|Publication number||US3870832 A|
|Publication date||11 Mar 1975|
|Filing date||29 Jul 1974|
|Priority date||18 Jul 1972|
|Publication number||US 3870832 A, US 3870832A, US-A-3870832, US3870832 A, US3870832A|
|Inventors||John M Fredrickson|
|Original Assignee||John M Fredrickson|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (3), Referenced by (129), Classifications (12)|
|External Links: USPTO, USPTO Assignment, Espacenet|
United States Patent 1191 v 1111 3,870,832 Fredrickson Mar. 11, 1975 . IMPLANTABLE ELECTROMAGNETIC OTHER PUBLICATIONS EA NG AID H R! 1 Course Lecture Mater1al,p. 54, H6. 65, American  Inventor: John M. Fredrickson, 24 Queen Academy f opthamology and omlarynaology.
y D Toronto Ontario, Course 319, Conservative Tympanoplasty," Oct. 1, Canada 1966.
 Filed: July 29, 1974  App]. No.: 492,675
Related [1.8. Application Data  Continuation-in-part of Ser. No. 364,938, May 29,  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-  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  US. Cl 179/107 E, 179/107 R in the e after removal of the incus, the magnet being ] 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-  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.
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.
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.
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. Strictly by way of example, 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.
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.
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.
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
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US3061689 *||27 May 1957||30 Oct 1962||Beltone Hearing Aid Company||Hearing aid|
|US3712962 *||5 Apr 1971||23 Jan 1973||J Epley||Implantable piezoelectric hearing aid|
|US3764748 *||19 May 1972||9 Oct 1973||J Branch||Implanted hearing aids|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US4352960 *||30 Sep 1980||5 Oct 1982||Baptist Medical Center Of Oklahoma, Inc.||Magnetic transcutaneous mount for external device of an associated implant|
|US4606329 *||22 May 1985||19 Aug 1986||Xomed, Inc.||Implantable electromagnetic middle-ear bone-conduction hearing aid device|
|US4612915 *||23 May 1985||23 Sep 1986||Xomed, Inc.||Direct bone conduction hearing aid device|
|US4628907 *||22 Mar 1984||16 Dec 1986||Epley John M||Direct contact hearing aid apparatus|
|US4729366 *||11 Aug 1986||8 Mar 1988||Medical Devices Group, Inc.||Implantable hearing aid and method of improving hearing|
|US4774933 *||17 Nov 1987||4 Oct 1988||Xomed, Inc.||Method and apparatus for implanting hearing device|
|US4776322 *||18 Aug 1986||11 Oct 1988||Xomed, Inc.||Implantable electromagnetic middle-ear bone-conduction hearing aid device|
|US4800884 *||7 Mar 1986||31 Jan 1989||Richards Medical Company||Magnetic induction hearing aid|
|US4817607 *||15 May 1987||4 Apr 1989||Richards Medical Company||Magnetic ossicular replacement prosthesis|
|US4840178 *||15 May 1987||20 Jun 1989||Richards Metal Company||Magnet for installation in the middle ear|
|US4850962 *||8 Mar 1988||25 Jul 1989||Medical Devices Group, Inc.||Implantable hearing aid and method of improving hearing|
|US4936305 *||20 Jul 1988||26 Jun 1990||Richards Medical Company||Shielded magnetic assembly for use with a hearing aid|
|US5015225 *||17 Mar 1988||14 May 1991||Xomed, Inc.||Implantable electromagnetic middle-ear bone-conduction hearing aid device|
|US5085628 *||12 Oct 1989||4 Feb 1992||Storz Instrument Company||Implantable hearing aid coupler device|
|US5220918 *||15 May 1991||22 Jun 1993||Smith & Nephew Richards, Inc.||Trans-tympanic connector for magnetic induction hearing aid|
|US5239588 *||18 Dec 1989||24 Aug 1993||Davis Murray A||Hearing aid|
|US5277694 *||13 Feb 1992||11 Jan 1994||Implex Gmbh||Electromechanical transducer for implantable hearing aids|
|US5390254 *||19 Apr 1993||14 Feb 1995||Adelman; Roger A.||Hearing apparatus|
|US5456654 *||1 Jul 1993||10 Oct 1995||Ball; Geoffrey R.||Implantable magnetic hearing aid transducer|
|US5554096 *||8 Apr 1994||10 Sep 1996||Symphonix||Implantable electromagnetic hearing transducer|
|US5558618 *||23 Jan 1995||24 Sep 1996||Maniglia; Anthony J.||Semi-implantable middle ear hearing device|
|US5562670 *||26 Apr 1994||8 Oct 1996||Medevelop Ab||Holding means and method of implantation thereof in osseous tissue|
|US5624376 *||3 Jan 1995||29 Apr 1997||Symphonix Devices, Inc.||Implantable and external hearing systems having a floating mass transducer|
|US5772575 *||22 Sep 1995||30 Jun 1998||S. George Lesinski||Implantable hearing aid|
|US5800336 *||3 Jan 1996||1 Sep 1998||Symphonix Devices, Inc.||Advanced designs of floating mass transducers|
|US5857958 *||23 Dec 1996||12 Jan 1999||Symphonix Devices, Inc.||Implantable and external hearing systems having a floating mass transducer|
|US5881158 *||23 May 1997||9 Mar 1999||United States Surgical Corporation||Microphones for an implantable hearing aid|
|US5897486 *||11 Mar 1997||27 Apr 1999||Symphonix Devices, Inc.||Dual coil floating mass transducers|
|US5906635 *||18 Aug 1997||25 May 1999||Maniglia; Anthony J.||Electromagnetic implantable hearing device for improvement of partial and total sensoryneural hearing loss|
|US5913815 *||6 Dec 1995||22 Jun 1999||Symphonix Devices, Inc.||Bone conducting floating mass transducers|
|US5951601 *||24 Mar 1997||14 Sep 1999||Lesinski; S. George||Attaching an implantable hearing aid microactuator|
|US5977689 *||18 Jul 1997||2 Nov 1999||Neukermans; Armand P.||Biocompatible, implantable hearing aid microactuator|
|US5984859 *||25 Apr 1996||16 Nov 1999||Lesinski; S. George||Implantable auditory system components and system|
|US5993376 *||7 Aug 1997||30 Nov 1999||St. Croix Medical, Inc.||Electromagnetic input transducers for middle ear sensing|
|US6001129 *||7 Aug 1997||14 Dec 1999||St. Croix Medical, Inc.||Hearing aid transducer support|
|US6041129 *||18 Jan 1996||21 Mar 2000||Adelman; Roger A.||Hearing apparatus|
|US6113531 *||18 Nov 1998||5 Sep 2000||Implex Aktiengesellschaft Hearing Technology||Process for optimization of mechanical inner ear stimulation in partially or fully implantable hearing systems|
|US6123660 *||14 May 1999||26 Sep 2000||Implex Aktiengesellschaft Hearing Technology||Partially or fully implantable hearing aid|
|US6137889 *||27 May 1998||24 Oct 2000||Insonus Medical, Inc.||Direct tympanic membrane excitation via vibrationally conductive assembly|
|US6139488 *||1 Sep 1998||31 Oct 2000||Symphonix Devices, Inc.||Biasing device for implantable hearing devices|
|US6153966 *||27 Sep 1999||28 Nov 2000||Neukermans; Armand P.||Biocompatible, implantable hearing aid microactuator|
|US6162169 *||25 Mar 1999||19 Dec 2000||Implex Aktiengesellschaft Hearing Technology||Transducer arrangement for partially or fully implantable hearing aids|
|US6277148||11 Feb 1999||21 Aug 2001||Soundtec, Inc.||Middle ear magnet implant, attachment device and method, and test instrument and method|
|US6315710||21 Jul 1997||13 Nov 2001||St. Croix Medical, Inc.||Hearing system with middle ear transducer mount|
|US6398717||22 May 2000||4 Jun 2002||Phonak Ag||Device for mechanical coupling of an electromechanical hearing aid converter which can be implanted in a mastoid cavity|
|US6436028||28 Dec 1999||20 Aug 2002||Soundtec, Inc.||Direct drive movement of body constituent|
|US6475134||14 Jan 1999||5 Nov 2002||Symphonix Devices, Inc.||Dual coil floating mass transducers|
|US6482144||6 Oct 2000||19 Nov 2002||Phonak Ag||Arrangement for mechanical coupling of a driver to a coupling site of the ossicular chain|
|US6488616||18 Apr 2000||3 Dec 2002||St. Croix Medical, Inc.||Hearing aid transducer support|
|US6516228 *||7 Feb 2000||4 Feb 2003||Epic Biosonics Inc.||Implantable microphone for use with a hearing aid or cochlear prosthesis|
|US6537199||26 Jul 2000||25 Mar 2003||Phonak Ag||Arrangement for mechanical coupling of a driver to a coupling site of the ossicular chain|
|US6540661||6 Oct 2000||1 Apr 2003||Phonak Ag||Arrangement for coupling of a driver to a coupling site of the ossicular chain|
|US6540662||5 Jul 2001||1 Apr 2003||St. Croix Medical, Inc.||Method and apparatus for reduced feedback in implantable hearing assistance systems|
|US6547715||10 Jul 2000||15 Apr 2003||Phonak Ag||Arrangement for mechanical coupling of a driver to a coupling site of the ossicular chain|
|US6554762||27 Aug 2001||29 Apr 2003||Cochlear Limited||Implantable hearing system with means for measuring its coupling quality|
|US6592512||13 Aug 2001||15 Jul 2003||Phonak Ag||At least partially implantable system for rehabilitation of a hearing disorder|
|US6676592||1 Nov 2002||13 Jan 2004||Symphonix Devices, Inc.||Dual coil floating mass transducers|
|US6689045||12 Dec 2001||10 Feb 2004||St. Croix Medical, Inc.||Method and apparatus for improving signal quality in implantable hearing systems|
|US6730015||1 Jun 2001||4 May 2004||Mike Schugt||Flexible transducer supports|
|US6755778||18 Oct 2002||29 Jun 2004||St. Croix Medical, Inc.||Method and apparatus for reduced feedback in implantable hearing assistance systems|
|US6840919||17 Dec 1998||11 Jan 2005||Osseofon Ab||Percutaneous bone anchored transferring device|
|US6914994||7 Sep 2001||5 Jul 2005||Insound Medical, Inc.||Canal hearing device with transparent mode|
|US6940988||25 Nov 1998||6 Sep 2005||Insound Medical, Inc.||Semi-permanent canal hearing device|
|US6940989||30 Dec 1999||6 Sep 2005||Insound Medical, Inc.||Direct tympanic drive via a floating filament assembly|
|US7016504||21 Sep 1999||21 Mar 2006||Insonus Medical, Inc.||Personal hearing evaluator|
|US7226406||27 Aug 2001||5 Jun 2007||Cochlear Limited||At least partially implantable hearing system|
|US7379555||26 Jan 2005||27 May 2008||Insound Medical, Inc.||Precision micro-hole for extended life batteries|
|US7424124||26 Apr 2005||9 Sep 2008||Insound Medical, Inc.||Semi-permanent canal hearing device|
|US7481761||14 Jan 2004||27 Jan 2009||Med-El Elektromedizinische Geräte Ges.m.b.H.||Implantable converter for cochlea implants and implantable hearing aids|
|US7651460 *||26 Jan 2010||The Board Of Regents Of The University Of Oklahoma||Totally implantable hearing system|
|US7664282||27 Sep 2005||16 Feb 2010||Insound Medical, Inc.||Sealing retainer for extended wear hearing devices|
|US7876919||25 Jan 2011||Insound Medical, Inc.||Hearing aid microphone protective barrier|
|US8068630||26 Nov 2007||29 Nov 2011||Insound Medical, Inc.||Precision micro-hole for extended life batteries|
|US8075630 *||13 Dec 2011||Bio-Lok International, Inc.||Transcutaneous port having micro-textured surfaces for tissue and bone integration|
|US8105229||9 Apr 2007||31 Jan 2012||Cochlear Limited||At least partially implantable hearing system|
|US8147544||26 Oct 2002||3 Apr 2012||Otokinetics Inc.||Therapeutic appliance for cochlea|
|US8184840 *||22 Aug 2006||22 May 2012||3Win N.V.||Combined set comprising a vibrator actuator and an implantable device|
|US8457336||4 Jun 2013||Insound Medical, Inc.||Contamination resistant ports for hearing devices|
|US8494200||15 Dec 2010||23 Jul 2013||Insound Medical, Inc.||Hearing aid microphone protective barrier|
|US8503707||23 Dec 2009||6 Aug 2013||Insound Medical, Inc.||Sealing retainer for extended wear hearing devices|
|US8538055||15 Feb 2008||17 Sep 2013||Insound Medical, Inc.||Semi-permanent canal hearing device and insertion method|
|US8666101||16 Nov 2011||4 Mar 2014||Insound Medical, Inc.||Precision micro-hole for extended life batteries|
|US8682016||23 Nov 2011||25 Mar 2014||Insound Medical, Inc.||Canal hearing devices and batteries for use with same|
|US8715154 *||24 Jun 2010||6 May 2014||Earlens Corporation||Optically coupled cochlear actuator systems and methods|
|US8761423||23 Nov 2011||24 Jun 2014||Insound Medical, Inc.||Canal hearing devices and batteries for use with same|
|US8808906||23 Nov 2011||19 Aug 2014||Insound Medical, Inc.||Canal hearing devices and batteries for use with same|
|US8876689||2 Apr 2012||4 Nov 2014||Otokinetics Inc.||Hearing aid microactuator|
|US9060234||21 May 2014||16 Jun 2015||Insound Medical, Inc.||Canal hearing devices and batteries for use with same|
|US9071914||13 Aug 2008||30 Jun 2015||Insound Medical, Inc.||Combined microphone and receiver assembly for extended wear canal hearing devices|
|US9113277 *||10 Dec 2009||18 Aug 2015||Vibrant Med-El Hearing Technology Gmbh||Skull vibrational unit|
|US9277335||10 Jun 2014||1 Mar 2016||Earlens Corporation||Eardrum implantable devices for hearing systems and methods|
|US20050113633 *||14 Jan 2004||26 May 2005||Med-El Elektromedizinische Gerate Ges.M.B.H.||Implantable converter for cochlea implants and implantable hearing aids|
|US20050199647 *||28 Jan 2005||15 Sep 2005||Akio Muto||Automatic feeding device for syringes and saline water cartridge of radiopharmaceuticals dispensing and injection system|
|US20050203557 *||26 Oct 2002||15 Sep 2005||Lesinski S. G.||Implantation method for a hearing aid microactuator implanted into the cochlea|
|US20050259840 *||26 Jan 2005||24 Nov 2005||Insound Medical, Inc.||Precision micro-hole for extended life batteries|
|US20050261544 *||18 Mar 2005||24 Nov 2005||Gan Rong Z||Totally implantable hearing system|
|US20050267591 *||12 May 2005||1 Dec 2005||Ricci John L||Transcutaneous port having micro-textured surfaces for tissue and bone integration|
|US20060002574 *||1 Jul 2005||5 Jan 2006||Insound Medical, Inc.||Canal hearing device with transparent mode|
|US20060050914 *||27 Sep 2005||9 Mar 2006||Insound Medical, Inc.||Sealing retainer for extended wear hearing devices|
|US20060210090 *||16 Mar 2006||21 Sep 2006||Insound Medical, Inc.||Personal hearing evaluator|
|US20070003087 *||29 Jun 2006||4 Jan 2007||Insound Medical, Inc.||Hearing aid microphone protective barrier|
|US20070249890 *||9 Apr 2007||25 Oct 2007||Cochlear Limited||At least partially implantable hearing system|
|US20080137892 *||15 Feb 2008||12 Jun 2008||Insound Medical, Inc.||Semi-permanent canal hearing device and insertion method|
|US20090074220 *||13 Aug 2008||19 Mar 2009||Insound Medical, Inc.||Combined microphone and receiver assembly for extended wear canal hearing devices|
|US20090141919 *||22 Aug 2006||4 Jun 2009||3Win N.V.||Combined set comprising a vibrator actuator and an implantable device|
|US20090253951 *||18 Jun 2009||8 Oct 2009||Vibrant Med-El Hearing Technology Gmbh||Bone conducting floating mass transducers|
|US20100098281 *||23 Dec 2009||22 Apr 2010||Insound Medical, Inc.||Sealing retainer for extended wear hearing devices|
|US20100145135 *||10 Dec 2009||10 Jun 2010||Vibrant Med-El Hearing Technology Gmbh||Skull Vibrational Unit|
|US20100322452 *||18 Jun 2010||23 Dec 2010||Insound Medical, Inc.||Contamination resistant ports for hearing devices|
|US20110082327 *||7 Apr 2011||Manning Miles Goldsmith||Saline membranous coupling mechanism for electromagnetic and piezoelectric round window direct drive systems for hearing amplification|
|US20110085688 *||15 Dec 2010||14 Apr 2011||Insound Medical, Inc.||Hearing aid microphone protective barrier|
|US20110144414 *||1 Oct 2010||16 Jun 2011||Ototronix, Llc||Middle ear implant and method|
|US20110152603 *||23 Jun 2011||SoundBeam LLC||Optically Coupled Cochlear Actuator Systems and Methods|
|USRE32947 *||14 Jan 1988||13 Jun 1989||Baptist Medical Center Of Oklahoma, Inc.||Magnetic transcutaneous mount for external device of an associated implant|
|DE3617118A1 *||22 May 1986||5 Feb 1987||Bristol Myers Co||Implantierbare elektromagnetische mittelohrhoerhilfe|
|DE19840212C2 *||3 Sep 1998||2 Aug 2001||Implex Hear Tech Ag||Wandleranordnung für teil- oder vollimplantierbare Hörgeräte|
|EP0263254A1 *||30 Jul 1987||13 Apr 1988||Medical Devices Group, Inc.||Implantable hearing aid|
|EP0622057A2 *||26 Apr 1994||2 Nov 1994||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|
|EP1179969A2||25 Jul 2001||13 Feb 2002||Phonak Ag||At least partially implantable hearing system|
|EP2484126A1 *||1 Oct 2010||8 Aug 2012||Ototronix LLC||Improved middle ear implant and method|
|WO1995001710A1 *||27 Jun 1994||12 Jan 1995||Ball Geoffrey R||Implantable magnetic hearing aid transducer|
|WO1996021335A1||3 Jan 1996||11 Jul 1996||Symphonix Devices, Inc.||Implantable and external hearing systems having a floating mass transducer|
|WO1996022727A1 *||26 Jan 1996||1 Aug 1996||Pierre Sabin||Transcutaneous electrical connection device for medical implant apparatus|
|WO1998041056A1 *||9 Mar 1998||17 Sep 1998||Symphonix Devices, Inc.||Improved dual coil floating mass transducers|
|WO1999007436A1 *||7 Aug 1998||18 Feb 1999||St. Croix Medical, Inc.||Electromagnetic input transducers for middle ear sensing|
|WO2001050815A1||28 Dec 2000||12 Jul 2001||Insonus Medical, Inc.||Direct tympanic drive via a floating filament assembly|
|WO2002098506A1 *||1 Jun 2001||12 Dec 2002||St. Croix Medical, Inc.||Flexible transducer suports|
|WO2011066295A1||23 Nov 2010||3 Jun 2011||Med-El Elektromedizinische Geraete Gmbh||Implantable microphone for hearing systems|
|WO2011066306A1||23 Nov 2010||3 Jun 2011||Med-El Elektromedizinische Geraete Gmbh||Implantable microphone for hearing systems|
|U.S. Classification||600/25, 381/326|
|International Classification||A61B5/07, A61F11/04, A61F2/18, H04R25/00|
|Cooperative Classification||H04R2225/67, A61F2002/183, H04R25/606, A61B5/076|
|European Classification||H04R25/60D1, A61B5/07D|