121115A1 (en) 2009-10-08
US20090252353A1 (en) 2009-10-08
US20090247810A1 (en) 2009-10-01
US8852251B2 (en) 2014-10-07
EP2269386B1 (en) 2018-08-01
US20110112462A1 (en) 2011-05-12
WO2009121106A9 (en) 2009-11-05
EP2272260A4 (en) 2011-05-04
WO2009121113A9 (en) 2009-11-05
WO2009124036A3 (en) 2009-12-30
EP2265318A1 (en) 2010-12-29
US8532322B2 (en) 2013-09-10
CN102047692B (en) 2014-07-30
WO2010008630A1 (en) 2010-01-21
WO2009121097A9 (en) 2009-11-05
EP2271282A4 (en) 2011-04-06
US20110190882A1 (en) 2011-08-04
US8401213B2 (en) 2013-03-19
US8526641B2 (en) 2013-09-03
US8831260B2 (en) 2014-09-09
US20110034755A1 (en) 2011-02-10
US20180376255A1 (en) 2018-12-27
WO2009121109A9 (en) 2009-11-05
WO2009124035A2 (en) 2009-10-08
US20090245556A1 (en) 2009-10-01
US8509461B2 (en) 2013-08-13
US8170252B2 (en) 2012-05-01
US20090245554A1 (en) 2009-10-01
WO2009124042A3 (en) 2010-01-07
WO2009121097A1 (en) 2009-10-08
WO2009121118A1 (en) 2009-10-08
US8363871B2 (en) 2013-01-29
US20110022119A1 (en) 2011-01-27
US8657734B2 (en) 2014-02-25
US8216287B2 (en) 2012-07-10
WO2009121109A1 (en) 2009-10-08
WO2009121104A9 (en) 2009-11-05
WO2009121116A1 (en) 2009-10-08
US20090247812A1 (en) 2009-10-01
WO2009124005A3 (en) 2010-01-07
US8532321B2 (en) 2013-09-10
EP2269386A2 (en) 2011-01-05
WO2009121117A9 (en) 2009-12-23
US20130345496A1 (en) 2013-12-26
US20090248155A1 (en) 2009-10-01
US20090248023A1 (en) 2009-10-01
US9602931B2 (en) 2017-03-21
US20090247813A1 (en) 2009-10-01
US9955270B2 (en) 2018-04-24
US20090247814A1 (en) 2009-10-01
WO2009121108A1 (en) 2009-10-08
EP2269388A1 (en) 2011-01-05
WO2009121098A9 (en) 2009-11-05
WO2009121118A9 (en) 2009-11-05

Similar Documents

Publication Publication Date Title
EP1340408B1 (en) Apparatus for delivery of pharmaceuticals to the cochlea
EP1145734B1 (en) At least partially implantable system for the rehabilitation of a hearing disorder
EP1246503B1 (en) Completely implantable hearing system
CN1732712B (en) Combined equipment comprising implantable apparatus and vibration actuator, and the implantable apparatus
AU2003291875B2 (en) Surgically implantable hearing aid
CA2236743C (en) Implantable microphone for cochlear implants and the like
US20100198302A1 (en) Electrical stimulation in the middle ear for treatment of hearing related disorders
DE60113293T2 (en) Cochlear implant electrode assembly with double stopper insert
EP1191815B1 (en) At least partially implantable hearing system with direct mechanical stimulation of a lymphatic space of the internal ear
US8657734B2 (en) Implantable universal docking station for prosthetic hearing devices
EP1233810B1 (en) Insertion tool for a cochlear implant electrode array
US6549814B1 (en) Blade electrode array for insertion under soft tissue of lateral wall of cochlea
US8000798B2 (en) Cochlear implant system substantially preserving the hydrodynamic nature of the cochlea
US20100048983A1 (en) Multipath Stimulation Hearing Systems
US8620459B2 (en) Pre-curved cochlear implant electrode array
US8688222B2 (en) Stimulus timing for a stimulating medical device
EP1255584B1 (en) Combination stylet and stiffening sheath in an implantable tissue stimulating device, in particular in a cochlear implant
AU778131B2 (en) At least partially implantable system for rehabilitation of hearing disorder
US6575894B2 (en) At least partially implantable system for rehabilitation of a hearing disorder
EP1173044B1 (en) Implantable system for the rehabilitation of a hearing disorder
US7406352B2 (en) Laminated electrode for a cochlear implant
US20100287770A1 (en) Manufacturing an electrode carrier for an implantable medical device
US6259951B1 (en) Implantable cochlear stimulator system incorporating combination electrode/transducer
US6473651B1 (en) Fluid filled microphone balloon to be implanted in the middle ear
AU777272B2 (en) Cochlear implant electrode array

Legal Events

Date Code Title Description
AS Assignment

Owner name: COCHLEAR LIMITED, AUSTRALIA

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:PARKER, JOHN L.;REEL/FRAME:028686/0859

Effective date: 20120620

STCB Information on status: application discontinuation

Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION