US3870832A - Implantable electromagnetic hearing aid - Google Patents
Implantable electromagnetic hearing aid Download PDFInfo
- Publication number
- US3870832A US3870832A US492675A US49267574A US3870832A US 3870832 A US3870832 A US 3870832A US 492675 A US492675 A US 492675A US 49267574 A US49267574 A US 49267574A US 3870832 A US3870832 A US 3870832A
- Authority
- US
- United States
- Prior art keywords
- coil
- magnet
- user
- bone
- hearing aid
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
Images
Classifications
-
- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
- H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
- H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
- H04R25/604—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers
- H04R25/606—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers acting directly on the eardrum, the ossicles or the skull, e.g. mastoid, tooth, maxillary or mandibular bone, or mechanically stimulating the cochlea, e.g. at the oval window
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/07—Endoradiosondes
- A61B5/076—Permanent implantations
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/18—Internal ear or nose parts, e.g. ear-drums
- A61F2002/183—Ear parts
-
- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
- H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
- H04R2225/67—Implantable hearing aids or parts thereof not covered by H04R25/606
Definitions
- This invention relates to hearing aids. More particularly, this invention relates to hearing aids that operate electromagnetically and some of the components of which areimplantable.
- a conventional hearing aid consists of a microphone, an amplifier, batteries and a loudspeaker. All of these components are mounted externally on the user, and various attempts have been made to disguise of hidethem, as by building them into the earpieces of eyeglasses for example.
- a hearing aid which eliminates or attenuates many of the disadvantages of conventional hearing aids of the type noted previously as well as those of hearing aids of the types noted in the two preceding paragraphs.
- a hearing aid embodying my invention may include a microphone, amplifier and a battery or batteries (or other suitable sound transducer), as is conventional, all of which may be located in a small housing that may be hidden behind one ear of the individual and which may plug into a receptacle and socket implated in the temporal bone behind the ear.
- the hearing aid further includes an implanted electromagnetic device that replaces the loudspeaker, tubing and earmould of a conventional hearing aid. This device consists of a magnet that is permanently attached to the stapes (one of the three auditory ossicles) and an implanted coil that is located in close proximity to the magnet and which receives electrical signals from the sound transducer. Also provided is a suitable support for the coil.
- FIG. 1 is a perspective view showing the aforesaid housing located behind the ear of an individual;
- FIG. 2 is a horizontal section through a normal human ear but with the outer tissue folded over on itself;
- FIG. 3 is a view similar to that of FIG. 2 but with the incus removed, a necessary step in the operative procedure for implanting certain components of a hearing aid embodying my invention
- FIG. 4 is a view similar to that of FIG. 2 but showing these components in place;
- FIG. 5 is a side view of an individuals right ear with the tissue removed and showing the same components as are seen in FIG. 4;
- FIGS. 6 and 7 are top and side views respectively showing the stapes and the components illustrated in FIGS. 4 and 5;
- FIG. 8 is a view similar to that of FIG. 7 but with the coil and its support removed;
- FIG. 9 is a view similar to FIG. 8 but showing another embodiment of my invention.
- FIG. 10 is an exploded view of certain components ,of a hearing aid embodying my invention.
- FIG. 11 is a schematic diagram of a hearing aid embodying my invention.
- a hearing aid embodying my in- I vention includes a housing 10 (see also FIG. 10) in which, as shown in FIG. 11, may be located a microphone 30, an amplifier 31 and a battery 32.
- This housing is very small and can be located behind the ear tissue of an individual. It has three male terminals 33 (FIG. 10) projecting therefrom adapted to plug into three female terminals 34 in a receptacle 11 (FIGS. 6 and 10).
- receptacle ll fits into and externally threaded socket 35.
- the lower part 36 of socket 35 is permanently implanted by an operative procedure into the temporal bone of the patient.
- socket 35 may be about 1 cm. long and have a maximum diameter of about 1.3 cm.
- Housing 10, receptacle 11 and socket 35 are fabricated of a material that is non tissue toxic.
- One suitable material is TEFLON (trade mark).
- Cap 37 also may be fabricated of this material or stainless steel, for example.
- Two of the three terminals 33 are, in fact, the output terminals of amplifier 31, the latter being powered by battery 32 and serving to amplify sounds picked up by microphone 30.
- the third terminal is for stability and locating.
- the microphone, amplifier and battery may be of a conventional type.
- a suitable microphone is a condensor microphone model No. BL1680 made by Knowles Electronics Inc., Franklin Park, Illinois.
- Amplifier 31 preferably is a logarithmic amplifier.
- Two suitable amplifiers both manufactured by Robert Bosch Electronic Company of Berlin, West Germany are STAR 6 (trade mark) dynamic range compression (DRC) amplifier and OMNITRON 11" (trade mark) DRC amplifier.
- the battery may be an EVEREADY (trade mark) model E675 1.4 volt mercury battery.
- Terminals 33 and 34 preferably are gold plated.
- microphone 30, amplifier 31 and battery 32 individually or in total may be located elsewhere than behind the ear.
- the other part of a hearing aid embodying my invention consists of a magnet 12 (FIGS. 5, 6, 8 and 12), which, in the embodiment shown, is cylindrical in con figuration, and which is secured to the stapes 13; a coil 14 located in close proximity to magnet 12; a support or holder 15 for the coil; and two lead-in conductors 16 connected between terminals 34 of receptacle 11 and coil 14. All of these components are surgically implanted.
- a holder 17 for magnet 12 is provided.
- This holder may be fabricated of TEFLON" (trade mark), for example, and is designed so as to be readily attached to stapes 13.
- Magnet 12 may be encased in the material of the holder.
- magnet 12 is firmly secured to the head of stapes 13 by a non tissue toxic cement such as SILASTIC (trade mark) or CRANIOPLAST (trade mark).
- SILASTIC trade mark
- CRANIOPLAST trademark
- magnet 12 unless magnet 12 is encapsulated in a non tissue toxic material, it itself must be non tissue toxic.
- VITALLIUM trademark
- a superior magnet is one made of cobalt symareum and available from the General Electric Company, Schenectady, New York. Such a magnet requires encapsulation in a non tissue toxic material.
- magnet 12 Regardless of how magnet 12 is secured to stapes 13, it must be firmly fastened thereto so that the magnet and stapes move as a unit without relative movement there-between in order to avoid microtrauma. This poses no problem where cement is used. Where holder 17 is mechanically secured to the stapes without cement, the inherent springiness of the holder material may be relied upon to provide the required connection or, depending on the holder material, it may be crimped in position.
- Magnet 12 is very small, typically about 1 mm. in diameter and 1 mm. long.
- Coil 14 must be sufficiently small to fit in the middle ear space and should have an input impedance that matches the output impedance of amplifier 31.
- coil 14 may consist of 1,600 turns of insulated 50 gauge copper wire embedded in a suitable non tissue toxic material such as SILASTIC (trade mark). It may be about 1.5 mm. internal diameter (core), 4 mm. outside diameter and 1 mm. long.
- Coil 14 is located in close proximity to magnet 12. In the embodiment of the invention shown in FIGS. 4, 6 and 7 it is positioned just above magnet 12 with the core of the coil and the magnet arranged coaxially. The coil could be arranged to surround holder 17 if desired. In other words, magnet 12 then would be in the core of the coil. The important thing, however, is that coil 14 and magnet 12 are so arranged that the interaction of the magnetic field of the magnet and that of the coil when energized results in movement of the stapes in the same manner as it normally would be moved by the incus.
- Holder 15 performs the important function of supporting coil 14 in a fixed position in the middle ear space. It may be a silver wire approximately 0.2 mm. in diameter. It may be flattened at one end and this fiattened end then wrapped around coil 14, the flattening being for the purpose of providing a greater surface area of contact. The other end of holder 15 is cemented to bone within the mastoid bowl.
- wires 16 which preferably are made of gold, are led into socket 35 through a small opening in the bottom wall thereof, are passed through and out of the socket and then are soldered to terminals 34.
- Socket 35 than may be screwed into the previously tapped opening in the mastoid tip of the temporal bone behind the patients ear and components l1, l0 and 37 located in position as previously explained herein.
- a hearing aid having certain components thereof that are implanted in the ear of the user, said hearing aid comprising sound transducer means for converting audio signals to electrical signals and electromagnetic transducer means for receiving said electrical signals and converting said electrical signals into mechanical movement of the stapes bone of the ear of the user, said electromagnetic transducer means being implantable in the ear of the user and comprising a magnet, means for firmly securing said magnet to the head of the stapes bone of the user such that said magnet and said stapes bone move as a unit without relative movement there between when said magnet is attracted by a magnetic field and a coil of a size that permits it to be implanted in the middle ear space of the ear of the user, said coil being adapted to be implanted in the middle ear space .of the ear of the user in close proximity to said magnet,
- said hearing aid when energized by said electrical signals producing a magnetic field in which said magnet is located, said coil and said magnet being positioned with respect to each other such that upon energization of said coil said stapes bone moves as a result of the interaction between the magnetic field of said magnet and said magnetic field of said coil in the same manner as said stapes bone normally is moved by the incus bone, said hearing aid also including implantable support means for said coil, said support means being adapted to be secured to a bone that holds said coil in a fixed position in said middle ear space.
- a hearing aid according to claim 1 wherein said sound transducer means comprises a microphone, an amplifier and a battery.
- a hearing aid further including a socket having electrical terminals therein, means electrically connecting said sound transducer means and said coil, said means electrically connecting said sound transducer means and said coil including implantable conductors connected to said terminals and to said coil for supplying said electrical signals to said coil, said socket being adapted to be located behind the ear of the user and secured to bone of the user thereat, a housing for said microphone, amplifier and battery, said housing having output terminals for said electrical signals, said housing being adapted for reception by said socket with said terminals of said socket electrically contacting said output terminals of said housing.
- a hearing aid according to claim 3 wherein said socket is externally threaded to threadablyengage in a stapes bone of the user comprises a non tissue toxic cement.
- a hearing aid according to claim 1 wherein said means for securing said magnet to the head of the stapes bones comprises a holder for said magnet, said holder being adapted for attachment to the head of the stapes bone of the user.
- a hearing aid according to claim 1 including meansfor securing said support means to a bone that holds said coil in a fixed position in said middle ear space.
- a hearing aid according to claim 7 wherein said means for securing said support means comprises a non tissue toxic cement.
- a hearing aid having certain components thereof implanted in an ear of the user from which the incus has been removed, said hearing aid comprising sound transducer means for converting audio signals to electrical signals and electromechanical transducer means adapted to receive said electrical signals and convert said electrical signals into mechanical movement of the stapes bone of said ear of said user, said electromechanical transducer means being implanted in said ear of said user and comprising a magnet, means for firmly securing said magnet to the head of said stapes bone such that said magnet and said stapes bone move as a unit without relative movement therebetween when said magnet is attracted by a magnetic field and a coil implanted in the middle ear space of said ear in close proximity to said magnet, said coil when energized by said electrical signals producing a magnetic field in which said magnet is located, said coil and said magnet being positioned with respect to each other such that upon energization of said coil said stapes bone is moved as a result of the interaction between the magnetic field of said magnet and said magnetic field of said coil in
- a hearing aid according to claim 9 further including a socket having electrical terminals therein, said socket being implanted in' bone behind the ear of said user, implanted conductors connected to said terminals and to said coil for supplying said electrical signals to said coil, and a housing for said sound transducer, said housing having output terminals for said electrical signals and being received by said socket with said terminals of said socket electrically connecting said output
Abstract
Problems of conventional hearing aids (low fidelity, poor frequency response and feedback) and of hearing aids employing implanted piezoelectric elements (high power requirements and microtrauma) are eliminated or attenuated by implanting a coil and magnet in the ear after removal of the incus, the magnet being fastened to the head of the stapes and the coil being energized by electrical signals from a sound transducer and producing a magnetic field which, interacting with the magnetic field of the magnet, causes movement of the stapes in the same manner as it normally is moved by the incus.
Description
United States Patent 1191 v 1111 3,870,832 Fredrickson Mar. 11, 1975 .[54] IMPLANTABLE ELECTROMAGNETIC OTHER PUBLICATIONS EA NG AID H R! 1 Course Lecture Mater1al,p. 54, H6. 65, American [76] Inventor: John M. Fredrickson, 24 Queen Academy f opthamology and omlarynaology.
y D Toronto Ontario, Course 319, Conservative Tympanoplasty," Oct. 1, Canada 1966.
[22] Filed: July 29, 1974 [21] App]. No.: 492,675
Related [1.8. Application Data [63] Continuation-in-part of Ser. No. 364,938, May 29, [57] ABSTRACT 1973 abandoned" Problems of conventional hearing aids (101v fidelity, poor frequency response and feedback) and of hearing aids employing implanted piezoelectric elements Primary Examiner-Ralph D. Blakeslee Attorney, Agent, or FirmSim 8; McBurney- [30] Foreign Application Priority Data July 18, 1972 Great Britain 33476/72 (high power requirements and microtrauma) are e1im 1 inated or attenuated by implanting a coil and magnet [52] US. Cl 179/107 E, 179/107 R in the e after removal of the incus, the magnet being [5]] IIILCI H04! 25/00 fastened to the head of the stapes and the Coil being I Field of Search 179/107 R7 107 107 BC energized by electrical signals from a sound transducer and producing a magnetic field which, interact- [56] Referen? Cited ing with the magnetic field of the magnet, causes UNITED STATES PATE S movement of the stapes in the same manner as it nor- 3,061,689 10/1962 McCarrell 179/107 E ma y s moved y the mens- 3,712,962 1/1973 Epley 179/107 R 3,764,748 10/1973 Branch 179/107 E 10 Claims 11 Drawing Figures PATENTED MAR] 1 I375 SHEET 2 0F 3 i I I IMPLANTABLE ELECTROMAGNETIC HEARING AID This' application is a continuation-in-part of Ser. No. 364,938 filed May 29, 1973, now abandoned.
BACKGROUND OF THE INVENTION This invention relates to hearing aids. More particularly, this invention relates to hearing aids that operate electromagnetically and some of the components of which areimplantable.
A conventional hearing aid consists of a microphone, an amplifier, batteries and a loudspeaker. All of these components are mounted externally on the user, and various attempts have been made to disguise of hidethem, as by building them into the earpieces of eyeglasses for example.
There is a considerable number of people with severe sensorineural hearing losses who are not adequately served by the most modern hearing aids that are available. The reasons for this revolve around the distortion inherent in the individuals hearing loss as well as the superadded distortion in the hearing aid which may include low fidelity, poor lowfrequency response and feedback.
Many conventional hearing aids require an ear mould and ear tubing. These components must be custom made, which is expensive. Moreover, if they are not made perfectly, feedback and consequent distortion problems are likely to arise.
A number of attempts have been made to solve the aforesaid problems. Thus it is known to place a magnet on the eardrum with a coil in an externally located earpiece and energize the coil via a microphone and amplifier. A hearing aid of this type suffers from low efficiency because the coil is located too far from the magnet. In addition, such a system does not provide a permanent solution for hearing loss because the magnet on the eardrum will be displaced-in a short time by migration of the epithelium. Epithelial migration commences at the eardrum. Only about six weeks is required for the epithelium to leave the eardrum, and only about five months is required for it to come out of the ear canal. Another disadvantage of this system is its high power requirements. This is due not only to the large distance between the externally located coil and implanted magnet, but also to the large mass (eardrum and ossicles) that must be moved, taking into consideration that all that really is required is movement of the stapes, and the area ratio of eardrum to stapes footplate is about 15:1.
In U.S. Pat. No. 3,594,514 dated July 20, 1971, R- bert C. Wingrove, and U.S. Pat. No. 3,712,962 dated Jan. 23, 1973, J.M. Epley, there are described implantable hearing aids that utilize piezoelectric ceramic elements. From an electrical point of view such systems, as compared to the electromagnetic system to be disclosed herein, have a higher impedance and higher voltage requirements. In fact such systems probably will require about a volt battery, which would be ezoelectric ceramic element will, as a result of its continually striking the bone (one of the ossicles) with which it cooperates, create microtrauma and erosion of that bone.
In accordance with my invention there is provided a hearing aid which eliminates or attenuates many of the disadvantages of conventional hearing aids of the type noted previously as well as those of hearing aids of the types noted in the two preceding paragraphs.
SUMMARY OF THE INVENTION A hearing aid embodying my invention may include a microphone, amplifier and a battery or batteries (or other suitable sound transducer), as is conventional, all of which may be located in a small housing that may be hidden behind one ear of the individual and which may plug into a receptacle and socket implated in the temporal bone behind the ear. The hearing aid further includes an implanted electromagnetic device that replaces the loudspeaker, tubing and earmould of a conventional hearing aid. This device consists of a magnet that is permanently attached to the stapes (one of the three auditory ossicles) and an implanted coil that is located in close proximity to the magnet and which receives electrical signals from the sound transducer. Also provided is a suitable support for the coil.
BRIEF DESCRIPTION OF THE DRAWINGS The invention will become more apparent from the following detailed description, taken in conjunction with the appended drawings, in which:
FIG. 1 is a perspective view showing the aforesaid housing located behind the ear of an individual;
FIG. 2 is a horizontal section through a normal human ear but with the outer tissue folded over on itself;
FIG. 3 is a view similar to that of FIG. 2 but with the incus removed, a necessary step in the operative procedure for implanting certain components of a hearing aid embodying my invention;
FIG. 4 is a view similar to that of FIG. 2 but showing these components in place;
FIG. 5 is a side view of an individuals right ear with the tissue removed and showing the same components as are seen in FIG. 4;
FIGS. 6 and 7 are top and side views respectively showing the stapes and the components illustrated in FIGS. 4 and 5;
FIG. 8 is a view similar to that of FIG. 7 but with the coil and its support removed;
FIG. 9 is a view similar to FIG. 8 but showing another embodiment of my invention;
FIG. 10 is an exploded view of certain components ,of a hearing aid embodying my invention; and
FIG. 11 is a schematic diagram of a hearing aid embodying my invention.
Referring to FIG. I, a hearing aid embodying my in- I vention includes a housing 10 (see also FIG. 10) in which, as shown in FIG. 11, may be located a microphone 30, an amplifier 31 and a battery 32. This housing is very small and can be located behind the ear tissue of an individual. It has three male terminals 33 (FIG. 10) projecting therefrom adapted to plug into three female terminals 34 in a receptacle 11 (FIGS. 6 and 10). As best shown in FIG. 10, receptacle ll fits into and externally threaded socket 35. The lower part 36 of socket 35 is permanently implanted by an operative procedure into the temporal bone of the patient. This procedure requires tapping a hole in the temporal bone immediately behind the ear to accommodate the lower part 36 of socket 35, this part being screwed into the tapped opening. Once housing has been plugged into receptacle 11, an internally threaded cap 37 (FIGS. 1 and 10) is threadably engaged with the upper part 38 of socket 35 to hold housing 10 and receptacle 11 in position. A cap (not shown) similar to cap 37 but with its top end closed may be provided and used in place of cap 37 when the individual is showering or swimming. lllustratively socket 35 may be about 1 cm. long and have a maximum diameter of about 1.3 cm.
Two of the three terminals 33 are, in fact, the output terminals of amplifier 31, the latter being powered by battery 32 and serving to amplify sounds picked up by microphone 30. The third terminal is for stability and locating. The microphone, amplifier and battery may be of a conventional type. A suitable microphone is a condensor microphone model No. BL1680 made by Knowles Electronics Inc., Franklin Park, Illinois. Amplifier 31 preferably is a logarithmic amplifier. Two suitable amplifiers both manufactured by Robert Bosch Electronic Company of Berlin, West Germany are STAR 6 (trade mark) dynamic range compression (DRC) amplifier and OMNITRON 11" (trade mark) DRC amplifier. The battery may be an EVEREADY (trade mark) model E675 1.4 volt mercury battery.
It should be understood, of course, that microphone 30, amplifier 31 and battery 32 individually or in total may be located elsewhere than behind the ear.
The other part of a hearing aid embodying my invention consists of a magnet 12 (FIGS. 5, 6, 8 and 12), which, in the embodiment shown, is cylindrical in con figuration, and which is secured to the stapes 13; a coil 14 located in close proximity to magnet 12; a support or holder 15 for the coil; and two lead-in conductors 16 connected between terminals 34 of receptacle 11 and coil 14. All of these components are surgically implanted.
As shown in FIGS. 4, 6, 7 and 8, a holder 17 for magnet 12 is provided. This holder may be fabricated of TEFLON" (trade mark), for example, and is designed so as to be readily attached to stapes 13. Magnet 12 may be encased in the material of the holder. In another embodiment of the invention shown in FIG. 9 magnet 12 is firmly secured to the head of stapes 13 by a non tissue toxic cement such as SILASTIC (trade mark) or CRANIOPLAST (trade mark). In this embodiment, unless magnet 12 is encapsulated in a non tissue toxic material, it itself must be non tissue toxic. Thus, it may be made ofVITALLIUM" (trade mark), for example. However, a superior magnet is one made of cobalt symareum and available from the General Electric Company, Schenectady, New York. Such a magnet requires encapsulation in a non tissue toxic material.
Regardless of how magnet 12 is secured to stapes 13, it must be firmly fastened thereto so that the magnet and stapes move as a unit without relative movement there-between in order to avoid microtrauma. This poses no problem where cement is used. Where holder 17 is mechanically secured to the stapes without cement, the inherent springiness of the holder material may be relied upon to provide the required connection or, depending on the holder material, it may be crimped in position.
In order to implant components 12 and 15 to 17 a maistoidectomy is performed, the facial triangle bone is removed from the posterior bony ear canal wall and the incus 18 (FIG. 2) is removed. Magnet 12 then is firmly secured to stapes 13. In the embodiment shown in FIGS. 4, 7 and 8 this is accomplished by fastening holder 17 to stapes 13, but it also may be accomplished by cementing the magnet or its encapsulating material to the stapes using a suitable cement as shown in FIG. 9. By means of a tool 19 (FIG. 4) which threadably engages a connector 20 (FIG. 4) secured to holder 15, coil 14 and holder 15 are positioned in place and holder 15 is permanently cemented in position using a suitable non tissue toxic cement 40 (FIG. 4) such as CRANIOPLAST" (trade mark). This operation is performed using a suitable micromanipulator. Tool 19 then is removed.
After tool 19 has been removed, wires 16, which preferably are made of gold, are led into socket 35 through a small opening in the bottom wall thereof, are passed through and out of the socket and then are soldered to terminals 34. Socket 35 than may be screwed into the previously tapped opening in the mastoid tip of the temporal bone behind the patients ear and components l1, l0 and 37 located in position as previously explained herein.
When coil 14 is energized by electrical signals from amplifier 31, the interaction of the magnetic field of coil 14 thereby created and the magnetic field of magnet 12 causes stapes 13 to function in its normal way like a piston causing vibration of the inner ear fluids in response to sound pick up by microphone 30.
It should be understood that my invention also may be practised using an implanted receiver and an external microphone and transmitter as'disclosed in aforementioned U.S. Pat. No. 3,712,962, the piezoelectric element disclosed in this patent being replaced with the electromagnetic system disclosed herein.
What I claim as my invention is:
l. A hearing aid having certain components thereof that are implanted in the ear of the user, said hearing aid comprising sound transducer means for converting audio signals to electrical signals and electromagnetic transducer means for receiving said electrical signals and converting said electrical signals into mechanical movement of the stapes bone of the ear of the user, said electromagnetic transducer means being implantable in the ear of the user and comprising a magnet, means for firmly securing said magnet to the head of the stapes bone of the user such that said magnet and said stapes bone move as a unit without relative movement there between when said magnet is attracted by a magnetic field and a coil of a size that permits it to be implanted in the middle ear space of the ear of the user, said coil being adapted to be implanted in the middle ear space .of the ear of the user in close proximity to said magnet,
said coil when energized by said electrical signals producing a magnetic field in which said magnet is located, said coil and said magnet being positioned with respect to each other such that upon energization of said coil said stapes bone moves as a result of the interaction between the magnetic field of said magnet and said magnetic field of said coil in the same manner as said stapes bone normally is moved by the incus bone, said hearing aid also including implantable support means for said coil, said support means being adapted to be secured to a bone that holds said coil in a fixed position in said middle ear space.
2. A hearing aid according to claim 1 wherein said sound transducer means comprises a microphone, an amplifier and a battery.
3. A hearing aid according to claim 2 further including a socket having electrical terminals therein, means electrically connecting said sound transducer means and said coil, said means electrically connecting said sound transducer means and said coil including implantable conductors connected to said terminals and to said coil for supplying said electrical signals to said coil, said socket being adapted to be located behind the ear of the user and secured to bone of the user thereat, a housing for said microphone, amplifier and battery, said housing having output terminals for said electrical signals, said housing being adapted for reception by said socket with said terminals of said socket electrically contacting said output terminals of said housing.
4. A hearing aid according to claim 3 wherein said socket is externally threaded to threadablyengage in a stapes bone of the user comprises a non tissue toxic cement.
6. A hearing aid according to claim 1 wherein said means for securing said magnet to the head of the stapes bones comprises a holder for said magnet, said holder being adapted for attachment to the head of the stapes bone of the user.
7. A hearing aid according to claim 1 including meansfor securing said support means to a bone that holds said coil in a fixed position in said middle ear space.
8. A hearing aid according to claim 7 wherein said means for securing said support means comprises a non tissue toxic cement.
9. A hearing aid having certain components thereof implanted in an ear of the user from which the incus has been removed, said hearing aid comprising sound transducer means for converting audio signals to electrical signals and electromechanical transducer means adapted to receive said electrical signals and convert said electrical signals into mechanical movement of the stapes bone of said ear of said user, said electromechanical transducer means being implanted in said ear of said user and comprising a magnet, means for firmly securing said magnet to the head of said stapes bone such that said magnet and said stapes bone move as a unit without relative movement therebetween when said magnet is attracted by a magnetic field and a coil implanted in the middle ear space of said ear in close proximity to said magnet, said coil when energized by said electrical signals producing a magnetic field in which said magnet is located, said coil and said magnet being positioned with respect to each other such that upon energization of said coil said stapes bone is moved as a result of the interaction between the magnetic field of said magnet and said magnetic field of said coil in the same manner as said stapes bone normally is moved by the incus bone, said hearing aid also including implanted support means for said coil for holding said coil in a fixed position .in said middle ear space, and means for securing said support means to a bone of said user that holds said coil in a fixed position in said middle ear space. a
10. A hearing aid according to claim 9 further including a socket having electrical terminals therein, said socket being implanted in' bone behind the ear of said user, implanted conductors connected to said terminals and to said coil for supplying said electrical signals to said coil, and a housing for said sound transducer, said housing having output terminals for said electrical signals and being received by said socket with said terminals of said socket electrically connecting said output
Claims (10)
1. A hearing aid having certain components thereof that are implanted in the ear of the user, said hearing aid comprising sound transducer means for converting audio signals to electrical signals and electromagnetic transducer means for receiving said electrical signals and converting said electrical signals into mechanical movement of the stapes bone of the ear of the user, said electromagnetic transducer means being implantable in the ear of the user and comprising a magnet, means for firmly securing said magnet to the head of the stapes bone of the user such that said magnet and said stapes bone move as a unit without relative movement therebetween when said magnet is attracted by a magnetic field and a coil of a size that permits it to be implanted in the middle ear spAce of the user, said coil being adapted to be implanted in the middle ear space of the ear of the user in close proximity to said magnet, said coil when energized by said electrical signals producing a magnetic field in which said magnet is located, said coil and said magnet being positioned with respect to each other such that upon energization of said coil said stapes bone moves as a result of the interaction between the magnetic field of said magnet and said magnetic field of said coil in the same manner as said stapes bone normally is moved by the incus bone, said hearing aid also including implantable support means for said coil, said support means being adapted to be secured to a bone that holds said coil in a fixed position in said middle ear space.
1. A hearing aid having certain components thereof that are implanted in the ear of the user, said hearing aid comprising sound transducer means for converting audio signals to electrical signals and electromagnetic transducer means for receiving said electrical signals and converting said electrical signals into mechanical movement of the stapes bone of the ear of the user, said electromagnetic transducer means being implantable in the ear of the user and comprising a magnet, means for firmly securing said magnet to the head of the stapes bone of the user such that said magnet and said stapes bone move as a unit without relative movement therebetween when said magnet is attracted by a magnetic field and a coil of a size that permits it to be implanted in the middle ear spAce of the user, said coil being adapted to be implanted in the middle ear space of the ear of the user in close proximity to said magnet, said coil when energized by said electrical signals producing a magnetic field in which said magnet is located, said coil and said magnet being positioned with respect to each other such that upon energization of said coil said stapes bone moves as a result of the interaction between the magnetic field of said magnet and said magnetic field of said coil in the same manner as said stapes bone normally is moved by the incus bone, said hearing aid also including implantable support means for said coil, said support means being adapted to be secured to a bone that holds said coil in a fixed position in said middle ear space.
2. A hearing aid according to claim 1 wherein said sound transducer means comprises a microphone, an amplifier and a battery.
3. A hearing aid according to claim 2 further including a socket having electrical terminals therein, means electrically connecting said sound transducer means and said coil, said means electrically connecting said sound transducer means and said coil including implantable conductors connected to said terminals and to said coil for supplying said electrical signals to said coil, said socket being adapted to be located behind the ear of the user and secured to bone of the user thereat, a housing for said microphone, amplifier and battery, said housing having output terminals for said electrical signals, said housing being adapted for reception by said socket with said terminals of said socket electrically contacting said output terminals of said housing.
4. A hearing aid according to claim 3 wherein said socket is externally threaded to threadably engage in a tapped opening in said bone behind the ear of the user.
5. A hearing aid according to claim 1 wherein said means for securing said magnet to the head of the stapes bone of the user comprises a non tissue toxic cement.
6. A hearing aid according to claim 1 wherein said means for securing said magnet to the head of the stapes bones comprises a holder for said magnet, said holder being adapted for attachment to the head of the stapes bone of the user.
7. A hearing aid according to claim 1 including means for securing said support means to a bone that holds said coil in a fixed position in said middle ear space.
8. A hearing aid according to claim 7 wherein said means for securing said support means comprises a non tissue toxic cement.
9. A hearing aid having certain components thereof implanted in an ear of the user from which the incus has been removed, said hearing aid comprising sound transducer means for converting audio signals to electrical signals and electromechanical transducer means adapted to receive said electrical signals and convert said electrical signals into mechanical movement of the stapes bone of said ear of said user, said electromechanical transducer means being implanted in said ear of said user and comprising a magnet, means for firmly securing said magnet to the head of said stapes bone such that said magnet and said stapes bone move as a unit without relative movement therebetween when said magnet is attracted by a magnetic field and a coil implanted in the middle ear space of said ear in close proximity to said magnet, said coil when energized by said electrical signals producing a magnetic field in which said magnet is located, said coil and said magnet being positioned with respect to each other such that upon energization of said coil said stapes bone is moved as a result of the interaction between the magnetic field of said magnet and said magnetic field of said coil in the same manner as said stapes bone normally is moved by the incus bone, said hearing aid also including implanted support means for said coil for holding said coil in a fixed position in said middle ear space, and means for securing said support means to a bone of said user that holds said coil in a fixed position in said middLe ear space.
Priority Applications (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
GB3144774A GB1440724A (en) | 1972-07-18 | 1974-07-16 | Implantable electromagnetic hearing aid |
US492675A US3870832A (en) | 1972-07-18 | 1974-07-29 | Implantable electromagnetic hearing aid |
Applications Claiming Priority (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
GB3347672 | 1972-07-18 | ||
US36493873A | 1973-05-29 | 1973-05-29 | |
GB3144774A GB1440724A (en) | 1972-07-18 | 1974-07-16 | Implantable electromagnetic hearing aid |
US492675A US3870832A (en) | 1972-07-18 | 1974-07-29 | Implantable electromagnetic hearing aid |
Publications (1)
Publication Number | Publication Date |
---|---|
US3870832A true US3870832A (en) | 1975-03-11 |
Family
ID=27448808
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US492675A Expired - Lifetime US3870832A (en) | 1972-07-18 | 1974-07-29 | Implantable electromagnetic hearing aid |
Country Status (2)
Country | Link |
---|---|
US (1) | US3870832A (en) |
GB (1) | GB1440724A (en) |
Cited By (106)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4352960A (en) * | 1980-09-30 | 1982-10-05 | Baptist Medical Center Of Oklahoma, Inc. | Magnetic transcutaneous mount for external device of an associated implant |
US4606329A (en) * | 1985-05-22 | 1986-08-19 | Xomed, Inc. | Implantable electromagnetic middle-ear bone-conduction hearing aid device |
US4612915A (en) * | 1985-05-23 | 1986-09-23 | Xomed, Inc. | Direct bone conduction hearing aid device |
US4628907A (en) * | 1984-03-22 | 1986-12-16 | Epley John M | Direct contact hearing aid apparatus |
US4729366A (en) * | 1984-12-04 | 1988-03-08 | Medical Devices Group, Inc. | Implantable hearing aid and method of improving hearing |
US4774933A (en) * | 1987-05-18 | 1988-10-04 | Xomed, Inc. | Method and apparatus for implanting hearing device |
US4776322A (en) * | 1985-05-22 | 1988-10-11 | Xomed, Inc. | Implantable electromagnetic middle-ear bone-conduction hearing aid device |
US4800884A (en) * | 1986-03-07 | 1989-01-31 | Richards Medical Company | Magnetic induction hearing aid |
US4817607A (en) * | 1986-03-07 | 1989-04-04 | Richards Medical Company | Magnetic ossicular replacement prosthesis |
USRE32947E (en) * | 1980-09-30 | 1989-06-13 | Baptist Medical Center Of Oklahoma, Inc. | Magnetic transcutaneous mount for external device of an associated implant |
US4840178A (en) * | 1986-03-07 | 1989-06-20 | Richards Metal Company | Magnet for installation in the middle ear |
US4850962A (en) * | 1984-12-04 | 1989-07-25 | Medical Devices Group, Inc. | Implantable hearing aid and method of improving hearing |
US4936305A (en) * | 1988-07-20 | 1990-06-26 | Richards Medical Company | Shielded magnetic assembly for use with a hearing aid |
US5015225A (en) * | 1985-05-22 | 1991-05-14 | Xomed, Inc. | Implantable electromagnetic middle-ear bone-conduction hearing aid device |
US5085628A (en) * | 1988-09-09 | 1992-02-04 | Storz Instrument Company | Implantable hearing aid coupler device |
US5220918A (en) * | 1988-11-16 | 1993-06-22 | Smith & Nephew Richards, Inc. | Trans-tympanic connector for magnetic induction hearing aid |
US5239588A (en) * | 1988-12-21 | 1993-08-24 | Davis Murray A | Hearing aid |
US5277694A (en) * | 1991-02-13 | 1994-01-11 | Implex Gmbh | Electromechanical transducer for implantable hearing aids |
EP0622057A2 (en) * | 1993-04-27 | 1994-11-02 | Medevelop Aktiebolag | Holding apparatus destined to be implanted into bone tissue for the controlled reception and fixation of equipment preferably usable for electrical information transmission |
WO1995001710A1 (en) * | 1993-07-01 | 1995-01-12 | Ball Geoffrey R | Implantable magnetic hearing aid transducer |
US5390254A (en) * | 1991-01-17 | 1995-02-14 | Adelman; Roger A. | Hearing apparatus |
US5456654A (en) * | 1993-07-01 | 1995-10-10 | Ball; Geoffrey R. | Implantable magnetic hearing aid transducer |
WO1996021335A1 (en) | 1995-01-03 | 1996-07-11 | Symphonix Devices, Inc. | Implantable and external hearing systems having a floating mass transducer |
WO1996022727A1 (en) * | 1995-01-26 | 1996-08-01 | Pierre Sabin | Transcutaneous electrical connection device for medical implant apparatus |
US5558618A (en) * | 1995-01-23 | 1996-09-24 | Maniglia; Anthony J. | Semi-implantable middle ear hearing device |
US5624376A (en) * | 1993-07-01 | 1997-04-29 | Symphonix Devices, Inc. | Implantable and external hearing systems having a floating mass transducer |
US5772575A (en) * | 1995-09-22 | 1998-06-30 | S. George Lesinski | Implantable hearing aid |
US5800336A (en) * | 1993-07-01 | 1998-09-01 | Symphonix Devices, Inc. | Advanced designs of floating mass transducers |
WO1998041056A1 (en) * | 1997-03-11 | 1998-09-17 | Symphonix Devices, Inc. | Improved dual coil floating mass transducers |
WO1999007436A1 (en) * | 1997-08-07 | 1999-02-18 | St. Croix Medical, Inc. | Electromagnetic input transducers for middle ear sensing |
US5881158A (en) * | 1996-05-24 | 1999-03-09 | United States Surgical Corporation | Microphones for an implantable hearing aid |
US5906635A (en) * | 1995-01-23 | 1999-05-25 | Maniglia; Anthony J. | Electromagnetic implantable hearing device for improvement of partial and total sensoryneural hearing loss |
US5951601A (en) * | 1996-03-25 | 1999-09-14 | Lesinski; S. George | Attaching an implantable hearing aid microactuator |
US5977689A (en) * | 1996-07-19 | 1999-11-02 | Neukermans; Armand P. | Biocompatible, implantable hearing aid microactuator |
US5984859A (en) * | 1993-01-25 | 1999-11-16 | Lesinski; S. George | Implantable auditory system components and system |
US6001129A (en) * | 1996-08-07 | 1999-12-14 | St. Croix Medical, Inc. | Hearing aid transducer support |
US6113531A (en) * | 1998-11-18 | 2000-09-05 | Implex Aktiengesellschaft Hearing Technology | Process for optimization of mechanical inner ear stimulation in partially or fully implantable hearing systems |
US6123660A (en) * | 1998-09-03 | 2000-09-26 | Implex Aktiengesellschaft Hearing Technology | Partially or fully implantable hearing aid |
US6137889A (en) * | 1998-05-27 | 2000-10-24 | Insonus Medical, Inc. | Direct tympanic membrane excitation via vibrationally conductive assembly |
US6139488A (en) * | 1997-09-25 | 2000-10-31 | Symphonix Devices, Inc. | Biasing device for implantable hearing devices |
US6162169A (en) * | 1998-09-03 | 2000-12-19 | Implex Aktiengesellschaft Hearing Technology | Transducer arrangement for partially or fully implantable hearing aids |
WO2001050815A1 (en) | 1999-12-30 | 2001-07-12 | Insonus Medical, Inc. | Direct tympanic drive via a floating filament assembly |
US6277148B1 (en) | 1999-02-11 | 2001-08-21 | Soundtec, Inc. | Middle ear magnet implant, attachment device and method, and test instrument and method |
US6315710B1 (en) | 1997-07-21 | 2001-11-13 | St. Croix Medical, Inc. | Hearing system with middle ear transducer mount |
EP1179969A2 (en) | 2000-08-11 | 2002-02-13 | Phonak Ag | At least partially implantable hearing system |
US6398717B1 (en) | 1999-05-21 | 2002-06-04 | Phonak Ag | Device for mechanical coupling of an electromechanical hearing aid converter which can be implanted in a mastoid cavity |
US6436028B1 (en) | 1999-12-28 | 2002-08-20 | Soundtec, Inc. | Direct drive movement of body constituent |
US6482144B1 (en) | 1999-10-07 | 2002-11-19 | Phonak Ag | Arrangement for mechanical coupling of a driver to a coupling site of the ossicular chain |
US6488616B1 (en) | 1996-08-07 | 2002-12-03 | St. Croix Medical, Inc. | Hearing aid transducer support |
WO2002098506A1 (en) * | 2001-06-01 | 2002-12-12 | St. Croix Medical, Inc. | Flexible transducer suports |
US6516228B1 (en) * | 2000-02-07 | 2003-02-04 | Epic Biosonics Inc. | Implantable microphone for use with a hearing aid or cochlear prosthesis |
US6537199B1 (en) | 1999-07-26 | 2003-03-25 | Phonak Ag | Arrangement for mechanical coupling of a driver to a coupling site of the ossicular chain |
US6540662B2 (en) | 1998-06-05 | 2003-04-01 | St. Croix Medical, Inc. | Method and apparatus for reduced feedback in implantable hearing assistance systems |
US6540661B1 (en) | 1999-10-07 | 2003-04-01 | Phonak Ag | Arrangement for coupling of a driver to a coupling site of the ossicular chain |
US6547715B1 (en) | 1999-07-08 | 2003-04-15 | Phonak Ag | Arrangement for mechanical coupling of a driver to a coupling site of the ossicular chain |
US6554762B2 (en) | 2000-08-25 | 2003-04-29 | Cochlear Limited | Implantable hearing system with means for measuring its coupling quality |
US6676592B2 (en) | 1993-07-01 | 2004-01-13 | Symphonix Devices, Inc. | Dual coil floating mass transducers |
US6689045B2 (en) | 1998-09-24 | 2004-02-10 | St. Croix Medical, Inc. | Method and apparatus for improving signal quality in implantable hearing systems |
US6730015B2 (en) | 2001-06-01 | 2004-05-04 | Mike Schugt | Flexible transducer supports |
US6840919B1 (en) | 1997-12-18 | 2005-01-11 | Osseofon Ab | Percutaneous bone anchored transferring device |
US20050113633A1 (en) * | 2003-01-15 | 2005-05-26 | Med-El Elektromedizinische Gerate Ges.M.B.H. | Implantable converter for cochlea implants and implantable hearing aids |
US6914994B1 (en) | 2001-09-07 | 2005-07-05 | Insound Medical, Inc. | Canal hearing device with transparent mode |
US6940988B1 (en) | 1998-11-25 | 2005-09-06 | Insound Medical, Inc. | Semi-permanent canal hearing device |
US20050199647A1 (en) * | 2004-02-06 | 2005-09-15 | Akio Muto | Automatic feeding device for syringes and saline water cartridge of radiopharmaceuticals dispensing and injection system |
US20050203557A1 (en) * | 2001-10-30 | 2005-09-15 | Lesinski S. G. | Implantation method for a hearing aid microactuator implanted into the cochlea |
US20050261544A1 (en) * | 2004-03-22 | 2005-11-24 | Gan Rong Z | Totally implantable hearing system |
US20050259840A1 (en) * | 1999-06-08 | 2005-11-24 | Insound Medical, Inc. | Precision micro-hole for extended life batteries |
US20050267591A1 (en) * | 2001-09-06 | 2005-12-01 | Ricci John L | Transcutaneous port having micro-textured surfaces for tissue and bone integration |
US20060050914A1 (en) * | 1998-11-25 | 2006-03-09 | Insound Medical, Inc. | Sealing retainer for extended wear hearing devices |
US7016504B1 (en) | 1999-09-21 | 2006-03-21 | Insonus Medical, Inc. | Personal hearing evaluator |
US20070003087A1 (en) * | 2005-06-30 | 2007-01-04 | Insound Medical, Inc. | Hearing aid microphone protective barrier |
US7226406B2 (en) | 2000-09-25 | 2007-06-05 | Cochlear Limited | At least partially implantable hearing system |
US20090074220A1 (en) * | 2007-08-14 | 2009-03-19 | Insound Medical, Inc. | Combined microphone and receiver assembly for extended wear canal hearing devices |
US20090141919A1 (en) * | 2005-08-22 | 2009-06-04 | 3Win N.V. | Combined set comprising a vibrator actuator and an implantable device |
US20090253951A1 (en) * | 1993-07-01 | 2009-10-08 | Vibrant Med-El Hearing Technology Gmbh | Bone conducting floating mass transducers |
US20100145135A1 (en) * | 2008-12-10 | 2010-06-10 | Vibrant Med-El Hearing Technology Gmbh | Skull Vibrational Unit |
US20100322452A1 (en) * | 2004-02-05 | 2010-12-23 | Insound Medical, Inc. | Contamination resistant ports for hearing devices |
US20110082327A1 (en) * | 2009-10-07 | 2011-04-07 | Manning Miles Goldsmith | Saline membranous coupling mechanism for electromagnetic and piezoelectric round window direct drive systems for hearing amplification |
WO2011066306A1 (en) | 2009-11-24 | 2011-06-03 | Med-El Elektromedizinische Geraete Gmbh | Implantable microphone for hearing systems |
US20110144414A1 (en) * | 2009-10-01 | 2011-06-16 | Ototronix, Llc | Middle ear implant and method |
US20110152603A1 (en) * | 2009-06-24 | 2011-06-23 | SoundBeam LLC | Optically Coupled Cochlear Actuator Systems and Methods |
US8682016B2 (en) | 2011-11-23 | 2014-03-25 | Insound Medical, Inc. | Canal hearing devices and batteries for use with same |
US8761423B2 (en) | 2011-11-23 | 2014-06-24 | Insound Medical, Inc. | Canal hearing devices and batteries for use with same |
US8808906B2 (en) | 2011-11-23 | 2014-08-19 | Insound Medical, Inc. | Canal hearing devices and batteries for use with same |
US9277335B2 (en) | 2009-06-18 | 2016-03-01 | Earlens Corporation | Eardrum implantable devices for hearing systems and methods |
US9544700B2 (en) | 2009-06-15 | 2017-01-10 | Earlens Corporation | Optically coupled active ossicular replacement prosthesis |
US9604325B2 (en) | 2011-11-23 | 2017-03-28 | Phonak, LLC | Canal hearing devices and batteries for use with same |
US10286215B2 (en) | 2009-06-18 | 2019-05-14 | Earlens Corporation | Optically coupled cochlear implant systems and methods |
US10321247B2 (en) | 2015-11-27 | 2019-06-11 | Cochlear Limited | External component with inductance and mechanical vibratory functionality |
US10492010B2 (en) | 2015-12-30 | 2019-11-26 | Earlens Corporations | Damping in contact hearing systems |
US10511913B2 (en) | 2008-09-22 | 2019-12-17 | Earlens Corporation | Devices and methods for hearing |
US10516951B2 (en) | 2014-11-26 | 2019-12-24 | Earlens Corporation | Adjustable venting for hearing instruments |
US10516950B2 (en) | 2007-10-12 | 2019-12-24 | Earlens Corporation | Multifunction system and method for integrated hearing and communication with noise cancellation and feedback management |
US10516949B2 (en) | 2008-06-17 | 2019-12-24 | Earlens Corporation | Optical electro-mechanical hearing devices with separate power and signal components |
US10531206B2 (en) | 2014-07-14 | 2020-01-07 | Earlens Corporation | Sliding bias and peak limiting for optical hearing devices |
US10555100B2 (en) | 2009-06-22 | 2020-02-04 | Earlens Corporation | Round window coupled hearing systems and methods |
US10609492B2 (en) | 2010-12-20 | 2020-03-31 | Earlens Corporation | Anatomically customized ear canal hearing apparatus |
US10629969B2 (en) | 2014-07-27 | 2020-04-21 | Sonova Ag | Batteries and battery manufacturing methods |
US10779094B2 (en) | 2015-12-30 | 2020-09-15 | Earlens Corporation | Damping in contact hearing systems |
US11058305B2 (en) | 2015-10-02 | 2021-07-13 | Earlens Corporation | Wearable customized ear canal apparatus |
US11102594B2 (en) | 2016-09-09 | 2021-08-24 | Earlens Corporation | Contact hearing systems, apparatus and methods |
US11166114B2 (en) | 2016-11-15 | 2021-11-02 | Earlens Corporation | Impression procedure |
US11212626B2 (en) | 2018-04-09 | 2021-12-28 | Earlens Corporation | Dynamic filter |
US11317224B2 (en) | 2014-03-18 | 2022-04-26 | Earlens Corporation | High fidelity and reduced feedback contact hearing apparatus and methods |
US11350226B2 (en) | 2015-12-30 | 2022-05-31 | Earlens Corporation | Charging protocol for rechargeable hearing systems |
US11516603B2 (en) | 2018-03-07 | 2022-11-29 | Earlens Corporation | Contact hearing device and retention structure materials |
Families Citing this family (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
NL181709C (en) * | 1977-02-18 | 1987-10-16 | Honeywell Bv | DEVICE FOR ADJUSTING A SKULL FOR INSTALLING A PRESSURE RECORDER. |
NL7801416A (en) * | 1977-03-04 | 1978-09-06 | Siemens Ag | IN THE SKULL OF A PATIENT SCREWABLE ADAPTER TO RECEIVE A PRESSURE CONVERTER. |
DE3707161A1 (en) * | 1987-03-06 | 1988-09-15 | Fleischer Gerald | EAR PROSTHESIS |
DE3918086C1 (en) * | 1989-06-02 | 1990-09-27 | Hortmann Gmbh, 7449 Neckartenzlingen, De |
Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3061689A (en) * | 1957-05-27 | 1962-10-30 | Beltone Hearing Aid Company | Hearing aid |
US3712962A (en) * | 1971-04-05 | 1973-01-23 | J Epley | Implantable piezoelectric hearing aid |
US3764748A (en) * | 1972-05-19 | 1973-10-09 | J Branch | Implanted hearing aids |
-
1974
- 1974-07-16 GB GB3144774A patent/GB1440724A/en not_active Expired
- 1974-07-29 US US492675A patent/US3870832A/en not_active Expired - Lifetime
Patent Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3061689A (en) * | 1957-05-27 | 1962-10-30 | Beltone Hearing Aid Company | Hearing aid |
US3712962A (en) * | 1971-04-05 | 1973-01-23 | J Epley | Implantable piezoelectric hearing aid |
US3764748A (en) * | 1972-05-19 | 1973-10-09 | J Branch | Implanted hearing aids |
Cited By (180)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4352960A (en) * | 1980-09-30 | 1982-10-05 | Baptist Medical Center Of Oklahoma, Inc. | Magnetic transcutaneous mount for external device of an associated implant |
USRE32947E (en) * | 1980-09-30 | 1989-06-13 | Baptist Medical Center Of Oklahoma, Inc. | Magnetic transcutaneous mount for external device of an associated implant |
US4628907A (en) * | 1984-03-22 | 1986-12-16 | Epley John M | Direct contact hearing aid apparatus |
US4850962A (en) * | 1984-12-04 | 1989-07-25 | Medical Devices Group, Inc. | Implantable hearing aid and method of improving hearing |
US4729366A (en) * | 1984-12-04 | 1988-03-08 | Medical Devices Group, Inc. | Implantable hearing aid and method of improving hearing |
FR2586557A1 (en) * | 1985-05-22 | 1987-03-06 | Bristol Myers Co | IMPLANTABLE ELECTROMAGNETIC DEVICE FOR ASSISTING BONE CONDUCTION HEARING IN THE MIDDLE EAR |
DE3617118A1 (en) * | 1985-05-22 | 1987-02-05 | Bristol Myers Co | IMPLANTABLE ELECTROMAGNETIC EARRING AID |
US4606329A (en) * | 1985-05-22 | 1986-08-19 | Xomed, Inc. | Implantable electromagnetic middle-ear bone-conduction hearing aid device |
NL8601307A (en) * | 1985-05-22 | 1986-12-16 | Bristol Myers Co | IMPLANTABLE ELECTROMAGNETIC HEARING AID WITH MIDDLE EAR CONDUCTION. |
US5015225A (en) * | 1985-05-22 | 1991-05-14 | Xomed, Inc. | Implantable electromagnetic middle-ear bone-conduction hearing aid device |
AU598464B2 (en) * | 1985-05-22 | 1990-06-28 | Soundtec, Inc. | Implantable electromagnetic middle-ear bone-conduction hearing aid device |
US4776322A (en) * | 1985-05-22 | 1988-10-11 | 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 |
JPH0552747B2 (en) * | 1985-05-23 | 1993-08-06 | Bristol Myers Squibb Co | |
JPS61273100A (en) * | 1985-05-23 | 1986-12-03 | ブリストル−マイヤ−ズ・コンパニ− | Hearing aid |
US4840178A (en) * | 1986-03-07 | 1989-06-20 | Richards Metal Company | Magnet for installation in the middle ear |
US4800884A (en) * | 1986-03-07 | 1989-01-31 | Richards Medical Company | Magnetic induction hearing aid |
US4817607A (en) * | 1986-03-07 | 1989-04-04 | Richards Medical Company | Magnetic ossicular replacement prosthesis |
EP0263254A1 (en) * | 1986-08-11 | 1988-04-13 | Medical Devices Group, Inc. | Implantable hearing aid |
AU608844B2 (en) * | 1987-05-15 | 1991-04-18 | Richards Medical Company | Magnet for installation in the middle ear |
US4774933A (en) * | 1987-05-18 | 1988-10-04 | Xomed, Inc. | Method and apparatus for implanting hearing device |
US4936305A (en) * | 1988-07-20 | 1990-06-26 | Richards Medical Company | Shielded magnetic assembly for use with a hearing aid |
US5085628A (en) * | 1988-09-09 | 1992-02-04 | Storz Instrument Company | Implantable hearing aid coupler device |
US5220918A (en) * | 1988-11-16 | 1993-06-22 | Smith & Nephew Richards, Inc. | Trans-tympanic connector for magnetic induction hearing aid |
US5239588A (en) * | 1988-12-21 | 1993-08-24 | Davis Murray A | Hearing aid |
US6041129A (en) * | 1991-01-17 | 2000-03-21 | Adelman; Roger A. | Hearing apparatus |
US5390254A (en) * | 1991-01-17 | 1995-02-14 | Adelman; Roger A. | Hearing apparatus |
US5277694A (en) * | 1991-02-13 | 1994-01-11 | Implex Gmbh | Electromechanical transducer for implantable hearing aids |
US5984859A (en) * | 1993-01-25 | 1999-11-16 | Lesinski; S. George | Implantable auditory system components and system |
EP0622057A2 (en) * | 1993-04-27 | 1994-11-02 | Medevelop Aktiebolag | Holding apparatus destined to be implanted into bone tissue for the controlled reception and fixation of equipment preferably usable for electrical information transmission |
US5562670A (en) * | 1993-04-27 | 1996-10-08 | Medevelop Ab | Holding means and method of implantation thereof in osseous tissue |
EP0622057A3 (en) * | 1993-04-27 | 1995-01-04 | Medevelop Ab | Holding apparatus destined to be implanted into bone tissue for the controlled reception and fixation of equipment preferably usable for electrical information transmission. |
AU681378B2 (en) * | 1993-04-27 | 1997-08-28 | Medevelop Ab | Holding means and method of implantation of osseous tissue |
US20090253951A1 (en) * | 1993-07-01 | 2009-10-08 | Vibrant Med-El Hearing Technology Gmbh | Bone conducting floating mass transducers |
WO1995001710A1 (en) * | 1993-07-01 | 1995-01-12 | Ball Geoffrey R | Implantable magnetic hearing aid transducer |
US6475134B1 (en) | 1993-07-01 | 2002-11-05 | Symphonix Devices, Inc. | Dual coil floating mass transducers |
US6676592B2 (en) | 1993-07-01 | 2004-01-13 | Symphonix Devices, Inc. | Dual coil floating mass transducers |
US5624376A (en) * | 1993-07-01 | 1997-04-29 | Symphonix Devices, Inc. | Implantable and external hearing systems having a floating mass transducer |
US5913815A (en) * | 1993-07-01 | 1999-06-22 | Symphonix Devices, Inc. | Bone conducting floating mass transducers |
AU683671B2 (en) * | 1993-07-01 | 1997-11-20 | Vibrant Med-El Hearing Technology Gmbh | Implantable magnetic hearing aid transducer |
US5897486A (en) * | 1993-07-01 | 1999-04-27 | Symphonix Devices, Inc. | Dual coil floating mass transducers |
US5800336A (en) * | 1993-07-01 | 1998-09-01 | Symphonix Devices, Inc. | Advanced designs of floating mass transducers |
US5456654A (en) * | 1993-07-01 | 1995-10-10 | Ball; Geoffrey R. | Implantable magnetic hearing aid transducer |
US5857958A (en) * | 1993-07-01 | 1999-01-12 | Symphonix Devices, Inc. | Implantable and external hearing systems having a floating mass transducer |
US5554096A (en) * | 1993-07-01 | 1996-09-10 | Symphonix | Implantable electromagnetic hearing transducer |
WO1996021335A1 (en) | 1995-01-03 | 1996-07-11 | Symphonix Devices, Inc. | Implantable and external hearing systems having a floating mass transducer |
US5906635A (en) * | 1995-01-23 | 1999-05-25 | Maniglia; Anthony J. | Electromagnetic implantable hearing device for improvement of partial and total sensoryneural hearing loss |
US5558618A (en) * | 1995-01-23 | 1996-09-24 | Maniglia; Anthony J. | Semi-implantable middle ear hearing device |
WO1996022727A1 (en) * | 1995-01-26 | 1996-08-01 | Pierre Sabin | Transcutaneous electrical connection device for medical implant apparatus |
FR2729844A1 (en) * | 1995-01-26 | 1996-08-02 | Sabin Pierre Jean Claude | IMPLANT MEDICAL DEVICE ASSEMBLY FOR ELECTRICAL CONNECTIONS THROUGH THE SKIN |
US5772575A (en) * | 1995-09-22 | 1998-06-30 | S. George Lesinski | Implantable hearing aid |
US5951601A (en) * | 1996-03-25 | 1999-09-14 | Lesinski; S. George | Attaching an implantable hearing aid microactuator |
US5881158A (en) * | 1996-05-24 | 1999-03-09 | United States Surgical Corporation | Microphones for an implantable hearing aid |
US5977689A (en) * | 1996-07-19 | 1999-11-02 | Neukermans; Armand P. | Biocompatible, implantable hearing aid microactuator |
US6153966A (en) * | 1996-07-19 | 2000-11-28 | Neukermans; Armand P. | Biocompatible, implantable hearing aid microactuator |
US6001129A (en) * | 1996-08-07 | 1999-12-14 | St. Croix Medical, Inc. | Hearing aid transducer support |
US6488616B1 (en) | 1996-08-07 | 2002-12-03 | St. Croix Medical, Inc. | Hearing aid transducer support |
WO1998041056A1 (en) * | 1997-03-11 | 1998-09-17 | Symphonix Devices, Inc. | Improved dual coil floating mass transducers |
US6315710B1 (en) | 1997-07-21 | 2001-11-13 | St. Croix Medical, Inc. | Hearing system with middle ear transducer mount |
US5993376A (en) * | 1997-08-07 | 1999-11-30 | St. Croix Medical, Inc. | Electromagnetic input transducers for middle ear sensing |
WO1999007436A1 (en) * | 1997-08-07 | 1999-02-18 | St. Croix Medical, Inc. | Electromagnetic input transducers for middle ear sensing |
US6139488A (en) * | 1997-09-25 | 2000-10-31 | Symphonix Devices, Inc. | Biasing device for implantable hearing devices |
US6840919B1 (en) | 1997-12-18 | 2005-01-11 | Osseofon Ab | Percutaneous bone anchored transferring device |
US6137889A (en) * | 1998-05-27 | 2000-10-24 | Insonus Medical, Inc. | Direct tympanic membrane excitation via vibrationally conductive assembly |
US6755778B2 (en) | 1998-06-05 | 2004-06-29 | St. Croix Medical, Inc. | Method and apparatus for reduced feedback in implantable hearing assistance systems |
US6540662B2 (en) | 1998-06-05 | 2003-04-01 | St. Croix Medical, Inc. | Method and apparatus for reduced feedback in implantable hearing assistance systems |
DE19840212C2 (en) * | 1998-09-03 | 2001-08-02 | Implex Hear Tech Ag | Transducer arrangement for partially or fully implantable hearing aids |
US6162169A (en) * | 1998-09-03 | 2000-12-19 | Implex Aktiengesellschaft Hearing Technology | Transducer arrangement for partially or fully implantable hearing aids |
US6123660A (en) * | 1998-09-03 | 2000-09-26 | Implex Aktiengesellschaft Hearing Technology | Partially or fully implantable hearing aid |
US6689045B2 (en) | 1998-09-24 | 2004-02-10 | St. Croix Medical, Inc. | Method and apparatus for improving signal quality in implantable hearing systems |
US6113531A (en) * | 1998-11-18 | 2000-09-05 | Implex Aktiengesellschaft Hearing Technology | Process for optimization of mechanical inner ear stimulation in partially or fully implantable hearing systems |
US20060050914A1 (en) * | 1998-11-25 | 2006-03-09 | Insound Medical, Inc. | Sealing retainer for extended wear hearing devices |
US7424124B2 (en) | 1998-11-25 | 2008-09-09 | Insound Medical, Inc. | Semi-permanent canal hearing device |
US20080137892A1 (en) * | 1998-11-25 | 2008-06-12 | Insound Medical, Inc. | Semi-permanent canal hearing device and insertion method |
US8538055B2 (en) | 1998-11-25 | 2013-09-17 | Insound Medical, Inc. | Semi-permanent canal hearing device and insertion method |
US7664282B2 (en) | 1998-11-25 | 2010-02-16 | Insound Medical, Inc. | Sealing retainer for extended wear hearing devices |
US8503707B2 (en) | 1998-11-25 | 2013-08-06 | Insound Medical, Inc. | Sealing retainer for extended wear hearing devices |
US6940988B1 (en) | 1998-11-25 | 2005-09-06 | Insound Medical, Inc. | Semi-permanent canal hearing device |
US20100098281A1 (en) * | 1998-11-25 | 2010-04-22 | Insound Medical, Inc. | Sealing retainer for extended wear hearing devices |
US6277148B1 (en) | 1999-02-11 | 2001-08-21 | Soundtec, Inc. | Middle ear magnet implant, attachment device and method, and test instrument and method |
US6398717B1 (en) | 1999-05-21 | 2002-06-04 | Phonak Ag | Device for mechanical coupling of an electromechanical hearing aid converter which can be implanted in a mastoid cavity |
US8068630B2 (en) | 1999-06-08 | 2011-11-29 | Insound Medical, Inc. | Precision micro-hole for extended life batteries |
US8666101B2 (en) | 1999-06-08 | 2014-03-04 | Insound Medical, Inc. | Precision micro-hole for extended life batteries |
US20050259840A1 (en) * | 1999-06-08 | 2005-11-24 | Insound Medical, Inc. | Precision micro-hole for extended life batteries |
US7379555B2 (en) | 1999-06-08 | 2008-05-27 | Insound Medical, Inc. | Precision micro-hole for extended life batteries |
US6547715B1 (en) | 1999-07-08 | 2003-04-15 | Phonak Ag | Arrangement for mechanical coupling of a driver to a coupling site of the ossicular chain |
US6537199B1 (en) | 1999-07-26 | 2003-03-25 | Phonak Ag | Arrangement for mechanical coupling of a driver to a coupling site of the ossicular chain |
US7016504B1 (en) | 1999-09-21 | 2006-03-21 | Insonus Medical, Inc. | Personal hearing evaluator |
US20060210090A1 (en) * | 1999-09-21 | 2006-09-21 | Insound Medical, Inc. | Personal hearing evaluator |
US6482144B1 (en) | 1999-10-07 | 2002-11-19 | Phonak Ag | Arrangement for mechanical coupling of a driver to a coupling site of the ossicular chain |
US6540661B1 (en) | 1999-10-07 | 2003-04-01 | Phonak Ag | Arrangement for coupling of a driver to a coupling site of the ossicular chain |
US6436028B1 (en) | 1999-12-28 | 2002-08-20 | Soundtec, Inc. | Direct drive movement of body constituent |
WO2001050815A1 (en) | 1999-12-30 | 2001-07-12 | Insonus Medical, Inc. | Direct tympanic drive via a floating filament assembly |
US6940989B1 (en) | 1999-12-30 | 2005-09-06 | Insound Medical, Inc. | Direct tympanic drive via a floating filament assembly |
US6516228B1 (en) * | 2000-02-07 | 2003-02-04 | Epic Biosonics Inc. | Implantable microphone for use with a hearing aid or cochlear prosthesis |
EP1179969A2 (en) | 2000-08-11 | 2002-02-13 | Phonak Ag | At least partially implantable hearing system |
US6592512B2 (en) | 2000-08-11 | 2003-07-15 | Phonak Ag | At least partially implantable system for rehabilitation of a hearing disorder |
US6554762B2 (en) | 2000-08-25 | 2003-04-29 | Cochlear Limited | Implantable hearing system with means for measuring its coupling quality |
US8105229B2 (en) | 2000-09-15 | 2012-01-31 | Cochlear Limited | At least partially implantable hearing system |
US20070249890A1 (en) * | 2000-09-15 | 2007-10-25 | Cochlear Limited | At least partially implantable hearing system |
US7226406B2 (en) | 2000-09-25 | 2007-06-05 | Cochlear Limited | At least partially implantable hearing system |
US6730015B2 (en) | 2001-06-01 | 2004-05-04 | Mike Schugt | Flexible transducer supports |
WO2002098506A1 (en) * | 2001-06-01 | 2002-12-12 | St. Croix Medical, Inc. | Flexible transducer suports |
US8075630B2 (en) * | 2001-09-06 | 2011-12-13 | Bio-Lok International, Inc. | Transcutaneous port having micro-textured surfaces for tissue and bone integration |
US20050267591A1 (en) * | 2001-09-06 | 2005-12-01 | Ricci John L | Transcutaneous port having micro-textured surfaces for tissue and bone integration |
US20060002574A1 (en) * | 2001-09-07 | 2006-01-05 | Insound Medical, Inc. | Canal hearing device with transparent mode |
US6914994B1 (en) | 2001-09-07 | 2005-07-05 | Insound Medical, Inc. | Canal hearing device with transparent mode |
US20050203557A1 (en) * | 2001-10-30 | 2005-09-15 | Lesinski S. G. | Implantation method for a hearing aid microactuator implanted into the cochlea |
US8147544B2 (en) | 2001-10-30 | 2012-04-03 | Otokinetics Inc. | Therapeutic appliance for cochlea |
US8876689B2 (en) | 2001-10-30 | 2014-11-04 | Otokinetics Inc. | Hearing aid microactuator |
US20050113633A1 (en) * | 2003-01-15 | 2005-05-26 | Med-El Elektromedizinische Gerate Ges.M.B.H. | Implantable converter for cochlea implants and implantable hearing aids |
US7481761B2 (en) | 2003-01-15 | 2009-01-27 | Med-El Elektromedizinische Geräte Ges.m.b.H. | Implantable converter for cochlea implants and implantable hearing aids |
US20100322452A1 (en) * | 2004-02-05 | 2010-12-23 | Insound Medical, Inc. | Contamination resistant ports for hearing devices |
US8457336B2 (en) | 2004-02-05 | 2013-06-04 | Insound Medical, Inc. | Contamination resistant ports for hearing devices |
US20050199647A1 (en) * | 2004-02-06 | 2005-09-15 | Akio Muto | Automatic feeding device for syringes and saline water cartridge of radiopharmaceuticals dispensing and injection system |
US20050261544A1 (en) * | 2004-03-22 | 2005-11-24 | Gan Rong Z | Totally implantable hearing system |
US7651460B2 (en) * | 2004-03-22 | 2010-01-26 | The Board Of Regents Of The University Of Oklahoma | Totally implantable hearing system |
US20110085688A1 (en) * | 2005-06-30 | 2011-04-14 | Insound Medical, Inc. | Hearing aid microphone protective barrier |
US8494200B2 (en) | 2005-06-30 | 2013-07-23 | Insound Medical, Inc. | Hearing aid microphone protective barrier |
US7876919B2 (en) | 2005-06-30 | 2011-01-25 | Insound Medical, Inc. | Hearing aid microphone protective barrier |
US20070003087A1 (en) * | 2005-06-30 | 2007-01-04 | Insound Medical, Inc. | Hearing aid microphone protective barrier |
US8184840B2 (en) * | 2005-08-22 | 2012-05-22 | 3Win N.V. | Combined set comprising a vibrator actuator and an implantable device |
US20090141919A1 (en) * | 2005-08-22 | 2009-06-04 | 3Win N.V. | Combined set comprising a vibrator actuator and an implantable device |
US9071914B2 (en) | 2007-08-14 | 2015-06-30 | Insound Medical, Inc. | Combined microphone and receiver assembly for extended wear canal hearing devices |
US20090074220A1 (en) * | 2007-08-14 | 2009-03-19 | Insound Medical, Inc. | Combined microphone and receiver assembly for extended wear canal hearing devices |
US10516950B2 (en) | 2007-10-12 | 2019-12-24 | Earlens Corporation | Multifunction system and method for integrated hearing and communication with noise cancellation and feedback management |
US10863286B2 (en) | 2007-10-12 | 2020-12-08 | Earlens Corporation | Multifunction system and method for integrated hearing and communication with noise cancellation and feedback management |
US11483665B2 (en) | 2007-10-12 | 2022-10-25 | Earlens Corporation | Multifunction system and method for integrated hearing and communication with noise cancellation and feedback management |
US11310605B2 (en) | 2008-06-17 | 2022-04-19 | Earlens Corporation | Optical electro-mechanical hearing devices with separate power and signal components |
US10516949B2 (en) | 2008-06-17 | 2019-12-24 | Earlens Corporation | Optical electro-mechanical hearing devices with separate power and signal components |
US11057714B2 (en) | 2008-09-22 | 2021-07-06 | Earlens Corporation | Devices and methods for hearing |
US10516946B2 (en) | 2008-09-22 | 2019-12-24 | Earlens Corporation | Devices and methods for hearing |
US10511913B2 (en) | 2008-09-22 | 2019-12-17 | Earlens Corporation | Devices and methods for hearing |
US10743110B2 (en) | 2008-09-22 | 2020-08-11 | Earlens Corporation | Devices and methods for hearing |
US20100145135A1 (en) * | 2008-12-10 | 2010-06-10 | Vibrant Med-El Hearing Technology Gmbh | Skull Vibrational Unit |
US9113277B2 (en) * | 2008-12-10 | 2015-08-18 | Vibrant Med-El Hearing Technology Gmbh | Skull vibrational unit |
US9544700B2 (en) | 2009-06-15 | 2017-01-10 | Earlens Corporation | Optically coupled active ossicular replacement prosthesis |
US10286215B2 (en) | 2009-06-18 | 2019-05-14 | Earlens Corporation | Optically coupled cochlear implant systems and methods |
US9277335B2 (en) | 2009-06-18 | 2016-03-01 | Earlens Corporation | Eardrum implantable devices for hearing systems and methods |
US10555100B2 (en) | 2009-06-22 | 2020-02-04 | Earlens Corporation | Round window coupled hearing systems and methods |
US11323829B2 (en) | 2009-06-22 | 2022-05-03 | Earlens Corporation | Round window coupled hearing systems and methods |
US8715154B2 (en) * | 2009-06-24 | 2014-05-06 | Earlens Corporation | Optically coupled cochlear actuator systems and methods |
US20110152603A1 (en) * | 2009-06-24 | 2011-06-23 | SoundBeam LLC | Optically Coupled Cochlear Actuator Systems and Methods |
EP2484126A4 (en) * | 2009-10-01 | 2014-08-20 | Ototronix Llc | Improved middle ear implant and method |
US20110144414A1 (en) * | 2009-10-01 | 2011-06-16 | Ototronix, Llc | Middle ear implant and method |
EP2484126A1 (en) * | 2009-10-01 | 2012-08-08 | Ototronix LLC | Improved middle ear implant and method |
US20110082327A1 (en) * | 2009-10-07 | 2011-04-07 | Manning Miles Goldsmith | Saline membranous coupling mechanism for electromagnetic and piezoelectric round window direct drive systems for hearing amplification |
WO2011066295A1 (en) | 2009-11-24 | 2011-06-03 | Med-El Elektromedizinische Geraete Gmbh | Implantable microphone for hearing systems |
WO2011066306A1 (en) | 2009-11-24 | 2011-06-03 | Med-El Elektromedizinische Geraete Gmbh | Implantable microphone for hearing systems |
US11743663B2 (en) | 2010-12-20 | 2023-08-29 | Earlens Corporation | Anatomically customized ear canal hearing apparatus |
US10609492B2 (en) | 2010-12-20 | 2020-03-31 | Earlens Corporation | Anatomically customized ear canal hearing apparatus |
US11153697B2 (en) | 2010-12-20 | 2021-10-19 | Earlens Corporation | Anatomically customized ear canal hearing apparatus |
US9060234B2 (en) | 2011-11-23 | 2015-06-16 | Insound Medical, Inc. | Canal hearing devices and batteries for use with same |
US10264372B2 (en) | 2011-11-23 | 2019-04-16 | Sonova Ag | Canal hearing devices and batteries for use with same |
US8808906B2 (en) | 2011-11-23 | 2014-08-19 | Insound Medical, Inc. | Canal hearing devices and batteries for use with same |
US8761423B2 (en) | 2011-11-23 | 2014-06-24 | Insound Medical, Inc. | Canal hearing devices and batteries for use with same |
US8682016B2 (en) | 2011-11-23 | 2014-03-25 | Insound Medical, Inc. | Canal hearing devices and batteries for use with same |
US9604325B2 (en) | 2011-11-23 | 2017-03-28 | Phonak, LLC | Canal hearing devices and batteries for use with same |
US11317224B2 (en) | 2014-03-18 | 2022-04-26 | Earlens Corporation | High fidelity and reduced feedback contact hearing apparatus and methods |
US10531206B2 (en) | 2014-07-14 | 2020-01-07 | Earlens Corporation | Sliding bias and peak limiting for optical hearing devices |
US11259129B2 (en) | 2014-07-14 | 2022-02-22 | Earlens Corporation | Sliding bias and peak limiting for optical hearing devices |
US11800303B2 (en) | 2014-07-14 | 2023-10-24 | Earlens Corporation | Sliding bias and peak limiting for optical hearing devices |
US10629969B2 (en) | 2014-07-27 | 2020-04-21 | Sonova Ag | Batteries and battery manufacturing methods |
US10516951B2 (en) | 2014-11-26 | 2019-12-24 | Earlens Corporation | Adjustable venting for hearing instruments |
US11252516B2 (en) | 2014-11-26 | 2022-02-15 | Earlens Corporation | Adjustable venting for hearing instruments |
US11058305B2 (en) | 2015-10-02 | 2021-07-13 | Earlens Corporation | Wearable customized ear canal apparatus |
US10321247B2 (en) | 2015-11-27 | 2019-06-11 | Cochlear Limited | External component with inductance and mechanical vibratory functionality |
US11516602B2 (en) | 2015-12-30 | 2022-11-29 | Earlens Corporation | Damping in contact hearing systems |
US11337012B2 (en) | 2015-12-30 | 2022-05-17 | Earlens Corporation | Battery coating for rechargable hearing systems |
US11350226B2 (en) | 2015-12-30 | 2022-05-31 | Earlens Corporation | Charging protocol for rechargeable hearing systems |
US11070927B2 (en) | 2015-12-30 | 2021-07-20 | Earlens Corporation | Damping in contact hearing systems |
US10779094B2 (en) | 2015-12-30 | 2020-09-15 | Earlens Corporation | Damping in contact hearing systems |
US10492010B2 (en) | 2015-12-30 | 2019-11-26 | Earlens Corporations | Damping in contact hearing systems |
US11102594B2 (en) | 2016-09-09 | 2021-08-24 | Earlens Corporation | Contact hearing systems, apparatus and methods |
US11540065B2 (en) | 2016-09-09 | 2022-12-27 | Earlens Corporation | Contact hearing systems, apparatus and methods |
US11166114B2 (en) | 2016-11-15 | 2021-11-02 | Earlens Corporation | Impression procedure |
US11671774B2 (en) | 2016-11-15 | 2023-06-06 | Earlens Corporation | Impression procedure |
US11516603B2 (en) | 2018-03-07 | 2022-11-29 | Earlens Corporation | Contact hearing device and retention structure materials |
US11212626B2 (en) | 2018-04-09 | 2021-12-28 | Earlens Corporation | Dynamic filter |
US11564044B2 (en) | 2018-04-09 | 2023-01-24 | Earlens Corporation | Dynamic filter |
Also Published As
Publication number | Publication date |
---|---|
GB1440724A (en) | 1976-06-23 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US3870832A (en) | Implantable electromagnetic hearing aid | |
US7526096B2 (en) | In the ear auxiliary microphone for behind the ear hearing prosthetic | |
US5411467A (en) | Implantable hearing aid | |
US5906635A (en) | Electromagnetic implantable hearing device for improvement of partial and total sensoryneural hearing loss | |
EP2577999B1 (en) | Implantable inner ear drive system | |
Yanagihara et al. | Development of an implantable hearing aid using a piezoelectric vibrator of bimorph design: state of the art | |
US20060015155A1 (en) | Partly implanted hearing aid | |
US7651460B2 (en) | Totally implantable hearing system | |
US7120501B2 (en) | Transcanal cochlear implant system | |
US20120029267A1 (en) | Electromagnetic Bone Conduction Hearing Device | |
US20090240099A1 (en) | Bi-modal cochlea stimulation | |
CA2280059C (en) | Implantable device for treatment of tinnitus | |
US20070106345A1 (en) | General purpose accessory for a cochlear implant system | |
US20090005836A1 (en) | Cochlear Implant | |
CN102598714A (en) | Round window coupled hearing systems and methods | |
EP1260118A2 (en) | An implantable microphone for use with a hearing aid or cochlear prosthesis | |
US20160094922A1 (en) | Positioned hearing system | |
JP2001506518A (en) | Implantable hearing aid with isolation electronics | |
Hüttenbrink | Current status and critical reflections on implantable hearing aids | |
CN101577850B (en) | Implanted piezoelectric ceramic microphone and manufacturing method thereof | |
US20110098787A1 (en) | Cochlear implant | |
EP4331660A1 (en) | Hearing implant and hearing system | |
Leuwer et al. | Restoration of hearing by hearing aids: conventional hearing aids–implantable hearing aids–cochlear implants–auditory brainstem implants | |
Sockalingam | Implantable Auditory Technologies. |