WO2009121097A9 - Mechanical fixation system for a prosthetic device - Google Patents
Mechanical fixation system for a prosthetic device Download PDFInfo
- Publication number
- WO2009121097A9 WO2009121097A9 PCT/AU2009/000350 AU2009000350W WO2009121097A9 WO 2009121097 A9 WO2009121097 A9 WO 2009121097A9 AU 2009000350 W AU2009000350 W AU 2009000350W WO 2009121097 A9 WO2009121097 A9 WO 2009121097A9
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- abutment
- conduction
- anchor
- plates
- bone
- Prior art date
Links
Classifications
-
- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
- H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
-
- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
- H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
- H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting
-
- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
- H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
- H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
- H04R25/604—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers
- H04R25/606—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers acting directly on the eardrum, the ossicles or the skull, e.g. mastoid, tooth, maxillary or mandibular bone, or mechanically stimulating the cochlea, e.g. at the oval window
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES 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
- A61M2205/00—General characteristics of the apparatus
- A61M2205/05—General characteristics of the apparatus combined with other kinds of therapy
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES 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
- A61M2210/00—Anatomical parts of the body
- A61M2210/06—Head
- A61M2210/0662—Ears
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES 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
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/142—Pressure infusion, e.g. using pumps
- A61M5/14244—Pressure infusion, e.g. using pumps adapted to be carried by the patient, e.g. portable on the body
- A61M5/14276—Pressure infusion, e.g. using pumps adapted to be carried by the patient, e.g. portable on the body specially adapted for implantation
-
- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
- H04R2460/00—Details 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
- H04R2460/13—Hearing devices using bone conduction transducers
-
- Y—GENERAL 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
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T29/00—Metal working
- Y10T29/49—Method of mechanical manufacture
- Y10T29/4957—Sound device making
- Y10T29/49572—Hearing aid component making
Definitions
- the present invention relates generally to prosthetic devices, and more particularly, to a mechanical fixation system for a prosthetic device.
- Hearing loss which may be due to many different causes, is generally of two types, conductive or sensorineural. In many people who are profoundly deaf, the reason for their deafness is sensorineural hearing loss. This type of hearing loss is due to the absence or destruction of the hair cells in the cochlea which transduce acoustic signals into nerve impulses.
- Various prosthetic hearing implants have been developed to provide individuals who suffer from sensorineural hearing loss with the ability to perceive sound.
- One such prosthetic hearing implant is referred to as a cochlear implant.
- Cochlear implants use an electrode array implanted in the cochlea of a recipient to bypass the mechanisms of the ear. More specifically, an electrical stimulus is provided via the electrode array directly to the cochlea nerve, thereby causing a hearing sensation.
- Conductive hearing loss occurs when the normal mechanical pathways to provide sound to hair cells in the cochlea are impeded, for example, by damage to the ossicular chain to ear canal. However, individuals who suffer from conductive hearing loss may still have some form of residual hearing because the hair cells in the cochlea are generally undamaged.
- a hearing aid typically uses an arrangement positioned in the recipient's ear canal to amplify a sound received by the outer ear of the recipient. This amplified sound reaches the cochlea and causes motion of the cochlea fluid and stimulation of the cochlea hair cells.
- hearing aids are typically unsuitable for individuals who suffer from single-sided deafness (total hearing loss only in one ear) or individuals who suffer from mixed hearing losses (ie. Combinations of sensorineural and conductive hearing loss).
- hearing prostheses that use the principles of bone conduction device to provide acoustic signals to a recipient.
- Such hearing prostheses direct vibrations into the bone, so that the vibrations are conducted into the cochlea and result in stimulation of the hairs in the cochlea.
- This type of prosthesis is typically referred to as a bone conduction device.
- Bone conduction devices function by converting a received sound signal into a mechanical vibration representative of the received sound. This vibration is then transferred to the bone structure of the skull, causing vibration of the recipient's skull. This skull vibration results in motion of the fluid of the cochlea, thereby stimulating the cochlea hair cells and causing a hearing sensation to be perceived by the recipient. Vibration from a bone conduction device is generally conducted to a recipient's cochlea via a screw implanted in the recipient's skull.
- the skull bone at the point of implant of the bone screw, is susceptible to damage from lateral forces on the bone screw, particularly during the healing period following the implant procedure.
- This healing period varies from person to person, depending upon many factors associated with the patient's overall health and genetics, but generally takes six weeks or more.
- the bone is so susceptible to damage that the general practice is that the bone conduction device is not coupled to bone screw until the healing period has ended. Further, while the bone is less susceptible to damage following the healing period, damage may still be possible if a large lateral force is applied thereto.
- a fixation system for a bone conduction device comprises: a bone anchor configured to be implanted in a recipient of the bone conduction device; an abutment coupled to the bone anchor defining a conduction path to the bone anchor such that vibrations applied to the abutment are transferred to the bone anchor, the abutment comprising a plurality of inter-locking stacked plates disposed adjacent the bone anchor forming part of the conduction path; and a vibratory coupler extending from the bone conduction device, comprising a second conduction surface and a magnet, wherein the magnet attracts to the abutment so as to couple the second conduction surface to the abutment, thereby enabling vibrations to pass through the conduction path, wherein the plates are configured to laterally slide with respect to another in response to tangential forces incident upon the abutment.
- an implantable anchor for coupling a vibratory coupler extending from the bone conduction device to a recipient, the bone conduction device comprising a second conduction surface and a magnet.
- the implantable anchor comprises: a bone anchor configured to be implanted in the recipient of the bone conduction device; and an abutment coupled to the bone anchor defining a conduction path to the bone anchor such that vibrations applied to the abutment are transferred to the bone anchor, the abutment comprising a plurality of inter-locking stacked plates disposed adjacent the bone anchor forming part of the conduction path; wherein when the second conduction surface is adjacent the abutment the magnet attracts to the abutment so as to couple the second conduction surface to the abutment, thereby enabling vibrations to pass through the conduction path, and wherein the plates are configured to laterally slide with respect to another in response to tangential forces incident upon the abutment.
- FIG. 1 is a partial sectional view of a skull showing the ear canal, the cochlea, and a bone conduction device with the bone anchor implanted in the skull and the external module coupled to the bone anchor;
- FIG. 2 is a schematic diagram of a bone conduction device
- FIG. 3 is an exploded view of an external module for a bone conduction device
- FIG. 4A is a partial sectional view of a fixation system for a bone conduction device
- FIG. 4B illustrates the vibratory coupler pivoted on the abutment for the bone conduction device of FIG. 4A;
- FIG. 5 is a graph illustrating the longitudinal loading force curve for a bone screw set into the skull bone as the bone heals over time
- FIG. 6 is a sectional view of a first alternative embodiment for the vibratory coupler associated with the external module of a bone conduction device
- FIG. 7 is a sectional view of a second alternative embodiment for the vibratory coupler associated with the external module of a bone conduction device
- FIG. 8A is a sectional view of a first alternative embodiment for the abutment of a bone conduction device
- FIG. 8B illustrates the lateral deformation of the abutment of FIG. 8A
- FIG. 9 A is a perspective view of a first alternative embodiment for shearing elements associated with the abutment
- FIG. 9B illustrates a sectional view of the coupling between shearing elements of FIG. 9A
- FIG. 10 is a sectional view of a second alternative embodiment for the abutment of a bone conduction device;
- FIG. 1 1 is a sectional view of a third alternative embodiment for the abutment of a bone conduction device;
- FIG. 12 is a sectional view of a fourth alternative embodiment for the abutment of a bone conduction device
- FIG. 13A is cross-sectional view of a coupling system in accordance with embodiments of the present invention.
- FIG. 13B is cross-sectional view of a coupling system in accordance with embodiments of the present invention.
- FIG. 13C is cross-sectional view of a coupling system in accordance with embodiments of the present invention.
- the present invention is directed toward a fixation system for a prosthetic device, such as bone conduction device.
- a bone anchor is implanted into the skull, and an abutment is coupled to the bone anchor so as to define a conduction path to the bone anchor such that vibrations applied to the abutment are transferred to the bone anchor.
- the abutment comprises a plurality of interlocking stacked plates disposed adjacent to the bone anchor that form part of the conduction path.
- the fixation system further comprises a vibratory coupler extending from the bone conduction device, comprising a second conduction surface and a magnet, wherein the magnet attracts to the abutment so as to couple the second conduction surface to the abutment, thereby enabling vibrations to pass through the conduction path.
- the plates are configured to slide laterally in response to tangential forces incident upon the abutment.
- the abutment has a bearing surface adjacent to the first conduction surface.
- the two surfaces intersect at a non-orthogonal angle.
- the vibratory coupler includes a leveraging extension extending away from the second conduction surface, and when the second conduction surface is seated on the first conduction surface, at least a distal edge of the leveraging extension seats upon the bearing surface.
- the bearing surface includes a shelf on which the leveraging extension seats.
- FIG. 1 is a perspective view of an exemplary bone conduction device 101 with which embodiments of the present invention may be advantageously implemented.
- the fully functional human hearing anatomy is generally divided up into the outer ear 105, the middle ear 107, and the inner ear 109.
- the outer ear 105 includes the auricle 111 and the ear canal 113.
- Sound waves 115 are collected by auricle 111 and channeled into and through ear canal 113.
- the tympanic membrane 117 which is located at the boundary between the outer ear 105 and the middle ear 107, vibrates in response to the sound waves 107.
- vibration of the tympanic membrane 117 is coupled to the fenestra ovalis 119 through three bones, collectively referred to as the ossicles 121.
- the ossicles 121 filter and amplify the vibrations, thereby causing the fenestra ovalis 119 to articulate.
- the movement of the fenestra ovalis 119 generates pressure waves in the fluid within cochlea 123, which in turn induces movement in the hairs lining the inside of the cochlea 123. Movement of the hairs generates nerve impulses in spiral ganglion cells to which the hairs are connected, and those nerve impulses are passed to the auditory nerve 125, and then to the brain (not shown), where they are perceived as sound.
- Bone conduction device 101 is shown positioned behind the auricle 111 of the recipient, although the device could also be positioned in a variety of other positions in the skull of the recipient.
- Bone conduction device 101 includes an external module 127, and is coupled to the skull of the recipient via an implanted anchor, such as bone screw 129. Bone screw 129 is secured to the skull bone 131 during the implant procedure.
- a vibratory coupler 133 which secures external module 127 to bone screw 129.
- any appropriate anchor system may be used in lieu of the bone screw 129, so long as the anchor system conducts sufficient vibrations from the bone conduction device 101 for the recipient to perceive the vibrations as sound.
- the anchor system may be implanted under skin 135 of the recipient, within muscle tissue 137 and/or fat tissue 139.
- the material from which the bone anchor is constructed is a matter of design choice.
- the material may be a metal that does not stimulate an undesirable response of body systems, or it may be any other type of biocompatible material.
- the sound and signal processing components of external module 127 are schematically shown in FIG. 2.
- Sound waves 203 are received by a sound pickup device 205 and converted into a representative signal, which is directed into a signal processor 207.
- Signal processor 207 converts the representative signal into an appropriate signal adjusted, as necessary, for the transducer drive circuit 209, which outputs a drive signal to a transducer module 211. Adjustments to the representative signal may include filtering, removal of distortions, reduction of background noises, and the like.
- Transducer module 211 generates a mechanical vibration representative of the sound waves 203, and these mechanical vibrations are conducted to the skull via a mechanical coupling between transducer module 211, namely vibratory coupler 133, and bone screw 129.
- An appropriate power module (not shown) is included as part of the external module to provide power to each of the various components.
- a control module 215, having control electronics therein, is electronically connected to sound pickup device 205, signal processor 207, and transducer drive circuit 209.
- Control module 215 may also be electronically connected to transducer module 211, or any other components of external module 127.
- Control module 215 monitors and controls operation of the electronic components and circuits to which it is connected. The amount of control provided by control module 215 may vary depending upon the component or circuit type. Control module 215 may also serve as a feedback loop to provide corrections to the output of any one or more of the components where necessary.
- An interface module 217 is connected to control module 215 to permit the recipient, or a skilled practitioner of the medical arts, to adjust preselected settings of external module 127.
- the preselected settings may include volume, sound processing strategies, power on/off the device, and the like.
- the interface module and the control module may be integrated into a single module.
- any of the signals between circuits forming part of external module 127 may be transmitted via a wired connection or wirelessly. Further, not all circuits need be housed within a single casing.
- Signal processor 207 may use one or more different techniques or strategies to selectively process, amplify, and/or filter the signal representative of sound waves 203.
- signal processor 207 may be of substantially the same as the sound processor that is used in an air conduction hearing aid.
- signal processor 207 may include and analog to digital converter and a digital signal processor.
- FIG. 3 illustrates an exploded view of one embodiment of an external module of a bone conduction device, referred to herein as external module 301.
- External module 301 shown in FIG. 3 includes an electronics module 303, a transducer module 305, and a battery shoe 307 for powering the electronic components.
- Electronics module 303 and the transducer module 305 operate as described above.
- Electronics module 303 includes a printed circuit board 309 (PCB) to electrically connect and mechanically support the various electronic components and circuits.
- PCB printed circuit board 309
- One or more microphones 311 are directly attached to PCB 309 to function as sound pickup devices.
- other types of direct audio input could be used as the sound pickup devices instead of, or in addition to, microphones 311.
- Such alternatives include digital or analog audio input ports, a telecoil, and the like.
- the housing for the external module 301 includes a top part 313a and a bottom part 313b.
- the two housing parts 313a, 313b are configured to mate with one another, leaving an opening for insertion of battery shoe 307. Following insertion of battery show 307, housing parts 313a, 313b substantially seal the internal components of external module 301 from external elements.
- the top housing part 313a includes one or more snap-on microphone covers 315, which protect the microphones 311 from dust, dirt and other debris.
- a user interface 317 is disposed on one side of the top housing part 313A to give the recipient access to the interface module 217 functions.
- the bottom housing part 313b includes an opening 319 for insertion of a fastener (not shown).
- the fastener secures transducer module 305 to the inside of the bottom housing part 313b, and/or secures a vibratory coupler, such as one of the vibratory couplers shown below, to the outside of the bottom housing part 313b and/or transducer module 305.
- a direct mechanical connection is established for conduction of vibrations from the transducer module 305 to the vibratory coupler, and from there into the bone anchor.
- opening 319 may be sealed against external elements by use of an o-ring or other sealant.
- FIG. 4 illustrates a coupling system in accordance with embodiments of the present invention.
- the coupling system comprises a vibratory coupler 403 and an implanted anchor system.
- vibratory coupler 403 extends from an external module 401, sometimes referred to herein as a vibration generating module 401, and is coupled to the implanted anchor system.
- the implanted anchor system comprises an abutment 405 and an anchor 407, such as bone screw 407. Abutment 405 may be releasably affixed to bone screw 407.
- abutment 405 extends above tissue 41 1 so that vibratory coupler 403 may be seated on abutment 405.
- the combination of vibratory coupler 403, abutment 405, and bone screw 407 enable vibrations from external module 401 to be conducted into bone 409.
- a bone anchor may also be used instead of the bone screw.
- One such example is a plate secured to the bone in at least two locations along the edge of the plate, such that the center portion of the plate rests against or is mechanically coupled to the skull bone, thereby enabling vibrations applied to the bone anchor to pass into the bone.
- the abutment may extend from the center portion of the plate, and forces normal to the skull incident upon the abutment or the external module would not impact a surgically modified site, but rather would impact an unaltered section of the skull bone.
- the top portion of the abutment 405, which extends above the tissue 411, has a regularly defined cross-section, and may be circular, elliptical, or any other shape according to design preferences.
- the radius about the entire cross-section need not be constant.
- a constant radius may be used in circumstances where it is desired to allow the external module to be mounted with any orientation.
- a non-constant radius may be used in circumstances where the external module is intended to have only a single orientation when the vibratory coupler is seated on the abutment.
- abutment 405 comprises a bearing surface 413 of which extends away from a conduction surface 415.
- Bearing surface 413 extends away from conduction surface such that an acute angle, or at least a non-orthogonal angle, is formed along the surface of abutment 405.
- the shapes of bearing surface 413 and the conduction surface 415 are a matter of design choice, however, the conduction surface is preferably planar to facilitate coupling with vibratory coupler 403 and conduction of vibrations. Alternatively, if bearing surface 413 is curved, the bearing surface and conduction surface 415 may intersect tangentially.
- a shelf 417 is formed in the bearing surface.
- the particular geometry of this shelf 417 may vary according to other design considerations, particularly the geometry of vibratory coupler 403.
- shelf 417 may be entirely omitted from abutment 405.
- abutment 405 also includes a magnetic material 419 set into the abutment 405 at conduction surface 415.
- This magnetic material 419 may form part of conduction surface 415, or alternatively, it may be disposed beneath the surface.
- the magnetic material may have any geometrical configuration that suits other design choices that are made concerning abutment 405 and vibratory coupler 403.
- Magnetic material 419 is preferably magnetizeable material, and not a permanent magnet, although a permanent magnet could be used.
- vibratory coupler 403 extends outward from external module 401 and includes a magnet 421.
- Vibratory coupler 403 further includes a conduction surface 423, and a leveraging extension 425.
- Conduction surface 423 of vibratory coupler 403 has a complimentary shape to conduction surface 415 of abutment 405, and seats directly on the conduction surface of the abutment such that mechanical contact is made between the two conduction surfaces 415, 423.
- Magnet 421 in vibratory coupler 403 interacts with the magnetic material 419 in the abutment 405 to retain the two conduction surfaces 415, 423 seated together under normal use conditions.
- the holding force generated between magnet 421 and magnetic material 419 should be sufficient to maintain the seating under the force generated by the weight of vibratory coupler 403. In addition, the holding force should also be sufficient to maintain the seating when the instantaneous force generated by vibrations from external module 401 are coupled with the weight of vibratory coupler 403.
- Leveraging extension 425 extends away from conduction surface 423 of vibratory coupler 403 such that at least a distal edge 427 of the leveraging extension seats upon the bearing surface 413, and preferably upon shelf 417.
- the entire inner surface of leveraging extension 425 may seat on bearing surface 413.
- the configuration of the leveraging extension 425 may vary widely.
- the leveraging extension may form an annular ring at the distal end, or alternatively, the annular ring may be divided up into two, four, or more sections, each section connected to the main body of the vibratory coupler via an arm.
- the leveraging extension may be a plurality of arms extending away from the main body of the vibratory coupler. In such an embodiment, more arms are preferable, however, as few as two arms will generally suffice.
- FIG. 4B illustrates how the vibratory coupler 403 is decoupled from abutment 405 when a part of the external module 401 is subjected to a force that is tangential to the skull.
- the tangential force is marked by the arrow, F, and upon incidence of this tangential force on external module 401, conduction surface 423 of the vibratory coupler 403 is pivoted up and away from the conduction surface 415 of abutment 405. This pivoting action is caused by the leveraging extension 425 seated upon the shelf 417 of abutment 405 on the opposite side of vibratory coupler 403 from where the force is incident.
- leveraging extension 425 acts as a lever arm, and assists in lifting and magnetically decoupling magnet 421 from magnetic material 419.
- F force to which abutment 405 is subjected
- FIG. 5 The amount of tangential force to which a bone screw may be subjected following implantation, without causing damage to the bone, is illustrated in FIG. 5. Initially, when a bone screw is implanted, the amount of tangential loading force to which it may be subjected is somewhat high.
- the decrease is at least partially due to the fact that when bones are damaged, the human body first breaks down some of the bone structure surrounding the damaged site before beginning to rebuild and heal the bone.
- the external module is not generally worn. For prior art bone conduction devices, this is how implant patients proceed—they refrain from regularly using the external module until healing is complete.
- FIG. 6 An alternative embodiment of a vibratory coupler in accordance with embodiments of the present invention is shown in FIG. 6.
- a sheath 603 extends from housing 605 of external module 601.
- a coupling arm 607 is partially disposed within sheath 603.
- Coupling arm 607 is held to the body of external module 601 via a fastener 609, which enables the position of coupling arm 607 relative to housing 605 to be adjusted.
- a spring 611 is also included within sheath 603 and biases against adjustments made by the fastener 609.
- the distal edges 613 of the sheath 603 exert pressure on leveraging extension 615 to cause constriction.
- leveraging extension 615 some variation may be introduced in the amount of tangential force required to unseat the vibratory coupler from the abutment, thereby enabling a custom fit for any particular implant recipient.
- FIG. 7 illustrates another embodiment of a vibratory coupler 701 in accordance with embodiments of the present invention.
- vibratory coupler 701 includes a sheath 703 is formed of two parts, a first part 705 which extends from body 707 of external module 701, and a second part 709 which is threaded into first part 705.
- the overall length of the sheath 703 is adjustable.
- coupling arm 711 extends into sheath 703.
- a post 713 extends from body 707, and the coupling arm 711 slidingly fits onto post 713.
- a spring 715 disposed within sheath 703 biases the coupling arm 711 toward body 707 of external module 701.
- constriction of leveraging extension 717 is enabled by lengthening sheath 707 and biasing the coupling arm into the sheath by use of spring 715. Conversely, the amount of constriction may be reduced by shortening sheath 707.
- FIG. 8 illustrates alternative embodiments for an abutment in accordance with embodiments of the present invention, referred to as abutment 801.
- Abutment 801 further reduces the amount of tangential force to which the bone screw 803, or other bone anchor, might be subjected.
- Abutment 801 comprises an outer sheath 805 which includes a conduction surface 807 and a bearing surface 809 as described above with reference to FIGS. 4A and 4B.
- Outer sheath 805 may be constructed of thin walled titanium, or other similar material, which can be laser welded to the bone screw to ensure that the interface between the outer sheath and the bone screw is smooth and does not provide crevices for the lodgment of debris.
- Outer sheath 805 is constructed to house a plurality of shearing elements, in this case, several stacked plates 811. The plates 811 are not connected to one another, and each may slide laterally with respect to adjacent plates. The plates 811 do not need to be similarly dimensioned.
- the surfaces of the plates 811 may be polished, or alternatively, a lubricant may be included within outer sheath 805.
- the material from which plates 811 are constructed is a matter of design choice. For example, they may be constructed from a light weight plastic or polymer material, a biocompatible material, or a heavier metal material.
- the plates may be constructed from a magnetizeable material, but preferably not from material that is a permanent magnet, as such a construction is likely to significantly inhibit lateral sliding between adjacent plates.
- Outer sheath 805 serves at least a few purposes in this embodiment.
- outer sheath 805 maintains each plate 811 within the stack in physical contact with each adjacent plate to ensure that abutment 805 is mechanically stiff in a direction normal to the skull.
- the stack conducts vibrations from conduction surface 807 through to bone screw 803.
- contact between plates 811 keep each plate from laterally sliding with respect to adjacent plates under normal use conditions.
- Another purpose of outer sheath 805 is to limit lateral sliding of the plates 811 so that a conduction path is maintained to pass vibrations from the external module to the bone screw 803.
- Yet another purpose of the outer sheath 805 is to assist in returning plates 811 to the default stack configuration following deformation of the stack when subjected to lateral forces.
- FIG. 8B shows the stack of plates 811 with the top two plates 811a, 811b laterally displaced as a result of a lateral force F.
- Outer sheath 805 deforms along with the stack of plates 811.
- outer sheath 805 may be formed from a shape memory material.
- springs may be included within outer sheath 805 to aid in biasing the stack of plates 811 toward the default stack configuration.
- Non-permanent magnets, strategically placed within each stacked plate, could also be used to aid in realignment of the stacked plates into the default stack configuration.
- FIG. 9A shows an alternative arrangement for a plurality of stacked plates 901 which may be used in accordance with embodiments of the present invention.
- each plate is interlocked with adjacent plates.
- Each plate 901a-d includes an outward extending pin 903 and a slot 905. Plates 901a-d are stacked so that pin 903a-d of each plate 901a-d is inserted into the slot 905a-d of an adjacent plate. The pin 903 of each plate seats within the slot 905 of an adjacent plate as shown in FIG. 9B.
- the pin 903a on the end plate 901a (as shown), having only a single adjacent plate, may either be omitted from the construction or used for another purpose — lacking an adjacent plate, the pin 903 of the end plate 901a is not inserted into a corresponding slot.
- the slot 905a-d in each plate 901 a-d is curved, so that when the stack 901 is subjected to a lateral force, displacement of any one or more plates will also cause rotation of the displaced plates. Such rotation helps to further absorb any incident lateral forces. Because the plates are interlocked, and an outer sheath is not required, although one may be used. Moreover, this embodiment might also be implanted subcutaneously.
- abutment 1001 comprises an outer sheath 1003 having an internal cavity 1005 and a granulated material 1007 disposed therein.
- the granulated material 1007 may any number of different types of material, from sand, to magnetizeable particles, to small beads, whether plastic, glass, or metal and the like.
- the magnet within the external module would align the particles to assist in forming a conduction path between the conduction surface and the bone anchor, while at the same time permitting shearing action between the particles in response to lateral forces incident upon the outer sheath.
- Additional materials may be included within the cavity to either better enable shearing action of the granulated particles, i.e., movement in the lateral direction in response to lateral forces incident upon the abutment, or to better enable conduction of vibrations from the external module, through the granulated material, to the bone anchor.
- collagen may be included within the internal cavity, along with beads, to better aid in the transmission of vibrations. It is anticipated that collagen might also aid in improving the shearing action of such beads.
- the outer sheath may be constructed using a shape memory material to aid in returning the abutment to a default shape.
- abutment 1101 in FIG. 11 Another embodiment of an abutment in accordance with embodiments of the present invention is illustrated as abutment 1101 in FIG. 11.
- This abutment includes an outer sheath 1103 with an external profile which is a matter of design choice.
- Outer sheath 1103 may be formed as shown, it may be formed according to any of the other embodiments discussed herein, or it may have an entirely different shape to suit other design considerations.
- Outer sheath forms an internal cavity 1105, in which is disposed a proximal plate 1107, a distal plate 1109, a wire 1111, which forms a flexible conduction path, and a spring 1113.
- the proximal plate 1107 is disposed adjacent to, and may be coupled to, the conduction surface 1115 of outer sheath 1103 such that vibrations applied to conduction surface 1115 pass through to distal plate 1109.
- the distal plate 1109 is disposed adjacent and coupled to bone anchor 1117.
- the wire 1111 extends between and is coupled to both proximal plate 1107 and distal plate 1109.
- spring 1113 is disposed between proximal and distal plates 1107, 1109, but spring 1113 biases the plates 1107, 1109 away from one another, thereby placing the wire 1111 under tension and enabling the wire 1111 to conduct vibrations applied to proximal plate 1107 through to the proximal plate 1109, and thus in to the bone anchor 1117.
- Additional wires may be included to form additional conduction paths.
- the material from which the wire or wires is constructed is a matter of design choice. Those skilled in the art will recognize that certain materials, such as metals and other materials that are less susceptible to permanent deformation due to stretching, are better suited for long term use within the abutment. Those materials that are susceptible to permanent deformation due to stretching may still be used, but abutments employing such materials may require more frequent replacement.
- abutment 1201 includes an outer sheath 1203 forming an internal cavity 1205.
- outer sheath 1203 is preferably constructed using a shape memory material to provide some flexibility, but at the same time be sufficiently rigid to seat a vibratory coupler.
- Outer sheath 1203 includes a conduction surface 1207 and a distal surface 1209 which is coupled to bone anchor 1211, and vibrations applied to distal surface 1209 are conducted into bone anchor 1211.
- a conduction axis, A defines the conduction path along which vibrations pass from an external module to bone anchor 1211 once the external module is seated on the abutment.
- a spiral spring 1213 and a magnet 1215 are disposed within the cavity 1205.
- the spiral spring 1213 has an outer end coupled to distal surface 1209, and the magnet 1215 is coupled to the center end of the spiral spring.
- the magnet 1215 has a magnetic axis, M, defined by the two magnetic poles, N and S, and the spiral spring 1213 biases the magnet 1215 so that the magnetic axis is not parallel to, and is preferably perpendicular to, the conduction axis A.
- magnet 1215 in the abutment 1201 rotates, it is attracted toward the magnet in the vibratory coupler. In addition, magnet 1215 in abutment 1201 will seat against distal surface 1209, thereby enabling vibrations applied to abutment 1201 to pass through to bone anchor 1211.
- FIG. 13A is cross-sectional view of a coupling system in accordance with embodiments of the present invention.
- the coupling system comprises a vibratory coupler 1306 attached to, and extending from, an external module 1301 of a bone conduction device.
- a magnet 1308 Disposed within vibratory coupler 1306 is a magnet 1308.
- Implanted within skin 1302 is an implanted anchor 1310. Vibration generated by external module 1301 is coupled through implanted anchor 1310 to the skull 1304.
- implanted anchor 1310 comprises a plurality of particles, beads, or other elements 1310 which are injected or implanted into skin 1302.
- the plurality of particles 1310 alter the material stiffness of the skin so that the vibration from vibrator coupler 1306 may be transferred to the skull 1304 with little to no loss, thus eliminating the need for an exposed abutment.
- any of a variety of particles may be injected or implanted into skin 1302 of a recipient.
- skin 1302 is stiffened by injecting a sufficient quantity of ceramic or metallic powder (e.g., titanium powder, platinum powder, etc) into the skin.
- ceramic or metallic powder e.g., titanium powder, platinum powder, etc
- collagen or any other bioresorable material that may provide stiffness to skin 1302 may be used.
- particles that enhance fibrous tissue growth may be injected or implanted into skin 1302.
- a magnet 1308 is disposed within vibratory coupler 1306.
- Magnet 1308 is configured to provide an attraction force between vibratory coupler 1306 and particles 1310. This attraction retains external module 1301 in position during normal use, and is sufficient to attach external module 1301 to the recipient under the force generated by the weight of vibratory coupler 1306. In addition, the attraction force should also be sufficient to maintain the attachment when the instantaneous force generated by vibrations from external module 1301 are coupled with the weight of vibratory coupler 1306.
- magnet 1308 may comprise a permanent magnet. In other embodiments, magnet 1308 may comprise a magnetic material that is not a permanent magnet.
- particles 1310 are prevented from migrating from the injection site.
- the particles may be tied to one another prior to injection/implantation.
- the particles may be coated with collagen to prevent migration.
- Other particles comprising, such as silicone particles, may promote tissue in-growth there with to prevent migration.
- FIG. 13B is cross-sectional view of a coupling system in accordance with embodiments of the present invention.
- implanted anchor 1318 comprises a granulated material 1322 bounded by a volume 1320.
- the granulated material 1322 may any number of different types of material, from sand, to magnetizeable particles, to small beads, whether plastic, glass, or metal and the like.
- Volume 1320 may comprise, for example, a surgically implanted mesh or cage 1320 which prevents migration of granulated material 1322.
- a magnet 1308 is disposed within vibratory coupler 1306.
- Magnet 1308 is configured to provide an attraction force between vibratory coupler 1306 and particles 1310. This attraction retains external module 1301 in position during normal use, and is sufficient to attach external module 1301 to the recipient under the force generated by the weight of vibratory coupler 1306. In addition, the attraction force should also be sufficient to maintain the attachment when the instantaneous force generated by vibrations from external module 1301 are coupled with the weight of vibratory coupler 1306.
- magnet 1308 may comprise a permanent magnet. In other embodiments, magnet 1308 may comprise a magnetic material that is not a permanent magnet.
- FIG. 13C is cross-sectional view of a coupling system in accordance with embodiments of the present invention. Similar to the embodiments described above with reference to FIG. 13B, a granulated material 1334 bounded by a volume 1336. The granulated material 1322 may any number of different types of material. Implanted anchor 1332 further comprises a magnet 1330 adjacent skull 1304. Vibratory coupler 1306 comprises a permanent magnet 1328. When vibratory coupler 1306 is positioned adjacent skin 1302, magnets 1330 and 1328 cause granulated material 1334 to be substantially aligned, thereby improving the transmission of vibration there through.
Abstract
A fixation system for a bone conduction device is disclosed. An abutment is coupled to a bone anchor such that vibrations applied to the abutment pass into the bone anchor. The abutment defines a conduction path to the bone anchor such that vibrations applied to the abutment are transferred to the bone anchor. The abutment comprises a plurality of interlocking stacked plates disposed adjacent the bone anchor, wherein the plates form part of the conduction path. The fixation system also comprises a vibratory coupler extending from the bone conduction device, comprising a second conduction surface and a magnet, wherein the magnet attracts to the abutment so as to couple the second conduction surface to the abutment, thereby enabling vibrations to pass through the conduction path. The plates are configured to slide laterally in response to tangential forces incident upon the abutment.
Description
MECHANICAL FIXATION SYSTEM FOR A PROSTHETIC DEVICE
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] The present application claims the benefit of U.S. Provisional Patent Application 61/041,185; filed March 31, 2008, which is hereby incorporated by reference herein.
BACKGROUND
Field of the Invention
[0002] The present invention relates generally to prosthetic devices, and more particularly, to a mechanical fixation system for a prosthetic device.
Related Art
[0003] Hearing loss, which may be due to many different causes, is generally of two types, conductive or sensorineural. In many people who are profoundly deaf, the reason for their deafness is sensorineural hearing loss. This type of hearing loss is due to the absence or destruction of the hair cells in the cochlea which transduce acoustic signals into nerve impulses. Various prosthetic hearing implants have been developed to provide individuals who suffer from sensorineural hearing loss with the ability to perceive sound. One such prosthetic hearing implant is referred to as a cochlear implant. Cochlear implants use an electrode array implanted in the cochlea of a recipient to bypass the mechanisms of the ear. More specifically, an electrical stimulus is provided via the electrode array directly to the cochlea nerve, thereby causing a hearing sensation.
[0004] Conductive hearing loss occurs when the normal mechanical pathways to provide sound to hair cells in the cochlea are impeded, for example, by damage to the ossicular chain to ear canal. However, individuals who suffer from conductive hearing loss may still have some form of residual hearing because the hair cells in the cochlea are generally undamaged.
[0005] Individuals who suffer from conductive hearing loss are typically not candidates for a cochlear implant due to the irreversible nature of the cochlear implant. Specifically, insertion of the electrode array into a recipient's cochlea results in the destruction of the majority of hair cells within the cochlea. The destruction of the cochlea hair cells results in the loss of all residual hearing by the recipient.
[0006] Rather, individuals suffering from conductive hearing loss typically receive an acoustic hearing aid, referred to as a hearing aid herein. Hearing aids rely on principles of air conduction to transmit acoustic signals through the outer and middle ears to the cochlea. In particular, a hearing aid typically uses an arrangement positioned in the recipient's ear canal to amplify a sound received by the outer ear of the recipient. This amplified sound reaches the cochlea and causes motion of the cochlea fluid and stimulation of the cochlea hair cells.
[0007] 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. Other individuals have malformed or absent outer ear and/or ear canals as a result of a birth defect, or as a result of common medical conditions such as Treacher Collins syndrome or Microtia. Furthermore, hearing aids are typically unsuitable for individuals who suffer from single-sided deafness (total hearing loss only in one ear) or individuals who suffer from mixed hearing losses (ie. Combinations of sensorineural and conductive hearing loss).
[0008] These individuals who cannot benefit from hearing aids may benefit from hearing prostheses that use the principles of bone conduction device to provide acoustic signals to a recipient. Such hearing prostheses direct vibrations into the bone, so that the vibrations are conducted into the cochlea and result in stimulation of the hairs in the cochlea. This type of prosthesis is typically referred to as a bone conduction device.
[0009] Bone conduction devices function by converting a received sound signal into a mechanical vibration representative of the received sound. This vibration is then transferred to the bone structure of the skull, causing vibration of the recipient's skull. This skull vibration results in motion of the fluid of the cochlea, thereby stimulating the cochlea hair cells and causing a hearing sensation to be perceived by the recipient. Vibration from a bone conduction device is generally conducted to a recipient's cochlea via a screw implanted in the recipient's skull.
[0010] The skull bone, at the point of implant of the bone screw, is susceptible to damage from lateral forces on the bone screw, particularly during the healing period following the implant procedure. This healing period varies from person to person, depending upon many factors associated with the patient's overall health and genetics, but generally takes six weeks or more.
During the healing period, the bone is so susceptible to damage that the general practice is that the bone conduction device is not coupled to bone screw until the healing period has ended. Further, while the bone is less susceptible to damage following the healing period, damage may still be possible if a large lateral force is applied thereto.
SUMMARY OF THE INVENTION
[OOll] In accordance with aspects of the present invention, a fixation system for a bone conduction device is provided. The fixation system comprises: a bone anchor configured to be implanted in a recipient of the bone conduction device; an abutment coupled to the bone anchor defining a conduction path to the bone anchor such that vibrations applied to the abutment are transferred to the bone anchor, the abutment comprising a plurality of inter-locking stacked plates disposed adjacent the bone anchor forming part of the conduction path; and a vibratory coupler extending from the bone conduction device, comprising a second conduction surface and a magnet, wherein the magnet attracts to the abutment so as to couple the second conduction surface to the abutment, thereby enabling vibrations to pass through the conduction path, wherein the plates are configured to laterally slide with respect to another in response to tangential forces incident upon the abutment.
[0012] In accordance with other aspects of the present invention, an implantable anchor for coupling a vibratory coupler extending from the bone conduction device to a recipient, the bone conduction device comprising a second conduction surface and a magnet is provided. The implantable anchor comprises: a bone anchor configured to be implanted in the recipient of the bone conduction device; and an abutment coupled to the bone anchor defining a conduction path to the bone anchor such that vibrations applied to the abutment are transferred to the bone anchor, the abutment comprising a plurality of inter-locking stacked plates disposed adjacent the bone anchor forming part of the conduction path; wherein when the second conduction surface is adjacent the abutment the magnet attracts to the abutment so as to couple the second conduction surface to the abutment, thereby enabling vibrations to pass through the conduction path, and wherein the plates are configured to laterally slide with respect to another in response to tangential forces incident upon the abutment.
BRIEF DESCRIPTION OF THE DRAWINGS
[0013] Illustrative embodiments of the present invention are described herein with reference to the accompanying drawings, in which:
[0014] FIG. 1 is a partial sectional view of a skull showing the ear canal, the cochlea, and a bone conduction device with the bone anchor implanted in the skull and the external module coupled to the bone anchor;
[0015] FIG. 2 is a schematic diagram of a bone conduction device;
[0016] FIG. 3 is an exploded view of an external module for a bone conduction device;
[0017] FIG. 4A is a partial sectional view of a fixation system for a bone conduction device;
[0018] FIG. 4B illustrates the vibratory coupler pivoted on the abutment for the bone conduction device of FIG. 4A;
[0019] FIG. 5 is a graph illustrating the longitudinal loading force curve for a bone screw set into the skull bone as the bone heals over time;
[0020] FIG. 6 is a sectional view of a first alternative embodiment for the vibratory coupler associated with the external module of a bone conduction device;
[0021] FIG. 7 is a sectional view of a second alternative embodiment for the vibratory coupler associated with the external module of a bone conduction device;
[0022] FIG. 8A is a sectional view of a first alternative embodiment for the abutment of a bone conduction device;
[0023] FIG. 8B illustrates the lateral deformation of the abutment of FIG. 8A;
[0024] FIG. 9 A is a perspective view of a first alternative embodiment for shearing elements associated with the abutment;
[0025] FIG. 9B illustrates a sectional view of the coupling between shearing elements of FIG. 9A;
[0026] FIG. 10 is a sectional view of a second alternative embodiment for the abutment of a bone conduction device;
[0027] FIG. 1 1 is a sectional view of a third alternative embodiment for the abutment of a bone conduction device;
[0028] FIG. 12 is a sectional view of a fourth alternative embodiment for the abutment of a bone conduction device;
[0029] FIG. 13A is cross-sectional view of a coupling system in accordance with embodiments of the present invention;
[0030] FIG. 13B is cross-sectional view of a coupling system in accordance with embodiments of the present invention; and
[0031] FIG. 13C is cross-sectional view of a coupling system in accordance with embodiments of the present invention.
DETAILED DESCRIPTION
[0032] The present invention is directed toward a fixation system for a prosthetic device, such as bone conduction device. A bone anchor is implanted into the skull, and an abutment is coupled to the bone anchor so as to define a conduction path to the bone anchor such that vibrations applied to the abutment are transferred to the bone anchor. The abutment comprises a plurality of interlocking stacked plates disposed adjacent to the bone anchor that form part of the conduction path. The fixation system further comprises a vibratory coupler extending from the bone conduction device, comprising a second conduction surface and a magnet, wherein the magnet attracts to the abutment so as to couple the second conduction surface to the abutment, thereby enabling vibrations to pass through the conduction path. The plates are configured to slide laterally in response to tangential forces incident upon the abutment.
[0033] In certain aspects of the present invention, the abutment has a bearing surface adjacent to the first conduction surface. The two surfaces intersect at a non-orthogonal angle. Further, the vibratory coupler includes a leveraging extension extending away from the second conduction surface, and when the second conduction surface is seated on the first conduction surface, at least a distal edge of the leveraging extension seats upon the bearing surface. Optionally, the bearing surface includes a shelf on which the leveraging extension seats.
[0034] FIG. 1 is a perspective view of an exemplary bone conduction device 101 with which embodiments of the present invention may be advantageously implemented. The fully functional human hearing anatomy is generally divided up into the outer ear 105, the middle ear 107, and the inner ear 109. The outer ear 105 includes the auricle 111 and the ear canal 113. Sound waves 115 are collected by auricle 111 and channeled into and through ear canal 113. The tympanic membrane 117, which is located at the boundary between the outer ear 105 and the middle ear 107, vibrates in response to the sound waves 107. Within the middle ear 107, vibration of the tympanic membrane 117 is coupled to the fenestra ovalis 119 through three bones, collectively referred to as the ossicles 121. The ossicles 121 filter and amplify the vibrations, thereby causing the fenestra ovalis 119 to articulate. The movement of the fenestra ovalis 119 generates pressure waves in the fluid within cochlea 123, which in turn induces movement in the hairs lining the inside of the cochlea 123. Movement of the hairs generates nerve impulses in spiral ganglion cells to which the hairs are connected, and those nerve
impulses are passed to the auditory nerve 125, and then to the brain (not shown), where they are perceived as sound.
[0035] Bone conduction device 101 is shown positioned behind the auricle 111 of the recipient, although the device could also be positioned in a variety of other positions in the skull of the recipient. Bone conduction device 101 includes an external module 127, and is coupled to the skull of the recipient via an implanted anchor, such as bone screw 129. Bone screw 129 is secured to the skull bone 131 during the implant procedure.
[0036] As discussed in more detail below, connected to external module 127 is a vibratory coupler 133 which secures external module 127 to bone screw 129. As should be appreciated, any appropriate anchor system may be used in lieu of the bone screw 129, so long as the anchor system conducts sufficient vibrations from the bone conduction device 101 for the recipient to perceive the vibrations as sound. For example, as discussed below, the anchor system may be implanted under skin 135 of the recipient, within muscle tissue 137 and/or fat tissue 139. In addition, the material from which the bone anchor is constructed is a matter of design choice. For example, the material may be a metal that does not stimulate an undesirable response of body systems, or it may be any other type of biocompatible material.
[0037] The sound and signal processing components of external module 127 are schematically shown in FIG. 2. Sound waves 203 are received by a sound pickup device 205 and converted into a representative signal, which is directed into a signal processor 207. Signal processor 207 converts the representative signal into an appropriate signal adjusted, as necessary, for the transducer drive circuit 209, which outputs a drive signal to a transducer module 211. Adjustments to the representative signal may include filtering, removal of distortions, reduction of background noises, and the like. Transducer module 211 generates a mechanical vibration representative of the sound waves 203, and these mechanical vibrations are conducted to the skull via a mechanical coupling between transducer module 211, namely vibratory coupler 133, and bone screw 129. An appropriate power module (not shown) is included as part of the external module to provide power to each of the various components.
[0038] A control module 215, having control electronics therein, is electronically connected to sound pickup device 205, signal processor 207, and transducer drive circuit 209. Control module 215 may also be electronically connected to transducer module 211, or any other components of
external module 127. Control module 215 monitors and controls operation of the electronic components and circuits to which it is connected. The amount of control provided by control module 215 may vary depending upon the component or circuit type. Control module 215 may also serve as a feedback loop to provide corrections to the output of any one or more of the components where necessary.
[0039] An interface module 217 is connected to control module 215 to permit the recipient, or a skilled practitioner of the medical arts, to adjust preselected settings of external module 127. The preselected settings may include volume, sound processing strategies, power on/off the device, and the like. Optionally, the interface module and the control module may be integrated into a single module.
[0040] Those skilled in the art will appreciate that, as a matter of design choice, any of the signals between circuits forming part of external module 127 may be transmitted via a wired connection or wirelessly. Further, not all circuits need be housed within a single casing.
[0041] Signal processor 207 may use one or more different techniques or strategies to selectively process, amplify, and/or filter the signal representative of sound waves 203. In certain embodiments, signal processor 207 may be of substantially the same as the sound processor that is used in an air conduction hearing aid. As another option, signal processor 207 may include and analog to digital converter and a digital signal processor.
[0042] FIG. 3 illustrates an exploded view of one embodiment of an external module of a bone conduction device, referred to herein as external module 301. External module 301 shown in FIG. 3 includes an electronics module 303, a transducer module 305, and a battery shoe 307 for powering the electronic components. Electronics module 303 and the transducer module 305 operate as described above. Electronics module 303 includes a printed circuit board 309 (PCB) to electrically connect and mechanically support the various electronic components and circuits. One or more microphones 311 are directly attached to PCB 309 to function as sound pickup devices. Alternatively, other types of direct audio input could be used as the sound pickup devices instead of, or in addition to, microphones 311. Such alternatives include digital or analog audio input ports, a telecoil, and the like.
[0043] The housing for the external module 301 includes a top part 313a and a bottom part 313b. The two housing parts 313a, 313b are configured to mate with one another, leaving an opening
for insertion of battery shoe 307. Following insertion of battery show 307, housing parts 313a, 313b substantially seal the internal components of external module 301 from external elements. The top housing part 313a includes one or more snap-on microphone covers 315, which protect the microphones 311 from dust, dirt and other debris. A user interface 317 is disposed on one side of the top housing part 313A to give the recipient access to the interface module 217 functions.
[0044] The bottom housing part 313b includes an opening 319 for insertion of a fastener (not shown). The fastener secures transducer module 305 to the inside of the bottom housing part 313b, and/or secures a vibratory coupler, such as one of the vibratory couplers shown below, to the outside of the bottom housing part 313b and/or transducer module 305. As such, a direct mechanical connection is established for conduction of vibrations from the transducer module 305 to the vibratory coupler, and from there into the bone anchor. Once the fastener is in place, opening 319 may be sealed against external elements by use of an o-ring or other sealant.
[0045] FIG. 4 illustrates a coupling system in accordance with embodiments of the present invention. As shown, the coupling system comprises a vibratory coupler 403 and an implanted anchor system. In the illustrated embodiment, vibratory coupler 403 extends from an external module 401, sometimes referred to herein as a vibration generating module 401, and is coupled to the implanted anchor system. The implanted anchor system comprises an abutment 405 and an anchor 407, such as bone screw 407. Abutment 405 may be releasably affixed to bone screw 407.
[0046] As shown, abutment 405 extends above tissue 41 1 so that vibratory coupler 403 may be seated on abutment 405. As discussed below, the combination of vibratory coupler 403, abutment 405, and bone screw 407 enable vibrations from external module 401 to be conducted into bone 409.
[0047] Those skilled in the art will recognize that alternate configurations for a bone anchor may also be used instead of the bone screw. One such example is a plate secured to the bone in at least two locations along the edge of the plate, such that the center portion of the plate rests against or is mechanically coupled to the skull bone, thereby enabling vibrations applied to the bone anchor to pass into the bone. With such a bone anchor, the abutment may extend from the center portion of the plate, and forces normal to the skull incident upon the abutment or the
external module would not impact a surgically modified site, but rather would impact an unaltered section of the skull bone.
[0048] The top portion of the abutment 405, which extends above the tissue 411, has a regularly defined cross-section, and may be circular, elliptical, or any other shape according to design preferences. In addition, the radius about the entire cross-section need not be constant. A constant radius may be used in circumstances where it is desired to allow the external module to be mounted with any orientation. On the other hand, a non-constant radius may be used in circumstances where the external module is intended to have only a single orientation when the vibratory coupler is seated on the abutment.
[0049] In the illustrated embodiment, abutment 405 comprises a bearing surface 413 of which extends away from a conduction surface 415. Bearing surface 413 extends away from conduction surface such that an acute angle, or at least a non-orthogonal angle, is formed along the surface of abutment 405. The shapes of bearing surface 413 and the conduction surface 415 are a matter of design choice, however, the conduction surface is preferably planar to facilitate coupling with vibratory coupler 403 and conduction of vibrations. Alternatively, if bearing surface 413 is curved, the bearing surface and conduction surface 415 may intersect tangentially.
[0050] In the illustrated embodiments, as bearing surface 413 extends away from conduction surface 415, a shelf 417 is formed in the bearing surface. The particular geometry of this shelf 417 may vary according to other design considerations, particularly the geometry of vibratory coupler 403. Optionally, and again depending upon the geometry of vibratory coupler 403, shelf 417 may be entirely omitted from abutment 405. In certain embodiments, as shown in FIG. 4, abutment 405 also includes a magnetic material 419 set into the abutment 405 at conduction surface 415. This magnetic material 419 may form part of conduction surface 415, or alternatively, it may be disposed beneath the surface. Moreover, the magnetic material may have any geometrical configuration that suits other design choices that are made concerning abutment 405 and vibratory coupler 403. Magnetic material 419 is preferably magnetizeable material, and not a permanent magnet, although a permanent magnet could be used.
[0051] As noted, vibratory coupler 403 extends outward from external module 401 and includes a magnet 421. Vibratory coupler 403 further includes a conduction surface 423, and a leveraging extension 425. Conduction surface 423 of vibratory coupler 403 has a complimentary shape to
conduction surface 415 of abutment 405, and seats directly on the conduction surface of the abutment such that mechanical contact is made between the two conduction surfaces 415, 423. Magnet 421 in vibratory coupler 403 interacts with the magnetic material 419 in the abutment 405 to retain the two conduction surfaces 415, 423 seated together under normal use conditions. The holding force generated between magnet 421 and magnetic material 419 should be sufficient to maintain the seating under the force generated by the weight of vibratory coupler 403. In addition, the holding force should also be sufficient to maintain the seating when the instantaneous force generated by vibrations from external module 401 are coupled with the weight of vibratory coupler 403.
[0052] Leveraging extension 425 extends away from conduction surface 423 of vibratory coupler 403 such that at least a distal edge 427 of the leveraging extension seats upon the bearing surface 413, and preferably upon shelf 417. Optionally, the entire inner surface of leveraging extension 425 may seat on bearing surface 413. The configuration of the leveraging extension 425 may vary widely. For example, the leveraging extension may form an annular ring at the distal end, or alternatively, the annular ring may be divided up into two, four, or more sections, each section connected to the main body of the vibratory coupler via an arm. In another alternative, the leveraging extension may be a plurality of arms extending away from the main body of the vibratory coupler. In such an embodiment, more arms are preferable, however, as few as two arms will generally suffice.
[0053] FIG. 4B illustrates how the vibratory coupler 403 is decoupled from abutment 405 when a part of the external module 401 is subjected to a force that is tangential to the skull. The tangential force is marked by the arrow, F, and upon incidence of this tangential force on external module 401, conduction surface 423 of the vibratory coupler 403 is pivoted up and away from the conduction surface 415 of abutment 405. This pivoting action is caused by the leveraging extension 425 seated upon the shelf 417 of abutment 405 on the opposite side of vibratory coupler 403 from where the force is incident. Upon application of the force, F, leveraging extension 425 acts as a lever arm, and assists in lifting and magnetically decoupling magnet 421 from magnetic material 419. By causing the decoupling in this manner, the amount of tangential force to which abutment 405 is subjected is significantly reduced.
[0054] The amount of tangential force to which a bone screw may be subjected following implantation, without causing damage to the bone, is illustrated in FIG. 5. Initially, when a bone screw is implanted, the amount of tangential loading force to which it may be subjected is somewhat high. As the healing process begins and continues, the amount of tangential force to which a bone screw may be subjected significantly decreases and then begins increasing to a level that is higher than at the stage of the initial implant. The decrease is at least partially due to the fact that when bones are damaged, the human body first breaks down some of the bone structure surrounding the damaged site before beginning to rebuild and heal the bone. Thus, following implantation of a bone screw, until a physician determines that the implant site is fully healed, if there is significant risk of damaging the bone at the implant site by wearing the external module, then the external module is not generally worn. For prior art bone conduction devices, this is how implant patients proceed—they refrain from regularly using the external module until healing is complete. With the bone conduction fixation system described above, it is anticipated that the external module may be seated upon and used with the implanted bone screw almost immediately following the implant procedure and continuing through the entire healing process.
[0055] An alternative embodiment of a vibratory coupler in accordance with embodiments of the present invention is shown in FIG. 6. In the illustrated embodiment, a sheath 603 extends from housing 605 of external module 601. A coupling arm 607 is partially disposed within sheath 603. Coupling arm 607 is held to the body of external module 601 via a fastener 609, which enables the position of coupling arm 607 relative to housing 605 to be adjusted. A spring 611 is also included within sheath 603 and biases against adjustments made by the fastener 609. As the position of the coupling arm 607 is adjusted, the distal edges 613 of the sheath 603 exert pressure on leveraging extension 615 to cause constriction. By constricting leveraging extension 615, some variation may be introduced in the amount of tangential force required to unseat the vibratory coupler from the abutment, thereby enabling a custom fit for any particular implant recipient.
[0056] FIG. 7 illustrates another embodiment of a vibratory coupler 701 in accordance with embodiments of the present invention. As shown, vibratory coupler 701 includes a sheath 703 is formed of two parts, a first part 705 which extends from body 707 of external module 701, and a second part 709 which is threaded into first part 705. With this arrangement, the overall length
of the sheath 703 is adjustable. Similar to the embodiments described above, coupling arm 711 extends into sheath 703. However, as shown, a post 713 extends from body 707, and the coupling arm 711 slidingly fits onto post 713. A spring 715 disposed within sheath 703 biases the coupling arm 711 toward body 707 of external module 701. Here, constriction of leveraging extension 717 is enabled by lengthening sheath 707 and biasing the coupling arm into the sheath by use of spring 715. Conversely, the amount of constriction may be reduced by shortening sheath 707.
[0057] FIG. 8 illustrates alternative embodiments for an abutment in accordance with embodiments of the present invention, referred to as abutment 801. As described below, Abutment 801 further reduces the amount of tangential force to which the bone screw 803, or other bone anchor, might be subjected.
[0058] Abutment 801 comprises an outer sheath 805 which includes a conduction surface 807 and a bearing surface 809 as described above with reference to FIGS. 4A and 4B. Outer sheath 805 may be constructed of thin walled titanium, or other similar material, which can be laser welded to the bone screw to ensure that the interface between the outer sheath and the bone screw is smooth and does not provide crevices for the lodgment of debris. Outer sheath 805 is constructed to house a plurality of shearing elements, in this case, several stacked plates 811. The plates 811 are not connected to one another, and each may slide laterally with respect to adjacent plates. The plates 811 do not need to be similarly dimensioned. To facilitate sliding, the surfaces of the plates 811 may be polished, or alternatively, a lubricant may be included within outer sheath 805. Further, the material from which plates 811 are constructed is a matter of design choice. For example, they may be constructed from a light weight plastic or polymer material, a biocompatible material, or a heavier metal material. In addition, the plates may be constructed from a magnetizeable material, but preferably not from material that is a permanent magnet, as such a construction is likely to significantly inhibit lateral sliding between adjacent plates.
[0059] Outer sheath 805 serves at least a few purposes in this embodiment. First, outer sheath 805 maintains each plate 811 within the stack in physical contact with each adjacent plate to ensure that abutment 805 is mechanically stiff in a direction normal to the skull. By maintaining such contact, and thereby keeping the stack of plates 805 mechanically stiff, the stack conducts
vibrations from conduction surface 807 through to bone screw 803. Additionally, contact between plates 811 keep each plate from laterally sliding with respect to adjacent plates under normal use conditions. Another purpose of outer sheath 805 is to limit lateral sliding of the plates 811 so that a conduction path is maintained to pass vibrations from the external module to the bone screw 803. Yet another purpose of the outer sheath 805 is to assist in returning plates 811 to the default stack configuration following deformation of the stack when subjected to lateral forces.
[0060] FIG. 8B shows the stack of plates 811 with the top two plates 811a, 811b laterally displaced as a result of a lateral force F. Outer sheath 805 deforms along with the stack of plates 811. To enable outer sheath 805 to return the plates to the default stack configuration, outer sheath 805 may be formed from a shape memory material. Alternatively, springs may be included within outer sheath 805 to aid in biasing the stack of plates 811 toward the default stack configuration. Non-permanent magnets, strategically placed within each stacked plate, could also be used to aid in realignment of the stacked plates into the default stack configuration.
[0061] FIG. 9A shows an alternative arrangement for a plurality of stacked plates 901 which may be used in accordance with embodiments of the present invention. In the illustrated embodiment, each plate is interlocked with adjacent plates. Each plate 901a-d includes an outward extending pin 903 and a slot 905. Plates 901a-d are stacked so that pin 903a-d of each plate 901a-d is inserted into the slot 905a-d of an adjacent plate. The pin 903 of each plate seats within the slot 905 of an adjacent plate as shown in FIG. 9B. The pin 903a on the end plate 901a (as shown), having only a single adjacent plate, may either be omitted from the construction or used for another purpose — lacking an adjacent plate, the pin 903 of the end plate 901a is not inserted into a corresponding slot. As shown, the slot 905a-d in each plate 901 a-d is curved, so that when the stack 901 is subjected to a lateral force, displacement of any one or more plates will also cause rotation of the displaced plates. Such rotation helps to further absorb any incident lateral forces. Because the plates are interlocked, and an outer sheath is not required, although one may be used. Moreover, this embodiment might also be implanted subcutaneously. Such a subcutaneous abutment would necessarily couple with the external module through the skin of the recipient, and all vibrations would be transmitted through tissues, including skin, covering the implant. The pin of the end plate may be used to assist with the coupling.
[0062] Yet another alternative embodiment of an abutment in accordance with embodiments of the present invention is illustrated in FIG. 10. In the illustrated embodiment, abutment 1001 comprises an outer sheath 1003 having an internal cavity 1005 and a granulated material 1007 disposed therein. The granulated material 1007 may any number of different types of material, from sand, to magnetizeable particles, to small beads, whether plastic, glass, or metal and the like. In the case of magnetizeable particles, it is anticipated that the magnet within the external module would align the particles to assist in forming a conduction path between the conduction surface and the bone anchor, while at the same time permitting shearing action between the particles in response to lateral forces incident upon the outer sheath. Additional materials may be included within the cavity to either better enable shearing action of the granulated particles, i.e., movement in the lateral direction in response to lateral forces incident upon the abutment, or to better enable conduction of vibrations from the external module, through the granulated material, to the bone anchor. For example, collagen may be included within the internal cavity, along with beads, to better aid in the transmission of vibrations. It is anticipated that collagen might also aid in improving the shearing action of such beads. As with the previous embodiment, the outer sheath may be constructed using a shape memory material to aid in returning the abutment to a default shape.
[0063] Another embodiment of an abutment in accordance with embodiments of the present invention is illustrated as abutment 1101 in FIG. 11. This abutment includes an outer sheath 1103 with an external profile which is a matter of design choice. Outer sheath 1103 may be formed as shown, it may be formed according to any of the other embodiments discussed herein, or it may have an entirely different shape to suit other design considerations. Outer sheath forms an internal cavity 1105, in which is disposed a proximal plate 1107, a distal plate 1109, a wire 1111, which forms a flexible conduction path, and a spring 1113. The proximal plate 1107 is disposed adjacent to, and may be coupled to, the conduction surface 1115 of outer sheath 1103 such that vibrations applied to conduction surface 1115 pass through to distal plate 1109. Similarly, the distal plate 1109 is disposed adjacent and coupled to bone anchor 1117. The wire 1111 extends between and is coupled to both proximal plate 1107 and distal plate 1109. Likewise, spring 1113 is disposed between proximal and distal plates 1107, 1109, but spring 1113 biases the plates 1107, 1109 away from one another, thereby placing the wire 1111 under
tension and enabling the wire 1111 to conduct vibrations applied to proximal plate 1107 through to the proximal plate 1109, and thus in to the bone anchor 1117.
[0064] Additional wires may be included to form additional conduction paths. The material from which the wire or wires is constructed is a matter of design choice. Those skilled in the art will recognize that certain materials, such as metals and other materials that are less susceptible to permanent deformation due to stretching, are better suited for long term use within the abutment. Those materials that are susceptible to permanent deformation due to stretching may still be used, but abutments employing such materials may require more frequent replacement.
[0065] Yet another embodiment of an abutment 1201 is shown in FIG. 12. In the illustrated embodiment, abutment 1201 includes an outer sheath 1203 forming an internal cavity 1205. As with other embodiments, outer sheath 1203 is preferably constructed using a shape memory material to provide some flexibility, but at the same time be sufficiently rigid to seat a vibratory coupler. Outer sheath 1203 includes a conduction surface 1207 and a distal surface 1209 which is coupled to bone anchor 1211, and vibrations applied to distal surface 1209 are conducted into bone anchor 1211. A conduction axis, A, defines the conduction path along which vibrations pass from an external module to bone anchor 1211 once the external module is seated on the abutment. A spiral spring 1213 and a magnet 1215 are disposed within the cavity 1205. The spiral spring 1213 has an outer end coupled to distal surface 1209, and the magnet 1215 is coupled to the center end of the spiral spring. The magnet 1215 has a magnetic axis, M, defined by the two magnetic poles, N and S, and the spiral spring 1213 biases the magnet 1215 so that the magnetic axis is not parallel to, and is preferably perpendicular to, the conduction axis A. When the vibratory coupler is seated on abutment 1201, a magnet within the vibratory coupler, as described in FIG. 4, induces magnet 1215 in abutment 1201 to rotate and align magnetic axis, M, with the conduction axis, A. Once the magnet 1215 in the abutment 1201 rotates, it is attracted toward the magnet in the vibratory coupler. In addition, magnet 1215 in abutment 1201 will seat against distal surface 1209, thereby enabling vibrations applied to abutment 1201 to pass through to bone anchor 1211.
[0066] Thus, a fixation system for a bone conduction device is disclosed. While embodiments of this invention have been shown and described, it will be apparent to those skilled in the art that
many more modifications are possible without departing from the inventive concepts herein. The invention, therefore, is not to be restricted except in the spirit of the following claims.
[0067] FIG. 13A is cross-sectional view of a coupling system in accordance with embodiments of the present invention. As shown, the coupling system comprises a vibratory coupler 1306 attached to, and extending from, an external module 1301 of a bone conduction device. Disposed within vibratory coupler 1306 is a magnet 1308. Implanted within skin 1302 is an implanted anchor 1310. Vibration generated by external module 1301 is coupled through implanted anchor 1310 to the skull 1304.
[0068] In the illustrated embodiments, implanted anchor 1310 comprises a plurality of particles, beads, or other elements 1310 which are injected or implanted into skin 1302. The plurality of particles 1310 alter the material stiffness of the skin so that the vibration from vibrator coupler 1306 may be transferred to the skull 1304 with little to no loss, thus eliminating the need for an exposed abutment.
[0069] Any of a variety of particles may be injected or implanted into skin 1302 of a recipient. In certain embodiments, skin 1302 is stiffened by injecting a sufficient quantity of ceramic or metallic powder (e.g., titanium powder, platinum powder, etc) into the skin. In other embodiments, collagen or any other bioresorable material that may provide stiffness to skin 1302 may be used. For example, in certain embodiments, particles that enhance fibrous tissue growth may be injected or implanted into skin 1302.
[0070] As noted, in the illustrated embodiment, a magnet 1308 is disposed within vibratory coupler 1306. Magnet 1308 is configured to provide an attraction force between vibratory coupler 1306 and particles 1310. This attraction retains external module 1301 in position during normal use, and is sufficient to attach external module 1301 to the recipient under the force generated by the weight of vibratory coupler 1306. In addition, the attraction force should also be sufficient to maintain the attachment when the instantaneous force generated by vibrations from external module 1301 are coupled with the weight of vibratory coupler 1306. In certain embodiments, magnet 1308 may comprise a permanent magnet. In other embodiments, magnet 1308 may comprise a magnetic material that is not a permanent magnet.
[0071] In further embodiments, particles 1310 are prevented from migrating from the injection site. In one such embodiment, the particles may be tied to one another prior to
injection/implantation. In another such embodiment, the particles may be coated with collagen to prevent migration. Other particles comprising, such as silicone particles, may promote tissue in-growth there with to prevent migration.
[0072] FIG. 13B is cross-sectional view of a coupling system in accordance with embodiments of the present invention. In this embodiment, implanted anchor 1318 comprises a granulated material 1322 bounded by a volume 1320. The granulated material 1322 may any number of different types of material, from sand, to magnetizeable particles, to small beads, whether plastic, glass, or metal and the like. Volume 1320 may comprise, for example, a surgically implanted mesh or cage 1320 which prevents migration of granulated material 1322.
[0073] Similar to the embodiments described above with reference to FIG. 13 A, a magnet 1308 is disposed within vibratory coupler 1306. Magnet 1308 is configured to provide an attraction force between vibratory coupler 1306 and particles 1310. This attraction retains external module 1301 in position during normal use, and is sufficient to attach external module 1301 to the recipient under the force generated by the weight of vibratory coupler 1306. In addition, the attraction force should also be sufficient to maintain the attachment when the instantaneous force generated by vibrations from external module 1301 are coupled with the weight of vibratory coupler 1306. In certain embodiments, magnet 1308 may comprise a permanent magnet. In other embodiments, magnet 1308 may comprise a magnetic material that is not a permanent magnet.
[0074] FIG. 13C is cross-sectional view of a coupling system in accordance with embodiments of the present invention. Similar to the embodiments described above with reference to FIG. 13B, a granulated material 1334 bounded by a volume 1336. The granulated material 1322 may any number of different types of material. Implanted anchor 1332 further comprises a magnet 1330 adjacent skull 1304. Vibratory coupler 1306 comprises a permanent magnet 1328. When vibratory coupler 1306 is positioned adjacent skin 1302, magnets 1330 and 1328 cause granulated material 1334 to be substantially aligned, thereby improving the transmission of vibration there through.
[0075] While various embodiments of the present invention have been described above, it should be understood that they have been presented by way of example only, and not limitation. It will be apparent to persons skilled in the relevant art that various changes in form and detail can be
made therein without departing from the spirit and scope of the invention. Thus, the breadth and scope of the present invention should not be limited by any of the above-described exemplary embodiments, but should be defined only in accordance with the following claims and their equivalents. All patents and publications discussed herein are incorporated in their entirety by reference thereto.
Claims
1. A fixation system for a bone conduction device comprising: a bone anchor configured to be implanted in a recipient of the bone conduction device; an abutment coupled to the bone anchor defining a conduction path to the bone anchor such that vibrations applied to the abutment are transferred to the bone anchor, the abutment comprising a plurality of inter-locking stacked plates disposed adjacent the bone anchor forming part of the conduction path; and a vibratory coupler extending from the bone conduction device, comprising a second conduction surface and a magnet, wherein the magnet attracts to the abutment so as to couple the second conduction surface to the abutment, thereby enabling vibrations to pass through the conduction path, wherein the plates are configured to laterally slide with respect to another in response to tangential forces incident upon the abutment.
2. The fixation system of claim 1, wherein the plurality of stacked plates comprise first and second end plates and one or more intermediate plates, and wherein each of the intermediate plates comprise a slot and a pin and the end plates comprise at least one of a slot and a pin, and wherein the pin of each plate extends through the slot of an adjacent plate, and the pin and slot combination of adjacent plates limit lateral sliding between adjacent plates.
3. The fixation system of claim 1, wherein the abutment further comprises a deformable sheath covering the stacked plates.
4. The fixation system of claim 3, wherein the deformable sheath is adapted to maintain each stacked plate in contact with adjacent stacked plates.
5. The fixation system of claim 1, wherein the abutment further comprises: a first conduction surface; and a magnetic material at or near the first conduction surface, wherein the magnet attracts to the magnetic material.
6. The fixation system of claim 1 , wherein the plates comprise a magnetic material, and wherein the magnet attracts to the magnetic material.
7. The fixation system of claim 1, wherein the abutment further comprises one or more elements disposed therein to facilitate sliding of adjacent plates.
8. The fixation system of claim 5, wherein the abutment further comprises a bearing surface and a first conduction surface that are formed as part of the deformable sheath.
9. The fixation system of claim 8, wherein the bearing surface is adjacent to the first conduction surface and intersects the first conduction surface at a non-orthogonal angle.
10. The fixation system of claim 8, wherein the vibratory coupler further comprises a leveraging extension, and wherein when the second conduction surface is seated on the first conduction surface at least a distal edge of the leveraging extension seats upon the bearing surface.
11. The fixation system of claim 8, wherein the bearing surface and the first conduction surface have different radii of curvatures.
12. The fixation system of claim 1, wherein the first conduction surface is substantially planar.
13. The fixation system of claim 1, wherein the bearing surface comprises a shelf on which the leveraging extension seats when the second conduction surface is seated on the first conduction surface.
14. An implantable anchor for coupling a vibratory coupler extending from the bone conduction device to a recipient, the bone conduction device comprising a second conduction surface and a magnet, the anchor comprising: a bone anchor configured to be implanted in the recipient of the bone conduction device; and an abutment coupled to the bone anchor defining a conduction path to the bone anchor such that vibrations applied to the abutment are transferred to the bone anchor, the abutment comprising a plurality of inter-locking stacked plates disposed adjacent the bone anchor forming part of the conduction path; wherein when the second conduction surface is adjacent the abutment the magnet attracts to the abutment so as to couple the second conduction surface to the abutment, thereby enabling vibrations to pass through the conduction path, and wherein the plates are configured to laterally slide with respect to another in response to tangential forces incident upon the abutment.
15. The anchor of claim 14, wherein the plurality of stacked plates comprise first and second end plates and one or more intermediate plates, and wherein each of the intermediate plates comprise a slot and a pin and the end plates comprise at least one of a slot and a pin, and wherein the pin of each plate extends through the slot of an adjacent plate, and the pin and slot combination of adjacent plates limit lateral sliding between adjacent plates.
16. The anchor of claim 14, wherein the abutment further comprises a deformable sheath covering the stacked plates.
17. The anchor of claim 15, wherein the deformable sheath is adapted to maintain each stacked plate in contact with adjacent stacked plates.
18. The anchor of claim 14, wherein the abutment further comprises: a first conduction surface; and a magnetic material at or near the first conduction surface, wherein the magnet attracts to the magnetic material.
19. The anchor of claim 14, wherein the plates comprise a magnetic material, and wherein the magnet attracts to the magnetic material.
20. The anchor of claim 14, wherein the abutment further comprises one or more elements disposed therein to facilitate sliding of adjacent plates.
21. The anchor of claim 16, wherein the abutment further comprises a bearing surface and a first conduction surface that are formed as part of the deformable sheath.
22. The anchor of claim 21, wherein the bearing surface is adjacent to the first conduction surface and intersects the first conduction surface at a non-orthogonal angle.
23. The anchor of claim 21, wherein the vibratory coupler further comprises a leveraging extension, and wherein when the second conduction surface is seated on the first conduction surface at least a distal edge of the leveraging extension seats upon the bearing surface.
24. The anchor of claim 21, wherein the bearing surface and the first conduction surface have different radii of curvatures.
25. The anchor of claim 14, wherein the first conduction surface is substantially planar.
26. The anchor of claim 23, wherein the bearing surface comprises a shelf on which the leveraging extension seats when the second conduction surface is seated on the first conduction surface.
Applications Claiming Priority (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US4118508P | 2008-03-31 | 2008-03-31 | |
US61/041,185 | 2008-03-31 | ||
US12/167,871 | 2008-07-03 | ||
US12/167,871 US8852251B2 (en) | 2008-03-31 | 2008-07-03 | Mechanical fixation system for a prosthetic device |
Publications (2)
Publication Number | Publication Date |
---|---|
WO2009121097A1 WO2009121097A1 (en) | 2009-10-08 |
WO2009121097A9 true WO2009121097A9 (en) | 2009-11-05 |
Family
ID=41117259
Family Applications (23)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/AU2009/000355 WO2009121101A1 (en) | 2008-03-31 | 2009-03-26 | Bone conduction hearing device having acoustic feedback reduction system |
PCT/AU2009/000350 WO2009121097A1 (en) | 2008-03-31 | 2009-03-26 | Mechanical fixation system for a prosthetic device |
PCT/AU2009/000351 WO2009121098A1 (en) | 2008-03-31 | 2009-03-26 | Tissue injection fixation system for a prosthetic device |
PCT/AU2009/000358 WO2009121104A1 (en) | 2008-03-31 | 2009-03-27 | A mechanically amplified piezoelectric transducer |
PCT/AU2009/000363 WO2009121109A1 (en) | 2008-03-31 | 2009-03-27 | Tangential force resistant coupling for a prosthetic device |
PCT/AU2009/000359 WO2009121105A1 (en) | 2008-03-31 | 2009-03-27 | Piercing conducted bone conduction device |
PCT/AU2009/000360 WO2009121106A1 (en) | 2008-03-31 | 2009-03-27 | Dual percutaneous anchors bone conduction device |
PCT/AU2009/000362 WO2009121108A1 (en) | 2008-03-31 | 2009-03-27 | Coupling system for a prosthetic device |
PCT/AU2009/000372 WO2009121116A1 (en) | 2008-03-31 | 2009-03-30 | A piezoelectric bone conduction device having enhanced transducer stroke |
PCT/AU2009/000365 WO2009121111A1 (en) | 2008-03-31 | 2009-03-30 | Bone conduction hearing device having acoustic feedback reduction system |
PCT/AU2009/000369 WO2009121115A1 (en) | 2008-03-31 | 2009-03-30 | Bone conduction devices generating tangentially-directed mechanical force using a linearly moving mass |
PCT/AU2009/000374 WO2009121118A1 (en) | 2008-03-31 | 2009-03-30 | Hearing device having one or more in-the-canal vibrating extensions |
PCT/AU2009/000367 WO2009121113A1 (en) | 2008-03-31 | 2009-03-30 | Alternative mass arrangements for bone conduction devices |
PCT/AU2009/000373 WO2009121117A1 (en) | 2008-03-31 | 2009-03-30 | Transcutaneous magnetic bone conduction device |
PCT/AU2009/000368 WO2009121114A1 (en) | 2008-03-31 | 2009-03-30 | Customizable mass arrangements for bone conduction devices |
PCT/US2009/038933 WO2009124036A2 (en) | 2008-03-31 | 2009-03-31 | Manufacturing implantable medical components |
PCT/US2009/038884 WO2009124008A1 (en) | 2008-03-31 | 2009-03-31 | Bone conduction device for a single sided deaf recipient |
PCT/US2009/038937 WO2009124038A1 (en) | 2008-03-31 | 2009-03-31 | A bimodal hearing prosthesis |
PCT/US2009/038879 WO2009124005A2 (en) | 2008-03-31 | 2009-03-31 | Bone conduction device fitting |
PCT/US2009/038932 WO2009124035A2 (en) | 2008-03-31 | 2009-03-31 | Objective fiting of a hearing prosthesis |
PCT/US2009/038942 WO2009124042A2 (en) | 2006-05-25 | 2009-03-31 | Pharmaceutical agent delivery in a stimulating medical device |
PCT/US2009/038893 WO2010008630A1 (en) | 2008-03-31 | 2009-03-31 | Implantable universal docking station for prosthetic hearing devices |
PCT/US2009/038890 WO2009124010A2 (en) | 2008-03-31 | 2009-03-31 | Bone conduction device fitting |
Family Applications Before (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/AU2009/000355 WO2009121101A1 (en) | 2008-03-31 | 2009-03-26 | Bone conduction hearing device having acoustic feedback reduction system |
Family Applications After (21)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/AU2009/000351 WO2009121098A1 (en) | 2008-03-31 | 2009-03-26 | Tissue injection fixation system for a prosthetic device |
PCT/AU2009/000358 WO2009121104A1 (en) | 2008-03-31 | 2009-03-27 | A mechanically amplified piezoelectric transducer |
PCT/AU2009/000363 WO2009121109A1 (en) | 2008-03-31 | 2009-03-27 | Tangential force resistant coupling for a prosthetic device |
PCT/AU2009/000359 WO2009121105A1 (en) | 2008-03-31 | 2009-03-27 | Piercing conducted bone conduction device |
PCT/AU2009/000360 WO2009121106A1 (en) | 2008-03-31 | 2009-03-27 | Dual percutaneous anchors bone conduction device |
PCT/AU2009/000362 WO2009121108A1 (en) | 2008-03-31 | 2009-03-27 | Coupling system for a prosthetic device |
PCT/AU2009/000372 WO2009121116A1 (en) | 2008-03-31 | 2009-03-30 | A piezoelectric bone conduction device having enhanced transducer stroke |
PCT/AU2009/000365 WO2009121111A1 (en) | 2008-03-31 | 2009-03-30 | Bone conduction hearing device having acoustic feedback reduction system |
PCT/AU2009/000369 WO2009121115A1 (en) | 2008-03-31 | 2009-03-30 | Bone conduction devices generating tangentially-directed mechanical force using a linearly moving mass |
PCT/AU2009/000374 WO2009121118A1 (en) | 2008-03-31 | 2009-03-30 | Hearing device having one or more in-the-canal vibrating extensions |
PCT/AU2009/000367 WO2009121113A1 (en) | 2008-03-31 | 2009-03-30 | Alternative mass arrangements for bone conduction devices |
PCT/AU2009/000373 WO2009121117A1 (en) | 2008-03-31 | 2009-03-30 | Transcutaneous magnetic bone conduction device |
PCT/AU2009/000368 WO2009121114A1 (en) | 2008-03-31 | 2009-03-30 | Customizable mass arrangements for bone conduction devices |
PCT/US2009/038933 WO2009124036A2 (en) | 2008-03-31 | 2009-03-31 | Manufacturing implantable medical components |
PCT/US2009/038884 WO2009124008A1 (en) | 2008-03-31 | 2009-03-31 | Bone conduction device for a single sided deaf recipient |
PCT/US2009/038937 WO2009124038A1 (en) | 2008-03-31 | 2009-03-31 | A bimodal hearing prosthesis |
PCT/US2009/038879 WO2009124005A2 (en) | 2008-03-31 | 2009-03-31 | Bone conduction device fitting |
PCT/US2009/038932 WO2009124035A2 (en) | 2008-03-31 | 2009-03-31 | Objective fiting of a hearing prosthesis |
PCT/US2009/038942 WO2009124042A2 (en) | 2006-05-25 | 2009-03-31 | Pharmaceutical agent delivery in a stimulating medical device |
PCT/US2009/038893 WO2010008630A1 (en) | 2008-03-31 | 2009-03-31 | Implantable universal docking station for prosthetic hearing devices |
PCT/US2009/038890 WO2009124010A2 (en) | 2008-03-31 | 2009-03-31 | Bone conduction device fitting |
Country Status (4)
Country | Link |
---|---|
US (28) | US8401213B2 (en) |
EP (6) | EP2269241A1 (en) |
CN (1) | CN102047692B (en) |
WO (23) | WO2009121101A1 (en) |
Families Citing this family (227)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8260430B2 (en) | 2010-07-01 | 2012-09-04 | Cochlear Limited | Stimulation channel selection for a stimulating medical device |
AUPS318202A0 (en) | 2002-06-26 | 2002-07-18 | Cochlear Limited | Parametric fitting of a cochlear implant |
US7561920B2 (en) | 2004-04-02 | 2009-07-14 | Advanced Bionics, Llc | Electric and acoustic stimulation fitting systems and methods |
WO2005122887A2 (en) | 2004-06-15 | 2005-12-29 | Cochlear Americas | Automatic determination of the threshold of an evoked neural response |
US7801617B2 (en) | 2005-10-31 | 2010-09-21 | Cochlear Limited | Automatic measurement of neural response concurrent with psychophysics measurement of stimulating device recipient |
US8401212B2 (en) | 2007-10-12 | 2013-03-19 | Earlens Corporation | Multifunction system and method for integrated hearing and communication with noise cancellation and feedback management |
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 |
SE531053C2 (en) * | 2007-05-24 | 2008-12-02 | Cochlear Ltd | Vibrator |
DE102007031872B4 (en) * | 2007-07-09 | 2009-11-19 | Siemens Audiologische Technik Gmbh | hearing Aid |
WO2009015103A1 (en) | 2007-07-20 | 2009-01-29 | Cochlear Americas | 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 |
US8190271B2 (en) | 2007-08-29 | 2012-05-29 | Advanced Bionics, Llc | Minimizing trauma during and after insertion of a cochlear lead |
US8401213B2 (en) * | 2008-03-31 | 2013-03-19 | Cochlear Limited | Snap-lock coupling system for a prosthetic device |
DK2301261T3 (en) | 2008-06-17 | 2019-04-23 | Earlens Corp | Optical electromechanical hearing aids with separate power supply and signal components |
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 |
WO2010033933A1 (en) | 2008-09-22 | 2010-03-25 | Earlens Corporation | Balanced armature devices and methods for hearing |
DE102009014770A1 (en) * | 2009-03-25 | 2010-09-30 | Cochlear Ltd., Lane Cove | vibrator |
USRE48797E1 (en) | 2009-03-25 | 2021-10-26 | Cochlear Limited | Bone conduction device having a multilayer piezoelectric element |
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 |
CN102458323B (en) * | 2009-06-09 | 2015-05-06 | 达尔豪西大学 | Subcutaneous piezoelectric bone conduction hearing aid actuator and system |
US8965021B2 (en) * | 2009-06-09 | 2015-02-24 | Dalhousie University | Subcutaneous piezoelectric bone conduction hearing aid actuator and system |
EP2490636A1 (en) * | 2009-10-21 | 2012-08-29 | Woodwelding AG | Method of anchoring an acoustic element in a bone of the craniomaxillofacial region and acoustic element |
JP5530528B2 (en) * | 2009-11-10 | 2014-06-25 | マサチューセッツ インスティテュート オブ テクノロジー | Buckling type phased array 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 |
US9301059B2 (en) | 2010-06-07 | 2016-03-29 | Advanced Bionics Ag | Bone conduction hearing aid system |
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 |
KR101824822B1 (en) * | 2010-12-27 | 2018-02-01 | 로무 가부시키가이샤 | Transmitter/receiver unit and receiver unit |
US9313306B2 (en) | 2010-12-27 | 2016-04-12 | Rohm Co., Ltd. | Mobile telephone cartilage conduction unit for making contact with the ear cartilage |
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 |
CN103503484B (en) | 2011-03-23 | 2017-07-21 | 耳蜗有限公司 | The allotment of hearing device |
US9107013B2 (en) | 2011-04-01 | 2015-08-11 | Cochlear Limited | Hearing prosthesis with a piezoelectric actuator |
US9872990B2 (en) | 2011-05-13 | 2018-01-23 | Saluda Medical Pty Limited | Method and apparatus for application of a neural stimulus |
US9974455B2 (en) | 2011-05-13 | 2018-05-22 | Saluda Medical Pty Ltd. | Method and apparatus for estimating neural recruitment |
CN103648583B (en) | 2011-05-13 | 2016-01-20 | 萨鲁达医疗有限公司 | For measuring method and the instrument of nerves reaction-A |
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 |
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 |
US20130018218A1 (en) * | 2011-07-14 | 2013-01-17 | Sophono, Inc. | Systems, Devices, Components and Methods for Bone Conduction Hearing Aids |
US20130030242A1 (en) * | 2011-07-26 | 2013-01-31 | Michael R. Ruehring | Dog anxiety relief bone conduction audio device, system |
US11843918B2 (en) * | 2011-10-11 | 2023-12-12 | Cochlear Limited | 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 |
US9210521B2 (en) * | 2012-07-16 | 2015-12-08 | Sophono, Inc. | Abutment attachment systems, mechanisms, devices, components and methods for bone conduction hearing aids |
US9022917B2 (en) | 2012-07-16 | 2015-05-05 | Sophono, Inc. | Magnetic spacer systems, devices, components and methods for bone conduction hearing aids |
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 |
US9031274B2 (en) | 2012-09-06 | 2015-05-12 | Sophono, Inc. | Adhesive bone conduction hearing device |
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 |
US9258656B2 (en) | 2011-12-09 | 2016-02-09 | Sophono, Inc. | Sound acquisition and analysis systems, devices and components for magnetic 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 |
AU2012358871B2 (en) * | 2011-12-22 | 2015-06-18 | Med-El Elektromedizinische Geraete Gmbh | Magnet arrangement for bone conduction hearing implant |
US11528562B2 (en) | 2011-12-23 | 2022-12-13 | Shenzhen Shokz Co., Ltd. | Bone conduction speaker and compound vibration device thereof |
US11575994B2 (en) | 2011-12-23 | 2023-02-07 | Shenzhen Shokz Co., Ltd. | Bone conduction speaker and compound vibration device thereof |
US11595760B2 (en) | 2011-12-23 | 2023-02-28 | Shenzhen Shokz Co., Ltd. | Bone conduction speaker and compound vibration device thereof |
US11638099B2 (en) | 2011-12-23 | 2023-04-25 | Shenzhen Shokz Co., Ltd. | Bone conduction speaker and compound vibration device thereof |
US11483661B2 (en) | 2011-12-23 | 2022-10-25 | Shenzhen Shokz Co., Ltd. | Bone conduction speaker and compound vibration device thereof |
US11665482B2 (en) | 2011-12-23 | 2023-05-30 | Shenzhen Shokz Co., Ltd. | Bone conduction speaker and compound vibration device thereof |
US11611834B2 (en) | 2011-12-23 | 2023-03-21 | Shenzhen Shokz Co., Ltd. | Bone conduction speaker and compound vibration device thereof |
US11540066B2 (en) | 2011-12-23 | 2022-12-27 | Shenzhen Shokz Co., Ltd. | Bone conduction speaker and compound vibration device thereof |
US11343626B2 (en) | 2011-12-23 | 2022-05-24 | Shenzhen Shokz Co., Ltd. | Bone conduction speaker and compound vibration device thereof |
US11540057B2 (en) | 2011-12-23 | 2022-12-27 | Shenzhen Shokz Co., Ltd. | Bone conduction speaker and compound vibration device thereof |
US11601761B2 (en) | 2011-12-23 | 2023-03-07 | Shenzhen Shokz Co., Ltd. | Bone conduction speaker and compound vibration device thereof |
US11399234B2 (en) | 2011-12-23 | 2022-07-26 | Shenzhen Shokz Co., Ltd. | Bone conduction speaker and compound vibration device thereof |
US11641552B2 (en) | 2011-12-23 | 2023-05-02 | Shenzhen Shokz Co., Ltd. | Bone conduction speaker and compound vibration device thereof |
US11641551B2 (en) | 2011-12-23 | 2023-05-02 | Shenzhen Shokz Co., Ltd. | Bone conduction speaker and compound vibration device thereof |
US11463814B2 (en) | 2011-12-23 | 2022-10-04 | Shenzhen Shokz Co., Ltd. | Bone conduction speaker and compound vibration device thereof |
US11716575B2 (en) | 2011-12-23 | 2023-08-01 | Shenzhen Shokz Co., Ltd. | Bone conduction speaker and compound vibration device thereof |
US9241205B2 (en) * | 2011-12-27 | 2016-01-19 | Kyocera Corporation | Vibration device, sound generator, speaker system, and electronic device |
TWI660618B (en) | 2012-01-20 | 2019-05-21 | 日商精良股份有限公司 | Mobile phone |
US8891795B2 (en) | 2012-01-31 | 2014-11-18 | Cochlear Limited | Transcutaneous bone conduction device vibrator having movable magnetic mass |
ES2906620T3 (en) | 2012-03-12 | 2022-04-19 | Hospital For Sick Children | Systems and methods for balance stabilization |
US9380379B1 (en) | 2012-03-14 | 2016-06-28 | Google Inc. | Bone-conduction anvil and diaphragm |
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 |
WO2013179274A2 (en) * | 2012-05-31 | 2013-12-05 | Cochlear Limited | Convertibility of a bone conduction device |
KR101836023B1 (en) | 2012-06-29 | 2018-03-07 | 로무 가부시키가이샤 | Stereo earphone |
WO2014011217A2 (en) * | 2012-07-09 | 2014-01-16 | Vibrant Med-El Hearing Technology Gmbh | Electromagnetic bone conduction 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 |
US9049515B2 (en) * | 2012-10-08 | 2015-06-02 | Keith Allen Clow | Wireless communication device |
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 |
AU2013344311B2 (en) | 2012-11-06 | 2017-11-30 | Saluda Medical Pty Ltd | Method and system for controlling electrical conditions of tissue |
SG11201503060SA (en) * | 2012-12-21 | 2015-05-28 | Widex As | Hearing aid fitting system and a method of fitting a hearing aid system |
US20140179985A1 (en) * | 2012-12-21 | 2014-06-26 | Marcus ANDERSSON | Prosthesis adapter |
US11095994B2 (en) | 2013-02-15 | 2021-08-17 | Cochlear Limited | Conformable pad bone conduction device |
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 |
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 |
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 |
CN105307719B (en) | 2013-05-30 | 2018-05-29 | 格雷厄姆·H.·克雷西 | Local nerve stimulation instrument |
US11229789B2 (en) | 2013-05-30 | 2022-01-25 | Neurostim Oab, Inc. | Neuro activator with controller |
EP3036917A1 (en) * | 2013-08-19 | 2016-06-29 | Advanced Bionics AG | Device and method for neural cochlea stimulation |
CN108551507A (en) * | 2013-08-23 | 2018-09-18 | 罗姆股份有限公司 | Exhalation/incoming call communication, receiver, earphone, business card, non-contact IC card, mobile phone and its application method |
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 |
US11412334B2 (en) * | 2013-10-23 | 2022-08-09 | Cochlear Limited | Contralateral sound capture with respect to stimulation energy source |
US9705548B2 (en) | 2013-10-24 | 2017-07-11 | Rohm Co., Ltd. | Wristband-type handset and wristband-type alerting device |
DE102013112319A1 (en) * | 2013-11-08 | 2015-05-13 | Cortec Gmbh | Holding device for the body-external transmitter unit |
EP3071100B1 (en) | 2013-11-22 | 2024-01-03 | Saluda Medical Pty Limited | Method and device for detecting a neural response in a neural measurement |
WO2015090352A1 (en) * | 2013-12-16 | 2015-06-25 | Phonak Ag | Method and apparatus for fitting a hearing device |
US11375324B2 (en) | 2014-01-06 | 2022-06-28 | Shenzhen Shokz Co., Ltd. | Systems and methods for suppressing sound leakage |
US11418895B2 (en) | 2014-01-06 | 2022-08-16 | Shenzhen Shokz Co., Ltd. | Systems and methods for suppressing sound leakage |
US11368801B2 (en) | 2014-01-06 | 2022-06-21 | Shenzhen Shokz Co., Ltd. | Systems and methods for suppressing sound leakage |
US11363392B2 (en) | 2014-01-06 | 2022-06-14 | Shenzhen Shokz Co., Ltd. | Systems and methods for suppressing sound leakage |
US11368800B2 (en) | 2014-01-06 | 2022-06-21 | Shenzhen Shokz Co., Ltd. | Systems and methods for suppressing sound leakage |
EP2897378B1 (en) * | 2014-01-21 | 2020-08-19 | Oticon Medical A/S | Hearing aid device using dual electromechanical vibrator |
US11240613B2 (en) | 2014-01-30 | 2022-02-01 | Cochlear Limited | Bone conduction implant |
WO2015130318A1 (en) | 2014-02-28 | 2015-09-03 | Advanced Bionics Ag | Systems and methods 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 |
DK3550857T3 (en) * | 2014-03-28 | 2020-11-30 | Oticon Medical As | Magnetic device for bone conduction hearing aids |
US20150287043A1 (en) * | 2014-04-02 | 2015-10-08 | Avaya Inc. | Network-based identification of device usage patterns that can indicate that the user has a qualifying disability |
US10272215B2 (en) * | 2014-04-07 | 2019-04-30 | Boehringer Ingelheim International Gmbh | Inhalation training device and system for practicing of an inhalation process of a patient |
DK3129087T3 (en) | 2014-04-07 | 2020-05-25 | Boehringer Ingelheim Int | PROCEDURE, ELECTRONIC DEVICE, INHALATION TRAINING SYSTEM TO EXERCISE AND / OR CONTROL A PATIENT INHALATION PROCESS |
US9998837B2 (en) | 2014-04-29 | 2018-06-12 | Cochlear Limited | Percutaneous vibration conductor |
US10368762B2 (en) | 2014-05-05 | 2019-08-06 | Saluda Medical Pty Ltd. | Neural measurement |
DK3149967T3 (en) | 2014-05-27 | 2020-11-30 | Sophono Inc | SYSTEMS, DEVICES, COMPONENTS AND METHODS OF REDUCING FEEDBACK BETWEEN MICROPHONES AND TRANSDUCERS IN CONDUCTIVE MAGNETIC HEARING AID |
GB201409547D0 (en) * | 2014-05-29 | 2014-07-16 | Gill Instr Ltd | An electroacoustic transducer |
WO2015191047A1 (en) | 2014-06-10 | 2015-12-17 | The Regents Of The University Of Michigan | Mechanical amplifier for energy harvester |
US20150367130A1 (en) * | 2014-06-18 | 2015-12-24 | Cochlear Limited | Internal pressure management system |
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 |
WO2016011044A1 (en) | 2014-07-14 | 2016-01-21 | Earlens Corporation | Sliding bias and peak limiting for optical hearing devices |
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 |
US9924276B2 (en) | 2014-11-26 | 2018-03-20 | Earlens Corporation | Adjustable venting for hearing instruments |
EP3218046B1 (en) | 2014-12-11 | 2024-04-17 | Saluda Medical Pty Ltd | Device and computer program for feedback control of neural stimulation |
WO2016098820A1 (en) | 2014-12-18 | 2016-06-23 | ローム株式会社 | Cartilage conduction hearing device using electromagnetic-type vibration unit, and electromagnetic-type vibration unit |
CN104507039B (en) * | 2014-12-27 | 2019-03-01 | 北京智谷睿拓技术服务有限公司 | Communication means and user equipment |
US11077301B2 (en) | 2015-02-21 | 2021-08-03 | NeurostimOAB, Inc. | Topical nerve stimulator and sensor for bladder control |
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 |
US20180110985A1 (en) | 2015-05-28 | 2018-04-26 | Jeryle L. Walter | Cochlear implants having mri-compatible magnet apparatus and associated methods |
TW201711713A (en) * | 2015-06-03 | 2017-04-01 | 賽諾菲阿凡提斯德意志有限公司 | Drug delivery device |
TW201707737A (en) | 2015-06-03 | 2017-03-01 | 賽諾菲阿凡提斯德意志有限公司 | Drug delivery device |
TW201709941A (en) * | 2015-06-03 | 2017-03-16 | 賽諾菲阿凡提斯德意志有限公司 | Audible indicator |
TW201709940A (en) * | 2015-06-03 | 2017-03-16 | 賽諾菲阿凡提斯德意志有限公司 | Audible indicator |
US9992584B2 (en) * | 2015-06-09 | 2018-06-05 | Cochlear Limited | Hearing prostheses for single-sided deafness |
US10130807B2 (en) | 2015-06-12 | 2018-11-20 | Cochlear Limited | Magnet management MRI compatibility |
US20160381473A1 (en) | 2015-06-26 | 2016-12-29 | Johan Gustafsson | Magnetic retention device |
WO2017010547A1 (en) | 2015-07-15 | 2017-01-19 | ローム株式会社 | Robot and robot system |
JP6651608B2 (en) | 2015-08-13 | 2020-02-19 | シェンヂェン ボクステック カンパニー リミテッドShenzhen Voxtech Co., Ltd | System for bone conduction speaker |
US9872115B2 (en) * | 2015-09-14 | 2018-01-16 | Cochlear Limited | Retention magnet system for medical device |
US10917730B2 (en) | 2015-09-14 | 2021-02-09 | Cochlear Limited | Retention magnet system for medical device |
JP6551929B2 (en) | 2015-09-16 | 2019-07-31 | 株式会社ファインウェル | Watch with earpiece function |
US9980066B2 (en) * | 2015-09-18 | 2018-05-22 | Med-El Elektromedizinische Geraete Gmbh | Bone conduction transducer system with adjustable retention force |
US10412510B2 (en) | 2015-09-25 | 2019-09-10 | Cochlear Limited | Bone conduction devices utilizing multiple actuators |
US20170095202A1 (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 |
WO2017087004A1 (en) | 2015-11-20 | 2017-05-26 | Advanced Bionics Ag | Cochlear implants and magnets for use with same |
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 |
US10532209B2 (en) | 2015-12-18 | 2020-01-14 | Advanced Bionics Ag | Cochlear implants having MRI-compatible magnet apparatus and associated methods |
WO2017105511A1 (en) | 2015-12-18 | 2017-06-22 | Advanced Bionics Ag | Cochlear implants having mri-compatible magnet apparatus |
US10178483B2 (en) | 2015-12-30 | 2019-01-08 | Earlens Corporation | Light based hearing systems, apparatus, and methods |
US11350226B2 (en) | 2015-12-30 | 2022-05-31 | Earlens Corporation | Charging protocol for rechargeable hearing systems |
US10492010B2 (en) | 2015-12-30 | 2019-11-26 | Earlens Corporations | Damping in contact hearing systems |
KR102108668B1 (en) | 2016-01-19 | 2020-05-07 | 파인웰 씨오., 엘티디 | Pen-type handset |
WO2017139891A1 (en) | 2016-02-17 | 2017-08-24 | Dalhousie University | Piezoelectric inertial actuator |
US11071869B2 (en) | 2016-02-24 | 2021-07-27 | Cochlear Limited | Implantable device having removable portion |
WO2018017515A1 (en) * | 2016-07-19 | 2018-01-25 | Med-El Elektromedizinische Geraete Gmbh | Opto-acoustic selective mechanical stimulation of the vestibular system |
US10123138B2 (en) | 2016-07-26 | 2018-11-06 | Cochlear Limited | Microphone isolation in a bone conduction device |
RU2722433C1 (en) * | 2016-08-17 | 2020-05-29 | Скотт Технолоджис, Инк. | Respiratory mask with integrated transducer whose principle of action is based on bone conductivity |
CN109952771A (en) | 2016-09-09 | 2019-06-28 | 伊尔兰斯公司 | Contact hearing system, device and method |
DK3293985T3 (en) | 2016-09-12 | 2021-06-21 | Sonion Nederland Bv | SOUND WITH INTEGRATED MEMBRANE MOVEMENT DETECTION |
US11432084B2 (en) * | 2016-10-28 | 2022-08-30 | Cochlear Limited | Passive integrity management of an implantable device |
US11253193B2 (en) * | 2016-11-08 | 2022-02-22 | Cochlear Limited | Utilization of vocal acoustic biomarkers for assistive listening device utilization |
US10646718B2 (en) | 2016-11-15 | 2020-05-12 | Advanced Bionics Ag | Cochlear implants and magnets for use with same |
WO2018093733A1 (en) | 2016-11-15 | 2018-05-24 | Earlens Corporation | Improved impression procedure |
US10499854B2 (en) | 2016-11-25 | 2019-12-10 | Cochlear Limited | Eliminating acquisition-related artifacts in electrophysiological recording |
US11595768B2 (en) | 2016-12-02 | 2023-02-28 | Cochlear Limited | Retention force increasing components |
US11128967B2 (en) * | 2017-02-23 | 2021-09-21 | Cochlear Limited | Transducer placement for growth accommodation |
DE102017105529A1 (en) * | 2017-03-15 | 2018-09-20 | Epcos Ag | Garment and use of the garment |
CN106954166A (en) * | 2017-03-22 | 2017-07-14 | 杭州索菲康医疗器械有限公司 | A kind of bone conduction hearing assistance device |
WO2018190813A1 (en) | 2017-04-11 | 2018-10-18 | Advanced Bionics Ag | Cochlear implants with retrofit magnets |
US10419843B1 (en) * | 2017-04-18 | 2019-09-17 | Facebook Technologies, Llc | Bone conduction transducer array for providing audio |
WO2018199936A1 (en) * | 2017-04-25 | 2018-11-01 | Advanced Bionics Ag | Cochlear implants having impact resistant mri-compatible magnet apparatus |
EP3618795A4 (en) * | 2017-05-05 | 2021-04-14 | Badri Amurthur | Stimulation methods and apparatus |
CN110650769B (en) | 2017-05-22 | 2023-12-22 | 领先仿生公司 | Particle alignment method and particle alignment indication kit |
US20180352348A1 (en) * | 2017-06-06 | 2018-12-06 | Sonitus Technologies Inc. | Bone conduction device |
US11035830B2 (en) * | 2017-06-23 | 2021-06-15 | Cochlear Limited | Electromagnetic transducer with dual flux |
US11223912B2 (en) | 2017-07-21 | 2022-01-11 | Cochlear Limited | Impact and resonance management |
US10646712B2 (en) | 2017-09-13 | 2020-05-12 | Advanced Bionics Ag | Cochlear implants having MRI-compatible magnet apparatus |
EP3684311B1 (en) * | 2017-09-22 | 2023-10-25 | Cochlear Limited | Trans middle ear-inner ear fluid flow implementations |
WO2019083540A1 (en) | 2017-10-26 | 2019-05-02 | Advanced Bionics Ag | Headpieces and implantable cochlear stimulation systems including the same |
US11400232B2 (en) | 2017-11-03 | 2022-08-02 | Sanofi | Drug delivery device |
EP3703783A1 (en) | 2017-11-03 | 2020-09-09 | Sanofi | Drug delivery device |
JP2021510608A (en) | 2017-11-07 | 2021-04-30 | ニューロスティム オーエービー インコーポレイテッド | Non-invasive nerve activator with adaptive circuit |
CN111937412B (en) * | 2018-02-06 | 2022-06-03 | 科利耳有限公司 | Prosthesis cognitive enhancement |
US11272297B2 (en) * | 2018-02-13 | 2022-03-08 | Cochlear Limited | Intra-operative determination of vibratory coupling efficiency |
WO2019160555A1 (en) | 2018-02-15 | 2019-08-22 | Advanced Bionics Ag | Headpieces and implantable cochlear stimulation systems including the same |
WO2019173470A1 (en) | 2018-03-07 | 2019-09-12 | Earlens Corporation | Contact hearing device and retention structure materials |
WO2019175764A1 (en) * | 2018-03-13 | 2019-09-19 | Cochlear Limited | Electrical field usage in cochleas |
WO2019199680A1 (en) | 2018-04-09 | 2019-10-17 | Earlens Corporation | Dynamic filter |
US10602258B2 (en) | 2018-05-30 | 2020-03-24 | Facebook Technologies, Llc | Manufacturing a cartilage conduction audio device |
EP3834434A4 (en) | 2018-08-08 | 2022-04-06 | Cochlear Limited | Electromagnetic transducer with new specific interface geometries |
US11750985B2 (en) | 2018-08-17 | 2023-09-05 | Cochlear Limited | Spatial pre-filtering in hearing prostheses |
JP2020053948A (en) | 2018-09-28 | 2020-04-02 | 株式会社ファインウェル | Hearing device |
DE102018220731B3 (en) | 2018-11-30 | 2020-06-04 | Med-El Elektromedizinische Geräte GmbH | Electroacoustic transducer for implantation in an ear, method for producing such an and cochlear implant system |
WO2020264214A1 (en) | 2019-06-26 | 2020-12-30 | Neurostim Technologies Llc | Non-invasive nerve activator with adaptive circuit |
EP3994734A4 (en) * | 2019-07-03 | 2023-07-12 | Earlens Corporation | Piezoelectric transducer for tympanic membrane |
CN110353633A (en) * | 2019-07-08 | 2019-10-22 | 宁波磁性材料应用技术创新中心有限公司 | A kind of wearable product |
KR102170372B1 (en) * | 2019-08-13 | 2020-10-27 | 주식회사 세이포드 | Sound anchor for transmitting sound to human tissues in the ear canal and semi-implantable hearing aid having the same |
US11890438B1 (en) * | 2019-09-12 | 2024-02-06 | Cochlear Limited | Therapeutic substance delivery |
US20210105074A1 (en) | 2019-10-02 | 2021-04-08 | NOTO Technologies Limited | Bone conduction communication system and method of operation |
JP2023506713A (en) | 2019-12-16 | 2023-02-20 | ニューロスティム テクノロジーズ エルエルシー | Noninvasive nerve activator using booster charge delivery |
US11178499B2 (en) * | 2020-04-19 | 2021-11-16 | Alpaca Group Holdings, LLC | Systems and methods for remote administration of hearing tests |
WO2021220078A1 (en) * | 2020-04-27 | 2021-11-04 | Cochlear Limited | Pinnal device |
US11483639B2 (en) * | 2020-06-16 | 2022-10-25 | New York University | Sound sensing system |
CN111698608B (en) * | 2020-07-02 | 2022-02-01 | 立讯精密工业股份有限公司 | Bone conduction earphone |
WO2022084763A1 (en) * | 2020-10-22 | 2022-04-28 | Cochlear Limited | Shaped piezoelectric actuator for medical implant |
CN112535808B (en) * | 2020-12-25 | 2022-10-25 | 哈尔滨工业大学 | Cochlear electrode implanting device |
WO2023148651A1 (en) * | 2022-02-02 | 2023-08-10 | Cochlear Limited | High impedance tissue mounting of implantable transducer |
WO2024052753A1 (en) * | 2022-09-06 | 2024-03-14 | Cochlear Limited | Auditory device with vibrating external actuator compatible with bilateral operation |
Family Cites Families (280)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US41595A (en) | 1864-02-16 | Improvement in vyagon-brakes | ||
US245555A (en) | 1881-08-09 | Ohaeles h | ||
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 |
US2045427A (en) | 1933-05-24 | 1936-06-23 | Sonotone Corp | Bone-conduction hearing-aid |
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 |
US3995644A (en) | 1975-09-16 | 1976-12-07 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Percutaneous connector device |
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, PREFERRED FOR MECHANICAL TRANSMISSION OF SOUND INFORMATION TO THE BALL OF A HEARING DAMAGED 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 | DEVICE FOR A HORSE DEVICE |
US4606329A (en) * | 1985-05-22 | 1986-08-19 | Xomed, Inc. | Implantable electromagnetic middle-ear bone-conduction hearing aid device |
US5015225A (en) | 1985-05-22 | 1991-05-14 | 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 |
DE3735137A1 (en) * | 1987-10-16 | 1989-05-03 | Siemens Ag | ARRANGEMENT FOR DISPENSING MEDICINES IN AN IMPLANTABLE MEDICAL DEVICE |
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 |
US5047994A (en) * | 1989-05-30 | 1991-09-10 | Center For Innovative Technology | Supersonic bone conduction hearing aid and method |
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 | HEARING AID DEVICE COMPRISING AN IMPLANTED AND AUTONOMOUS HEARING AID WITH DIRECT BONE CONDUCTION. |
JPH0456531A (en) * | 1990-06-26 | 1992-02-24 | Matsushita Electric Ind Co Ltd | Voice input device |
DE4104358A1 (en) * | 1991-02-13 | 1992-08-20 | Implex Gmbh | IMPLANTABLE HOER DEVICE FOR EXCITING THE INNER EAR |
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 the implementation 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 method |
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 |
SE503791C2 (en) * | 1994-12-02 | 1996-09-02 | P & B Res Ab | Hearing aid device |
SE503790C2 (en) * | 1994-12-02 | 1996-09-02 | P & B Res Ab | Displacement device for implant connection at 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 WITH 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 | AMPLIFIED PIEZOACTIVE ACTUATOR WITH HIGH STRAIGHTNESS |
FR2740349B1 (en) * | 1995-10-30 | 1997-11-21 | Dynastar Skis Sa | VIBRATION DAMPING DEVICE FOR MOUNTING ON A SPORTS ARTICLE |
DE29724567U1 (en) * | 1996-02-14 | 2003-01-16 | Walter Lorenz Surgical Inc | Bone fixation device and instrument for inserting the bone fixation device |
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 sensory 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 |
US5899847A (en) * | 1996-08-07 | 1999-05-04 | St. Croix Medical, Inc. | Implantable middle-ear hearing assist system using piezoelectric transducer film |
US6001129A (en) | 1996-08-07 | 1999-12-14 | St. Croix Medical, Inc. | Hearing aid transducer support |
ATE249134T1 (en) | 1996-10-01 | 2003-09-15 | Phonak Ag | VOLUME LIMIT |
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 |
WO1998040038A1 (en) * | 1997-03-13 | 1998-09-17 | 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 | Device for 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 |
US6325755B1 (en) | 1997-08-07 | 2001-12-04 | St. Croix Medical, Inc. | Mountable transducer assembly with removable sleeve |
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 | Percutaneous bone anchored transducer |
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 |
EP0936840A1 (en) * | 1998-02-16 | 1999-08-18 | Daniel F. àWengen | Implantable hearing aid |
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 |
US6267731B1 (en) * | 1998-06-05 | 2001-07-31 | 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 |
US6309410B1 (en) * | 1998-08-26 | 2001-10-30 | Advanced Bionics Corporation | Cochlear electrode with drug delivery channel and method of making same |
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 |
KR100282067B1 (en) * | 1998-12-30 | 2001-09-29 | 조진호 | Transducer of Middle Ear Implant Hearing Aid |
EP1142442A2 (en) * | 1999-01-07 | 2001-10-10 | Sarnoff Corporation | Hearing aid with large diaphragm microphone element including a printed circuit board |
US6554861B2 (en) * | 1999-01-19 | 2003-04-29 | Gyrus Ent L.L.C. | Otologic prosthesis |
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 | Rotary blade flap drive |
US6094492A (en) * | 1999-05-10 | 2000-07-25 | Boesen; Peter V. | Bone conduction voice transmission apparatus and system |
US6754537B1 (en) * | 1999-05-14 | 2004-06-22 | Advanced Bionics Corporation | Hybrid implantable cochlear stimulator hearing aid system |
CA2370860A1 (en) * | 1999-05-14 | 2000-11-23 | Thomas J. Balkany | Hybrid implantable cochlear stimulator hearing aid system |
DE19935029C2 (en) * | 1999-07-26 | 2003-02-13 | Phonak Ag Staefa | Implantable arrangement for mechanically coupling a driver part to a coupling point |
DE19948375B4 (en) | 1999-10-07 | 2004-04-01 | Phonak Ag | Arrangement for mechanically coupling a driver to a coupling point of the ossicle chain |
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 |
KR100743403B1 (en) | 1999-12-27 | 2007-07-30 | 알자 코포레이션 | 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 |
TW511391B (en) * | 2000-01-24 | 2002-11-21 | New Transducers Ltd | Transducer |
US6885753B2 (en) | 2000-01-27 | 2005-04-26 | New Transducers Limited | Communication device using bone conduction |
SE516270C2 (en) | 2000-03-09 | 2001-12-10 | Osseofon Ab | Electromagnetic vibrator |
DE20004499U1 (en) | 2000-03-14 | 2000-12-07 | Daimler Chrysler Ag | Aerodynamic flow profile with leading edge flap |
DE10017332C2 (en) | 2000-04-07 | 2002-04-18 | Daimler Chrysler Ag | Piezoelectric actuator for flap control on the rotor blade of a helicopter |
DE60135741D1 (en) | 2000-05-19 | 2008-10-23 | Baycrest Ct For Geriatric Care | DEVICE FOR OBJECTIVE AUDIBLE EVALUATION USING AUDITIVE STATIONARY EVOKED POTENTIALS |
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 |
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 |
SE0002072L (en) | 2000-06-02 | 2001-05-21 | P & B Res Ab | Vibrator for leg anchored and leg conduit hearing aids |
SE523123C2 (en) * | 2000-06-02 | 2004-03-30 | P & B Res Ab | Hearing aid that works with the principle of bone conduction |
WO2001095668A1 (en) | 2000-06-02 | 2001-12-13 | Erich Bayer | Otoplasty for behind-the-ear hearing aids |
SE0002073L (en) | 2000-06-02 | 2001-05-21 | P & B Res Ab | Vibrator for leg anchored and leg conduit hearing aids |
DE10031832C2 (en) * | 2000-06-30 | 2003-04-30 | Cochlear Ltd | Hearing aid for the 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 leg anchored hearing aids and ear or eye prostheses in the skull |
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 | 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 |
KR100347595B1 (en) * | 2000-11-02 | 2002-08-07 | 심윤주 | method of automatically fitting hearing aids |
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 system |
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-piece leg anchored hearing aid |
SE523100C2 (en) | 2001-06-21 | 2004-03-30 | P & B Res Ab | Leg anchored hearing aid designed for the transmission of sound |
SE523125C2 (en) | 2001-06-21 | 2004-03-30 | P & B Res Ab | Vibrator for vibration generation in bone anchored hearing aids |
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 |
US6875166B2 (en) * | 2001-09-06 | 2005-04-05 | St. Croix Medical, Inc. | Method for creating a coupling between a device and an ear structure in an implantable hearing assistance device |
US7127078B2 (en) * | 2001-10-03 | 2006-10-24 | Advanced Bionics Corporation | Implanted outer ear canal hearing aid |
US6786860B2 (en) * | 2001-10-03 | 2004-09-07 | Advanced Bionics Corporation | Hearing aid design |
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 |
FR2836536B1 (en) | 2002-02-26 | 2004-05-14 | Cedrat Technologies | PIEZOELECTRIC VALVE |
US6879693B2 (en) * | 2002-02-26 | 2005-04-12 | Otologics, Llc. | Method and system for external assessment of hearing aids that include implanted actuators |
US6626909B2 (en) * | 2002-02-27 | 2003-09-30 | Kingsley Richard Chin | Apparatus and method for spine fixation |
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 | Device for electromagnetic vibrator |
US7695441B2 (en) | 2002-05-23 | 2010-04-13 | Tympany, Llc | Automated diagnostic hearing test |
FR2841429B1 (en) * | 2002-06-21 | 2005-11-11 | Mxm | HEARING AID DEVICE FOR THE REHABILITATION OF PATIENTS WITH PARTIAL NEUROSENSORY DEATHS |
BR0312909A (en) * | 2002-07-26 | 2005-07-12 | Oakley Inc | Portable, wireless audio interfaces, audio interface systems, eyeglasses, eyepieces and interactive audio devices and methods of receiving telephone calls, signal handling in a wireless network and menu navigation |
KR100390003B1 (en) | 2002-10-02 | 2003-07-04 | Joo Bae Kim | Bone-conduction speaker using vibration plate and mobile telephone using the same |
AU2003270597A1 (en) * | 2002-09-10 | 2004-04-30 | 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 |
US7386143B2 (en) * | 2002-10-02 | 2008-06-10 | 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 |
DE60331455D1 (en) * | 2002-10-04 | 2010-04-08 | Microchips Inc | MEDICAL DEVICE FOR THE CONTROLLED MEDICAMENTAL ADMINISTRATION AND HEART CONTROL AND / OR HEART STIMULATION |
EP1551499A1 (en) * | 2002-10-04 | 2005-07-13 | Microchips, Inc. | Medical device for neural stimulation and controlled drug delivery |
WO2004034934A2 (en) * | 2002-10-15 | 2004-04-29 | Ludwig Arwed | Implant for implanting under the scalp for the magnetic fixing of a prosthesis |
AT507045B1 (en) | 2002-11-29 | 2010-04-15 | Cochlear Ltd | IMPLANTABLE, TISSUE-STIMULATING DEVICE |
US7033313B2 (en) * | 2002-12-11 | 2006-04-25 | No. 182 Corporate Ventures Ltd. | Surgically implantable hearing aid |
EP1435757A1 (en) * | 2002-12-30 | 2004-07-07 | Andrzej Zarowski | Device implantable in a bony wall of the inner ear |
WO2004062482A2 (en) * | 2003-01-10 | 2004-07-29 | Abdou Samy M | Plating system for bone fixation and subsidence and method of implantation |
FR2850217A1 (en) | 2003-01-17 | 2004-07-23 | Cedrat Technologies | PIEZOACTIVE ACTUATOR WITH AMPLIFIED MOVEMENT |
US6999818B2 (en) * | 2003-05-23 | 2006-02-14 | Greatbatch-Sierra, Inc. | Inductor capacitor EMI filter for human implant applications |
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 |
SE526548C2 (en) | 2003-05-30 | 2005-10-04 | Entific Medical Systems Ab | Device for implants |
ATE527829T1 (en) * | 2003-06-24 | 2011-10-15 | Gn Resound As | BINAURAL HEARING AID SYSTEM WITH COORDINATED SOUND PROCESSING |
SE526099C2 (en) | 2003-06-30 | 2005-07-05 | Entific Medical Systems Ab | Device for wireless signal and energy transfer 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 |
US7442164B2 (en) * | 2003-07-23 | 2008-10-28 | Med-El Elektro-Medizinische Gerate Gesellschaft M.B.H. | Totally implantable hearing prosthesis |
US20060018488A1 (en) | 2003-08-07 | 2006-01-26 | Roar Viala | Bone conduction systems and methods |
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 |
SE0302489L (en) * | 2003-09-19 | 2005-03-22 | P & B Res Ab | Method and device for attenuating resonant frequency |
US20070213788A1 (en) * | 2003-09-19 | 2007-09-13 | Osberger Mary J | Electrical stimulation of the inner ear in patients with unilateral hearing loss |
SE527006C2 (en) * | 2003-10-22 | 2005-12-06 | Entific Medical Systems Ab | Device for curing or reducing stuttering |
US7241258B2 (en) * | 2003-11-07 | 2007-07-10 | Otologics, Llc | Passive vibration isolation of implanted microphone |
US20050101830A1 (en) * | 2003-11-07 | 2005-05-12 | Easter James R. | Implantable hearing aid transducer interface |
WO2005072168A2 (en) * | 2004-01-20 | 2005-08-11 | Sound Techniques Systems Llc | Method and apparatus for improving hearing in patients suffering from hearing loss |
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 |
US7651460B2 (en) * | 2004-03-22 | 2010-01-26 | The Board Of Regents Of The University Of Oklahoma | Totally implantable hearing system |
US7214179B2 (en) * | 2004-04-01 | 2007-05-08 | Otologics, Llc | Low acceleration sensitivity microphone |
US7840020B1 (en) * | 2004-04-01 | 2010-11-23 | Otologics, Llc | Low acceleration sensitivity microphone |
US6942696B1 (en) * | 2004-04-28 | 2005-09-13 | Clarity Corporation | Ossicular prosthesis adjusting device |
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 |
US8244365B2 (en) * | 2004-05-10 | 2012-08-14 | Cochlear Limited | Simultaneous delivery of electrical and acoustical stimulation in a hearing prosthesis |
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 |
WO2005122887A2 (en) * | 2004-06-15 | 2005-12-29 | Cochlear Americas | Automatic determination of the threshold of an evoked neural response |
US7421087B2 (en) * | 2004-07-28 | 2008-09-02 | Earlens Corporation | Transducer for electromagnetic hearing devices |
US7867160B2 (en) * | 2004-10-12 | 2011-01-11 | Earlens Corporation | Systems and methods for photo-mechanical hearing transduction |
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 |
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 |
CA2588810A1 (en) * | 2004-11-30 | 2006-06-08 | Cochlear Acoustics Ltd | Implantable actuator for hearing aid applications |
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 |
GB0500616D0 (en) | 2005-01-13 | 2005-02-23 | Univ Dundee | Hearing implant |
JP5088788B2 (en) | 2005-01-27 | 2012-12-05 | コクレア リミテッド | Implantable medical devices |
SE528279C2 (en) | 2005-02-21 | 2006-10-10 | Entific Medical Systems Ab | Vibrator for bone conductive hearing aid |
ATE531346T1 (en) * | 2005-02-24 | 2011-11-15 | Morphogeny Llc | CONNECTED, SLIDING AND MATCHABLE ROTATABLE COMPONENTS |
WO2006091808A2 (en) * | 2005-02-25 | 2006-08-31 | Medical Research Products-B, Inc. | Fully implantable hearing aid system |
WO2006101935A2 (en) * | 2005-03-16 | 2006-09-28 | 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 |
DE102005017493A1 (en) * | 2005-04-15 | 2006-10-19 | Siemens Audiologische Technik Gmbh | Hearing aid with two different output transducers and fitting procedure |
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 |
AU2006283905B2 (en) * | 2005-08-22 | 2009-12-03 | 3Win N.V. | A 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 |
US7753838B2 (en) * | 2005-10-06 | 2010-07-13 | Otologics, Llc | Implantable transducer with transverse force application |
EP1952620A2 (en) | 2005-10-31 | 2008-08-06 | Audiodent Israel Ltd. | Miniature bio-compatible piezoelectric transducer apparatus |
WO2007102894A2 (en) * | 2005-11-14 | 2007-09-13 | Oticon A/S | 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 |
JP2007184722A (en) | 2006-01-05 | 2007-07-19 | Nagasaki Univ | Bone conduction hearing-aid and bone conduction speaker |
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 | MOBILE 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 |
US20080255406A1 (en) * | 2007-03-29 | 2008-10-16 | Vibrant Med-El Hearing Technology Gmbh | Implantable Auditory Stimulation Systems Having a Transducer and a Transduction Medium |
WO2008134642A1 (en) * | 2007-04-27 | 2008-11-06 | Personics Holdings Inc. | Method and device for personalized voice operated control |
SE531053C2 (en) | 2007-05-24 | 2008-12-02 | Cochlear Ltd | Vibrator |
WO2009015103A1 (en) | 2007-07-20 | 2009-01-29 | Cochlear Americas | Coupling apparatus for a bone anchored hearing device |
EP2177046B2 (en) * | 2007-08-14 | 2020-05-27 | 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 |
EP2066140B1 (en) * | 2007-11-28 | 2016-01-27 | Oticon Medical A/S | Method for fitting a bone anchored hearing aid to a user and bone anchored bone conduction hearing aid system. |
DK2083582T3 (en) | 2008-01-28 | 2013-11-11 | Oticon Medical As | Bone conductive 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 |
US8401213B2 (en) | 2008-03-31 | 2013-03-19 | Cochlear Limited | Snap-lock coupling system for a prosthetic device |
US20100137675A1 (en) * | 2008-03-31 | 2010-06-03 | Cochlear Limited | Bone conduction devices generating tangentially-directed mechanical force using a rotationally moving mass |
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 |
WO2010042463A1 (en) | 2008-10-07 | 2010-04-15 | Med-El Elektromedizinische Geraete Gmbh | Cochlear implant sound processor for sleeping with tinnitus suppression and alarm function |
SE0900372A1 (en) | 2009-03-24 | 2010-06-15 | Osseofon Ab | Leg conduit vibrator design with improved high frequency response |
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 |
US8655455B2 (en) | 2009-10-13 | 2014-02-18 | Incumed, Llc | Neural stimulator with percutaneous connectivity |
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 |
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 |
US11843918B2 (en) | 2011-10-11 | 2023-12-12 | Cochlear Limited | Bone conduction implant |
EP2592848B1 (en) | 2011-11-08 | 2019-06-26 | Oticon Medical A/S | Acoustic transmission method and listening device. |
US9998837B2 (en) | 2014-04-29 | 2018-06-12 | Cochlear Limited | Percutaneous vibration conductor |
-
2008
- 2008-07-03 US US12/167,796 patent/US8401213B2/en not_active Expired - Fee Related
- 2008-07-03 US US12/167,871 patent/US8852251B2/en not_active Expired - Fee Related
- 2008-07-03 US US12/167,825 patent/US20090248085A1/en not_active Abandoned
- 2008-07-03 US US12/167,668 patent/US8363871B2/en active Active
- 2008-07-03 US US12/167,728 patent/US8526641B2/en not_active Expired - Fee Related
- 2008-07-03 US US12/167,851 patent/US8216287B2/en not_active Expired - Fee Related
- 2008-07-07 US US12/168,529 patent/US8150083B2/en active Active
- 2008-07-07 US US12/168,620 patent/US8655002B2/en active Active
- 2008-07-07 US US12/168,603 patent/US8532321B2/en not_active Expired - Fee Related
- 2008-07-07 US US12/168,653 patent/US8170252B2/en not_active Expired - Fee Related
- 2008-07-07 US US12/168,636 patent/US20090248155A1/en not_active Abandoned
- 2008-07-07 US US12/168,572 patent/US8154173B2/en not_active Expired - Fee Related
- 2008-10-14 US US12/251,437 patent/US20090247813A1/en not_active Abandoned
- 2008-10-14 US US12/251,443 patent/US8831260B2/en active Active
-
2009
- 2009-03-05 US US12/398,586 patent/US8433081B2/en not_active Expired - Fee Related
- 2009-03-26 WO PCT/AU2009/000355 patent/WO2009121101A1/en active Application Filing
- 2009-03-26 WO PCT/AU2009/000350 patent/WO2009121097A1/en active Application Filing
- 2009-03-26 WO PCT/AU2009/000351 patent/WO2009121098A1/en active Application Filing
- 2009-03-27 WO PCT/AU2009/000358 patent/WO2009121104A1/en active Application Filing
- 2009-03-27 WO PCT/AU2009/000363 patent/WO2009121109A1/en active Application Filing
- 2009-03-27 WO PCT/AU2009/000359 patent/WO2009121105A1/en active Application Filing
- 2009-03-27 WO PCT/AU2009/000360 patent/WO2009121106A1/en active Application Filing
- 2009-03-27 EP EP09726548A patent/EP2269241A1/en not_active Withdrawn
- 2009-03-27 WO PCT/AU2009/000362 patent/WO2009121108A1/en active Application Filing
- 2009-03-30 WO PCT/AU2009/000372 patent/WO2009121116A1/en active Application Filing
- 2009-03-30 EP EP09728994.6A patent/EP2269388B1/en active Active
- 2009-03-30 CN CN200980115881.9A patent/CN102047692B/en active Active
- 2009-03-30 WO PCT/AU2009/000365 patent/WO2009121111A1/en active Application Filing
- 2009-03-30 WO PCT/AU2009/000369 patent/WO2009121115A1/en active Application Filing
- 2009-03-30 WO PCT/AU2009/000374 patent/WO2009121118A1/en active Application Filing
- 2009-03-30 WO PCT/AU2009/000367 patent/WO2009121113A1/en active Application Filing
- 2009-03-30 WO PCT/AU2009/000373 patent/WO2009121117A1/en active Application Filing
- 2009-03-30 WO PCT/AU2009/000368 patent/WO2009121114A1/en active Application Filing
- 2009-03-31 EP EP09727686A patent/EP2271282A4/en not_active Withdrawn
- 2009-03-31 US US12/935,887 patent/US9955270B2/en active Active
- 2009-03-31 WO PCT/US2009/038933 patent/WO2009124036A2/en active Application Filing
- 2009-03-31 US US12/935,895 patent/US8532322B2/en active Active
- 2009-03-31 WO PCT/US2009/038884 patent/WO2009124008A1/en active Application Filing
- 2009-03-31 US US12/935,901 patent/US8945216B2/en active Active
- 2009-03-31 EP EP09798353A patent/EP2272260A4/en not_active Withdrawn
- 2009-03-31 EP EP09727994.7A patent/EP2269386B1/en not_active Not-in-force
- 2009-03-31 US US12/935,909 patent/US20110112462A1/en not_active Abandoned
- 2009-03-31 WO PCT/US2009/038937 patent/WO2009124038A1/en active Application Filing
- 2009-03-31 EP EP09726479A patent/EP2265318A4/en not_active Withdrawn
- 2009-03-31 WO PCT/US2009/038879 patent/WO2009124005A2/en active Application Filing
- 2009-03-31 US US12/935,906 patent/US8657734B2/en active Active
- 2009-03-31 US US12/935,650 patent/US20110029031A1/en not_active Abandoned
- 2009-03-31 WO PCT/US2009/038932 patent/WO2009124035A2/en active Application Filing
- 2009-03-31 US US12/935,905 patent/US8731205B2/en active Active
- 2009-03-31 WO PCT/US2009/038942 patent/WO2009124042A2/en active Application Filing
- 2009-03-31 WO PCT/US2009/038893 patent/WO2010008630A1/en active Application Filing
- 2009-03-31 WO PCT/US2009/038890 patent/WO2009124010A2/en active Application Filing
-
2010
- 2010-01-15 US US12/688,491 patent/US8509461B2/en not_active Expired - Fee Related
-
2013
- 2013-08-13 US US13/965,718 patent/US20130345496A1/en not_active Abandoned
- 2013-11-05 US US14/072,398 patent/US9602931B2/en active Active
-
2017
- 2017-03-20 US US15/464,090 patent/US11570552B2/en active Active
-
2018
- 2018-04-20 US US15/958,212 patent/US20180376255A1/en active Pending
-
2023
- 2023-01-30 US US18/103,215 patent/US20230179929A1/en active Pending
Also Published As
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US8852251B2 (en) | Mechanical fixation system for a prosthetic device | |
US11889272B2 (en) | Implantable medical device | |
US9973866B2 (en) | Medical device coupling arrangement | |
AU784113B2 (en) | At least partially implantable system for rehabilitation of a hearing disorder | |
US9162054B2 (en) | Implantable component interface | |
DK1709835T3 (en) | Implantable dentures with direct mechanical stimulation of the inner ear | |
US20120215057A1 (en) | Multi-mode hearing prosthesis | |
US20150343225A1 (en) | Distributed Implantable Hearing Systems | |
US10003898B1 (en) | Flexible connection bone conduction device | |
US10812917B2 (en) | Under-lip bone conduction device | |
US10798502B2 (en) | Implantable transducer system | |
WO2024052754A1 (en) | Transducer failsafe for medical implant | |
CN112752593A (en) | Passive hearing implant |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
121 | Ep: the epo has been informed by wipo that ep was designated in this application |
Ref document number: 09728698 Country of ref document: EP Kind code of ref document: A1 |
|
NENP | Non-entry into the national phase |
Ref country code: DE |
|
122 | Ep: pct application non-entry in european phase |
Ref document number: 09728698 Country of ref document: EP Kind code of ref document: A1 |