AU593251B2 - Creación de Inventos y Patentes con Inteligencia Artificial

AU593251B2 – Direct bone conduction hearing aid device
– Google Patents

AU593251B2 – Direct bone conduction hearing aid device
– Google Patents
Direct bone conduction hearing aid device

Download PDF
Info

Publication number
AU593251B2

AU593251B2
AU57803/86A
AU5780386A
AU593251B2
AU 593251 B2
AU593251 B2
AU 593251B2
AU 57803/86 A
AU57803/86 A
AU 57803/86A
AU 5780386 A
AU5780386 A
AU 5780386A
AU 593251 B2
AU593251 B2
AU 593251B2
Authority
AU
Australia
Prior art keywords
hearing aid
skull
aid device
bone
sound
Prior art date
1985-05-23
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.)

Ceased

Application number
AU57803/86A
Other versions

AU5780386A
(en

Inventor
Kenneth Everett Barton Jr.
Robert Yuk Chow
Paul Dicarlo
Jack Van Doren Hough
Gordon Leroy Richard
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)

Xomed Treace Inc

Original Assignee
Bristol Myers Co
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
1985-05-23
Filing date
1986-05-22
Publication date
1990-02-08

1986-05-22
Application filed by Bristol Myers Co
filed
Critical
Bristol Myers Co

1986-11-27
Publication of AU5780386A
publication
Critical
patent/AU5780386A/en

1990-02-08
Application granted
granted
Critical

1990-02-08
Publication of AU593251B2
publication
Critical
patent/AU593251B2/en

1995-05-25
Assigned to XOMED-TREACE, INC.
reassignment
XOMED-TREACE, INC.
Alteration of Name(s) in Register under S187
Assignors: BRISTOL-MYERS COMPANY

2006-05-22
Anticipated expiration
legal-status
Critical

Status
Ceased
legal-status
Critical
Current

Links

Espacenet

Global Dossier

Discuss

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

H—ELECTRICITY

H04—ELECTRIC COMMUNICATION TECHNIQUE

H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS

H04R2460/00—Details of hearing devices, i.e. of ear- or headphones covered by H04R1/10 or H04R5/033 but not provided for in any of their subgroups, or of hearing aids covered by H04R25/00 but not provided for in any of its subgroups

H04R2460/13—Hearing devices using bone conduction transducers

Description

is, Form COMMONWEAL7H O’F AUSTRALIA PATENTS A’UT 1952-69 COMPLETE SPECIFICATION
‘ORIGINA.L)
Application Number: Lodged-, Class 4 Int. Class Complete Specif ication Lodged; lpricrjrty: ‘-Pelated Art: Accepted: Published:, This doc~ument contains the’~ amendments made tinderI Section 49 and is correct far printing, ‘Nam of Applicant; SAJrios of Applicant:.
*Actual Inventor:, Address for Service,.
BRItSTOL-MYERS COMPANY 345 Park Avenue, New York, New York 10154, United States of America JACK VAN DOREN HOUGH-, GORDON LEROY RICHARD, KENNETH EVERETT BARTON, JR. PAUL DICARLO, and ROBERT YUK CHOW EDWD. WATERS SONS, 50 QUJEEN STREET, MELBOURNE, AUSTRALIA, 3000, ZV I Complete Specif ication for the Invention entitled: DIRECT BONE CONDUCTION, HEARING AID DEVICE The following statement-‘ssa full description ot this Invention, Including the beot method of performing it known to us l -la- DIRECT BONE CONDUCTION HEARING AID DEVICE i Field and Background Of The Invention This invention relates to devices for aiding the hearing impaired and more particularly to such a device which stimulates the inner ear to create the per- 5 ception of sound through conduction of vibrations through the bone structure of the skull.
Background Of The Invention The normal perception of sound occurs when sound waves strike the tympanic membrane and cause it to vibrate. These vibrations are transmitted through the three tiny bones in the middle ear (ossicular chain) to the cochlea in the inner ear, which results in electrical impulses being transmitted through the auditory nerve to the brain. Even if the sound conducting mechanisms of the middle ear are functioning perfectly, a hearing loss can be experienced if the inner Ear is damaged.
A conventional, «air cond-ction» hearing aid can t» t sometimes be used to overcome a hearing loss due to inner Sear damage (sensorineural loss) and/or hearing loss due to a mild impediment of the sound conducting mechanism of the middle ear. A conventional air conduction hearing aid works by simply amplifying the incoming sound and delivering the amplified sound signal by way of a speaker positioned in the ear canal. This amplified sound simply «overdrives» the ear’s sound conducting mechanism.
Since an air conduction hearing aid must have some of its componetry in the ear canal, and since it also requires a fairly normal tympanic membrane and middle ear space, some hearing impaired persons are unable to derive any benefit from a device.
/I
-2- Persons who cannot benefit from an air conduction hearing aid can sometimes benefit from a «bone conduction» hearing aid. A bone conduction hearing aid works by converting t 4 he sound signal into a mechanical vibratory stimulus. Heretofore, the vibrating portion of the aid has been placed against the skin, usually behind the ear, under some pressure. The vibrator transmits its vibrations through the skin and soft tissue into the bone structure of the skull. The vibration of the skull stimulates the cochlea and a sound is perceived. Such bone conduction devices are not very popular due to several Slimitations. First, the devices are bulky and must be Sworn on a head band or a special eyeglass frame in order to keep the vibrator pressed tightly against the skull.
t 15 In addition, because the vibration must be transmitted ‘t through the soft tissue overlying the skull, the fidelity of sound and the efficiency of the device are poor.
Proposals have been made for improving bone conduction devices for stimulating the inner ear. One such proposal is disclosed in United States Patent No.
3,209,081 in which a radio receiver is implanted underneath the skin and includes a vibration generating means which is connected to the temporal bone subcutaneously.
A transmitter may be located at any remote place on the body of the user within the range of the implanted radio receiver for generating a modulated signal in response to sound received by a microphone. This modulated signal is received by the radio receiver and the vibrator is caused to vibrate in response to the modulated signal and set up vibrations within the temporal bone which in turn stimu- 2 lates the inner ear to create a perception of sound.
This implanted radio receiver is quite complex and includes numerous implanted electronic components including a power supply, which are susceptible to malfunction and
(K
-3other potential problems which could cause extreme difficulty due to the implanted nature thereof.
A second proposal relates to some experimental work conducted in Europe and described in a recent published paper wherein a direct bone conduction device was implanted which included a bone screw implanted directly in the temporal bone subcutaneously and a post connected directly thereto. This post extends percutaneously (throuyhI the skin) to a location externally of the skin. A vibrator which creates vibrations in response to a modulated signal is connected to this post and vibrations are transmitted by the post to the bone screw and thence to the temporal bone of the skull to t ,..stimulate the inner ear and create the perception of S 15 sound. This device has distinct disadvantages, not the least of which are the likelihood of infection and the undesirability of a ceramic element extending permanently through the skin from aesthetic, psychological and comfort standpoints.
Objects And Summary Of The Invention With the foregoing in mind, it is an object of J the present invention to provide a direct bone conduction hearing aid device which is very simple and which overcomes the deficiencies and problems heretofore encountered with bone conduction hearing aid devices.
A more specific object of the present invention is to provide a hearing aid device for the hearing impaired in which direct conduction of vibrations into the bone is provided and in which the signal transmitting device is held in place without unsightly or uncomfortable external devices.
These objects are accomplished by the present invention in which a sound processor including a sensitive microphone is located externally of the body of the user to receive sound and a suitable electronic means
I
I
On o 0 is connected to the microphone for converting the sound waves received by the microphone into an electromagnetic field. This electronic means includes an output transmitter adapted to be positioned against the skin over a skull bone of the hearing impaired person, preferably over the mastoid area of the temporal bone of the skull behind the ear of the user, for transmitting the electromagnetic field transcutaneously and a first magnetic means, preferably a permanent magnet. Additionally, vibration generating means is adapted to be implanted subcutaneously in the skull bone of the hearing impaired person, preferably in the mastoid area of the temporal bone behind the ear, and includes means for securing the vibration generating means subcutaneously to a skull bone, preferably a bone screw adapted to be implanted directly into the temporal bone behind the ear.
The vibration generating means further includes second magnetic means, preferably a permanent magnet, for cooperating with said first magnetic means to hold the transmitter in position supercutaneously on the skull, for receiving the electromagnetic signal from the tranismitter of the sound processing means, and for vibrating the skull bone in response to the electromagnetic signal. Such vibrations are then conducted through the bones of the skull and thereby to the cochlea to stimulate the inner ear to create the perception of sound.
Brief DescriptiLon Of The Drawings Some of the features and advantages of the invention having been briefly stated, others will appear from the detailed description which follows, when taken in connection with the accompanying drawings, in which Figure 1 is a perspective view illustrating the manner of use of the direct bone conduction hearing aid device of the present invention;
I-.
r 7r
I
Figure 2 is an enlarged perspective view of the vibration generating means of the hearing aid device of the present invention; Figure 3 is a prospective view of the vibration generating means shown in Figure 2 looking upwardly from Ithe bottom thereof; Figure 4 is a transverse sectional view taken substantially along line 4-4 in Figure 2; Figure 5 is a fragmentary elevationu view illustrating the manner of implantation of the vibration generating means shown in Figures 2 and 3; rt,°.Figure 6 is an enlarged fragmentary sectional view illustrating the implanted vibration generating orc means and associated output transmitter which causes ,t 15 vibration in the vibration generating means; f» Figure 7 is a perspective view of a sound pro- Scessor forming a part of the hearing aid device of the present invention; Figure 8 is a schematic circuit diagram of the sound processor illustrated in Figure 7; and Figures 9-12 are enlarged fragmentary sectional views illustrating alternative embodiments of the implanted vibration generating means.
Detailed Description Of The Illustrated Embodiments Referring now .rore specifically to the drawings, the direct bone conduction hearing aid device of the pre- ,sent invention is generally indicated at 10 in Figure 1 t Qr with a preferred embodiment being illustrated in Figures 2-8 and alternative embodiments being illustrated in Figures 9-12.
The hearing aid device 10 comprises a sound processing means 11 (Figure 7) and vibration generating means 12. The sound processing means 11 is illustrated as being confined in a case ila and including a oair of output transmitters 13 connected to the case Ila by
I
-6suitable wiring 14. Whether one or two output transmitters 13 are used will depend upon whether the hearing aid device 10 is to be utilized in connection with one or both ears of a hearing impaired person. Also, the case lla could be formed in different configurations and could be located behind the ear or in glasses, etc. of the user. The sound processing means 11 includes electronic circuitry as illustrated by way of example in Figure 8.
As shown in Figure 8, the electronic sound processing circuitry includes a sensitive microphone 15 for converting sound waves into electrical signals that are processed and passed to output transmitter (inductive coil) 13 for generating at the output transmitter 13 an bs0 electromagnetic field having an amplitude proportional to 15 the amplitude of the sound waves received by the microphone Microphone 15 includes a diaphragm or membrane (not shown) which vibrates in response to the sound waves impinging thereon. The electrical signal from the 20 microphone 15 is then amplified by a pre-amplifier This signal is then passed through a low frequency cutoff passive filter 30. The amplified and filtered signal is then fed to an output amplifier 40 through a volume control 50 which provides a full or attenuated signal from the pre-amplifier to the amplifier. The output amplifier 40 amplifies the signal and then drives the output transmitter (indictive coil) 13.
A voltage regulation/isolation circuitry 60 minimizes crosstalk through the power supply (not shown) from amplifier to pre-amplifier providing virtually a distor- Stionless power source for both.
A circuit cutoff circuit 70 acts to conserve bat- I tery energy. This circuit cuteff 70 simply removes all power to the outpkt stage extending battery life if the device is on and is not required to function for approxi- -7mately one minute. In the event a sound signal is received by the microphone 15 when the power is removed from the output stage, the power is restored by the circuit cutoff circuit 70 and normal operation is continued.
Specifically, the cutoff circuit 70 operates by generating a series of timed pulses generated by a clock 71 which are counted by a counter 72. The counter is reset when a sound signal is processed, not allowing the counter 72 to reach its full count which takes approxima- 13 tely one minute of no sound processing activity. If the counter 72 is allowed to reach its full count, the output o amplifier 40 will return to its non-energized state.
Output transmitter 13 comprises an induction coil 75 wound about a core 76 which contains a first magnetic C 15 means. This first magnetic means may be of any suitable type, but preferably is a permanent magnet such as a 4,, r osamariam-cobalt type, and is formed in such manner that it may be included in the core 76 about which induction coil 75 is wound.
As stated previously, vibration generating means 12 is adapted to be implanted subcutaneously for receipt of the signal by electromagnetic coupling from output transmitter 13 for causing vibration of the skull.
Vibration generating means 12 includes means for securing the vibration generating means 12 to a skull bone of the hearing impaired person, preferably in the form of a bone screw 80 adapted to be inserted in the mastoid area of the temporal bone behind the ear of a hearing impaired person. Bone screw 80 has its upper end threadably received in a cap 81 to firmly and structurally connect the cap 81 to the bone screw 80. Bone screw 80 and cap 81 are formed of tissue tolerant material, such as titanium.
Cap 81 has a flange 81a extending around the upper periphery thereof and defining an upwardly opening, ip r @4 4 4 9 044 9 *49) to 9* centrally positioned cavity therewithin (Figure The flange 81a also has an outwardly facing groove in the outer side thereof.
A second magnetic means, preferably in the form of a second permanent magnet 82, is mounted within the upwardly opening cavity defined within flange 81a of cap 81 and is of a size so as to snugly fit within the cavity and have its outer periphery closely adjacent or in contact with the flange 81a. Magnet 82 is coated with a biocompatible material, such as paralyene, and preferably is of the samariam-cobalt type. Obviously, any suitable permanent magnet may be used provided that it has the sufficient magnetic field characteristics and long life needed for this application.
15 The second permanent magnet 82 is firmly anchored to cap 81 by an adhesive 83 placed between T’he bottom of the magnet and cap 81. Finally, the outer surface of the magnet 82 and of the flange 81a is covered by a suitable tissue tolerant material 84, such as silicone. It is noted that the silicone 84 is molded in place and includes a portion which is received within the outwardly facing groove in flange 81a to firmly anchor the silicone cover 84 to the cap 81. The cover 84 further protects the magnet 82 and the upper portion of the cap 81 from the surrounding tissue once the vibration generating means 12 is implanted.
Preferably, a pair of concave depressions 85 are formed in diametrically opposed sections of the cover 84 and cap 81 for receipt of a suitable tool to be used to implant the bone screw 80 in the temporal bone.
The procedure to be employed in the implantation of the vibration generating means 12 is illustrated in Figure 5 and constitutes a surgical procedure in which an incision is made in the skin and underlying tissue to expose the mastoid area of the temporal bone behind one -9or both ears. The bone screw 80 is implanted directly in the mastoid area of the temporal bones B by a pilot hole being drilled therein and then the screw 80 is screwed into the bone. Then, the skin S and underlying soft tissue T are replaced over the implanted device and suitably sutured.
As shown in Figure 6, the vibration generating means 12 is implanted in the bone B beneath the tissue T and remains underneath the skin S. When tho hearing aiu device 10 of the present invention is desired to be used, it is only necessary to place the output o a transmitter 13 externally of the skin S in juxtaposed rel» tion to the implanted vibration generating means 12.
The permanent magnets located in the output transmitter o 15 13 and the vibration generating means 12 serve to hold Sthe output transmitter 13 in operative position relative S0* to the implanted vibration generating means 12.
In operation, the sound processor 11 receives sound by way of microphone 15 and such sound is converted 20 into an amplified electrical signal by the pre-amplifier 0 20, amplifier 40 and output transmitter 13. An electromagnetic field is generated by the inductive coil 76 oi tran, itter 13 and transmitted to the implanted vibration 0a« a generation means 12 which causes the second permanent magnet 82 to vibrate in response to the amplitude of the field. Since permanent magnet 82 is firmly anchored to a cap 81, the vibrations generated by magnet 82 are transmitted directly to cap 81 and thence to bone screw The implanted bone screw 80 transmits such vibrations to the temporal bone and such vibrations are conducted by the bone structure of the skull to the cochlea to stimulate the inner ear to create the perception of sound.
Considering variations and alternative embodiments to the preferred form of the direct bone conduction 0 7S 71 a 444 01 4 4* 44 hearing aid device 10 described above.. it is possible that the vibration generating means 12 could be secured subcutaneously to, any of the skull bones on the hearing impaired person for being vibrated to transmit suck.
vibrations through the tones of the skull to stimulate the inner ear to create the preception of sound in the hearing impaired person, although the mastoid area of the temporal bone behind at least one ear of the hearing impaired person is preferred.
Additionally, although the means for securing the vibration generating means 12 to a skull bone of the hearing impaired person is preferably in the form of a bone screw 80, other securement means could be utilized.
As illustrated in Figure 9, this securexnent means is in the z’orm of adhesive 90 for adhesively securing the vibration generating means 12 dietyto a skull bone of the user. As illustrated in Figure 10, the means for securing the vibration generating means 12 to a skull bone of the hearing impaired person is in the form of a, post 92 which is implanted into a cut-ou~t portion of the skull bone of the user and may include a porous coating thereon for allowing the skull bone. to grow into the. post for securing the post therein or b, post 92 may be adhesively secured within such cut-out portion of the skull bone of the user.
As illustrated in Figure 11, the entire vibration generating means 1.2 may be in the form of a bone screw 80′ for being imbedded directly into the skull bone of the user. Alternatively, as illustrated in Figure 1, the entire vibration generating means 12 could be in the form of a. post 92′ which Is imbedded directly into a cutoi,* in the skull bone of the user and may include a, porous coating thereon !~or ingrowth of the skull bone to secure the vibration generating means in the cut-out pottion of the skull bone or may be adhesively secured therein.
r 4’ -CIIIIII~– 119~91~ 11– *0 9 4 4 0 *090 4 1~ 0 94 Lastly, the first and second magnetic means of the output transmitter 13 of the sound processing means 11 and of the vibration generating means 12, respectively, could take various alternative forms. For example, at least one of these first and second magnetic means could comprise a magnet, including a permanent magnet as described above; whereas, the other of the first and second magnetic means could comprise magnetically attractive material, such as ferromagnetic material. Other combinations may be possible so long as the second magnetic means of the vibration generating means 12 cooperates with the first magnetic means of the transmitter 13 to hold the transmitter 13 in position supercutaneously on the skull of the hearing impaired person, receives the electromagnetic signal from the transmitter 13 of the sound processing means 11, and (3) vibrates the skull bones of the hearing impaired person in response to such electromagnetic signal, whereby vibrations are generated subcutaneously in response to the analog electromagnetic signal and conducted through the bones of the skull to stimulate the inner ear to create the preception of sound in the hearing impaired person.
In the drawings and specification there have been disclosed typical preferred embodiments of the invention, an, although specific terms are employed, they are used in a generic and descriptive sense only, and not for the purposes of limitation.

Claims (6)

1. A direct bone conduction hearing aid device comprising sound processing means for converting sound into an analog electromagnetic signal and including an output transmitter for transmitting the electromagnetic signal and being adapted to be placed supercutaneously on the skull of a hearing impaired person and having first magnetic means therein; and vibration generating means adapted to be implanted subcutaneously and comprising means for securing said vibration generating means subcutaneously to a skull bone of the hearing impaired person and second magnetic means for cooperating with said first magnetic means to hold said transmitter in position supercutaneously on the skull of the hearing impaired person, for receiving the electromagnetic signal from said transmitter of said sound processing means, and for vibrating the skull bone in 44 response to such electromagnetic signal whereby, vibrations are generated subcutaneously in response to the analog electremagnetic signal and conducted through the bones of the skull to stimulate the inner ear to create the perception of sound in the hearing impaired person. S 2. A hearing aid device according to claim 1 wherein said vibratign qenerator means comprises a hollow component 4 r 1 11 made of tissue tolerant material within which said second mragnetic means is releasably housed.

3. A hearing aid devi- 4 a according to claim 2, wherein said second magnetic means is adhesively secured within said hollow component.

4. A hearing aid device as claimed in eitnier claim 2 or claim 3 wherein said hollow component is disc shaped and is secured to post means adapted to penetrate into the skull bone whereby the hollow component engages against the skull bone. 000 45. A hear-ing aid device as claimed in claim 4, wherein said post means is externally screw-threaded for screw threaded reception by a recess formed in the skull bone.

6. A hearing aid device as claimed in either claim 2 or claim 3 wherein said hollow component is disc shaped and is 0* adhesivel.y secured to the skull bone. A hearing aid device as claimed in either claim 2 or 410#44: wherein said hollow component is disc shaped and is 9 itself adapted to penetrate into a formed recess in the skull bone.

8. A hearing aid device as claimed in claim 7, wherein the disc shaped hollow component is externally screw-threaded for screw-threaded receptioIL by the formed recess. A L Ll t t *t a a, a. a tt~ a. a ass a a a, a a a at a

14- 9. A hearing aid device according to Claim 1, wherain, zaid output transmitter icludes an induction coil wound around a core, and wherein said .:rst magnetic means is a permanent magnet~ located in the core of said induction coil. DATED this 17th day of October, 1989. BRISTOL-MYERS COMPANY WATERMARK PATENT ATTORNEYS QUEEN STREET MELBOURNE VIC. 3000

AU57803/86A
1985-05-23
1986-05-22
Direct bone conduction hearing aid device

Ceased

AU593251B2
(en)

Applications Claiming Priority (2)

Application Number
Priority Date
Filing Date
Title

US737188

1985-05-23

US06/737,188

US4612915A
(en)

1985-05-23
1985-05-23
Direct bone conduction hearing aid device

Publications (2)

Publication Number
Publication Date

AU5780386A

AU5780386A
(en)

1986-11-27

AU593251B2
true

AU593251B2
(en)

1990-02-08

Family
ID=24962921
Family Applications (1)

Application Number
Title
Priority Date
Filing Date

AU57803/86A
Ceased

AU593251B2
(en)

1985-05-23
1986-05-22
Direct bone conduction hearing aid device

Country Status (14)

Country
Link

US
(1)

US4612915A
(en)

JP
(1)

JPS61273100A
(en)

AU
(1)

AU593251B2
(en)

BE
(1)

BE904809A
(en)

CA
(1)

CA1251274A
(en)

DE
(1)

DE3617089A1
(en)

DK
(1)

DK238086A
(en)

ES
(1)

ES8707067A1
(en)

FR
(1)

FR2582216B1
(en)

GB
(1)

GB2176078B
(en)

IL
(1)

IL78724A
(en)

IT
(1)

IT1189678B
(en)

NL
(1)

NL8601286A
(en)

SE
(1)

SE468374B
(en)

Cited By (1)

* Cited by examiner, † Cited by third party

Publication number
Priority date
Publication date
Assignee
Title

AU614616B2
(en)

1988-05-24
1991-09-05
Steen B. Rasmussen
Earplug for noise protected communication between the user of the earplug and surroundings

Families Citing this family (129)

* Cited by examiner, † Cited by third party

Publication number
Priority date
Publication date
Assignee
Title

US5015225A
(en)

1985-05-22
1991-05-14
Xomed, Inc.
Implantable electromagnetic middle-ear bone-conduction hearing aid device

US4606329A
(en)

1985-05-22
1986-08-19
Xomed, Inc.
Implantable electromagnetic middle-ear bone-conduction hearing aid device

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

NL8602043A
(en)

1986-08-08
1988-03-01
Forelec N V

METHOD FOR PACKING AN IMPLANT, FOR example AN ELECTRONIC CIRCUIT, PACKAGING AND IMPLANT.

US4791673A
(en)

1986-12-04
1988-12-13
Schreiber Simeon B
Bone conduction audio listening device and method

US4774933A
(en)

1987-05-18
1988-10-04
Xomed, Inc.
Method and apparatus for implanting hearing device

US4892108A
(en)

1987-07-23
1990-01-09
The Regents Of The University Of Michigan
Multi-channel extracochlear implant

DE3744745A1
(en)

1987-12-04
1989-06-15
Claus Dr Med Jansen
Electroacoustic transducer

DE8816422U1
(en)

1988-05-06
1989-08-10
Siemens Ag, 1000 Berlin Und 8000 Muenchen, De

CA1331803C
(en)

1988-12-21
1994-08-30
Murray A. Davis
Hearing aid

ATE110252T1
(en)

1989-06-07
1994-09-15
Assistance Publique

TRANSCUTANEOUS CONNECTION DEVICE.

FR2650948A1
(en)

1989-08-17
1991-02-22
Issalene Robert

ASSISTANCE DEVICE FOR HEARING BY BONE CONDUCTION

US5337364A
(en)

1990-11-28
1994-08-09
Canadian Bionic Research Inc.
Communication device for transmitting audio information to a user

DE4104358A1
(en)

1991-02-13
1992-08-20
Implex Gmbh

IMPLANTABLE HOER DEVICE FOR EXCITING THE INNER EAR

US5360388A
(en)

1992-10-09
1994-11-01
The University Of Virginia Patents Foundation
Round window electromagnetic implantable hearing aid

US5624376A
(en)

1993-07-01
1997-04-29
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

US5456654A
(en)

1993-07-01
1995-10-10
Ball; Geoffrey R.
Implantable magnetic hearing aid transducer

US20090253951A1
(en)

1993-07-01
2009-10-08
Vibrant Med-El Hearing Technology Gmbh
Bone conducting floating mass transducers

US6676592B2
(en)

1993-07-01
2004-01-13
Symphonix Devices, Inc.
Dual coil floating mass transducers

US5913815A
(en)

1993-07-01
1999-06-22
Symphonix Devices, Inc.
Bone conducting floating mass transducers

US5800336A
(en)

1993-07-01
1998-09-01
Symphonix Devices, Inc.
Advanced designs of floating mass transducers

US5897486A
(en)

1993-07-01
1999-04-27
Symphonix Devices, Inc.
Dual coil floating mass transducers

US5460593A
(en)

1993-08-25
1995-10-24
Audiodontics, Inc.
Method and apparatus for imparting low amplitude vibrations to bone and similar hard tissue

USD380048S
(en)

1994-04-14
1997-06-17
Jan Hampf
Combined hearing instrument and personal communicator

US5902167A
(en)

1997-09-09
1999-05-11
Sonic Bites, Llc
Sound-transmitting amusement device and method

US6115477A
(en)

1995-01-23
2000-09-05
Sonic Bites, Llc
Denta-mandibular sound-transmitting system

WO1997006651A1
(en)

1995-08-03
1997-02-20
Borowsky Hans Dieter
Hearing aid

US5772575A
(en)

1995-09-22
1998-06-30
S. George Lesinski
Implantable hearing aid

US5757935A
(en)

1996-03-01
1998-05-26
Electronics And Telecommunications Research Institute
Audio listening device for the hearing impaired

EP0891684B1
(en)

1996-03-25
2008-11-12
S. George Lesinski
Attaching of an implantable hearing aid microactuator

DE69733837T2
(en)

1996-05-24
2006-04-27
Lesinski, S. George, Cincinnati

IMPROVED MICROPHONES FOR IMPLANTED HEARING AID

WO1998003134A1
(en)

1996-07-19
1998-01-29
Neukermans Armand P
Biocompatible, implantable hearing aid microactuator

US6010532A
(en)

1996-11-25
2000-01-04
St. Croix Medical, Inc.
Dual path implantable hearing assistance device

US5935166A
(en)

1996-11-25
1999-08-10
St. Croix Medical, Inc.
Implantable hearing assistance device with remote electronics unit

US6277148B1
(en)

1999-02-11
2001-08-21
Soundtec, Inc.
Middle ear magnet implant, attachment device and method, and test instrument and method

DE60044521D1
(en)

1999-02-16
2010-07-22
Yugen Kaisha Gm & M

LANGUAGE CONVERSION DEVICE AND PROCEDURE

GB2360663A
(en)

1999-12-16
2001-09-26
John Nicholas Marshall
Implantable hearing aid

US6436028B1
(en)

1999-12-28
2002-08-20
Soundtec, Inc.
Direct drive movement of body constituent

KR200200211Y1
(en)

2000-05-17
2000-10-16
전창
Portable bone conduction hearing aid

US6517476B1
(en)

2000-05-30
2003-02-11
Otologics Llc
Connector for implantable hearing aid

SE523123C2
(en)

2000-06-02
2004-03-30
P & B Res Ab

Hearing aid that works with the principle of bone conduction

DE10047388C1
(en)

2000-09-25
2002-01-10
Implex Hear Tech Ag
Implantable hearing system, includes a detachable coupling for securing and locating a transducer and a micro-manipulator

US20030095677A1
(en)

2000-11-22
2003-05-22
Takeshi Takeda
Aural aid

US6643378B2
(en)

2001-03-02
2003-11-04
Daniel R. Schumaier
Bone conduction hearing aid

SE523124C2
(en)

2001-06-21
2004-03-30
P & B Res Ab

Coupling device for a two-piece leg anchored hearing aid

US6702847B2
(en)

2001-06-29
2004-03-09
Scimed Life Systems, Inc.
Endoluminal device with indicator member for remote detection of endoleaks and/or changes in device morphology

WO2003037212A2
(en)

2001-10-30
2003-05-08
Lesinski George S
Implantation method for a hearing aid microactuator implanted into the cochlea

AU2003238608B9
(en)

2002-06-03
2008-07-31
Med-El Elektromedizinische Geraete Gmbh
Implantable device with flexible interconnect to coil

US7974700B1
(en)

2002-08-09
2011-07-05
Cochlear Limited
Cochlear implant component having a unitary faceplate

AU2002950755A0
(en)

2002-08-09
2002-09-12
Cochlear Limited
Fixation system for a cochlear implant

AU2002950754A0
(en)

2002-08-09
2002-09-12
Cochlear Limited
Mechanical design for a cochlear implant

US7033313B2
(en)

2002-12-11
2006-04-25
No. 182 Corporate Ventures Ltd.
Surgically implantable hearing aid

JP4587195B2
(en)

2003-03-19
2010-11-24
奈良県

hearing aid

AU2003901867A0
(en)

2003-04-17
2003-05-08
Cochlear Limited
Osseointegration fixation system for an implant

SE526548C2
(en)

2003-05-30
2005-10-04
Entific Medical Systems Ab

Device for implants

US7087081B2
(en)

2003-09-19
2006-08-08
Clarity Corporation
Stapedial prosthesis and method of implanting the same

US20050091060A1
(en)

2003-10-23
2005-04-28
Wing Thomas W.
Hearing aid for increasing voice recognition through voice frequency downshift and/or voice substitution

US7651460B2
(en)

2004-03-22
2010-01-26
The Board Of Regents Of The University Of Oklahoma
Totally implantable hearing system

US7302071B2
(en)

2004-09-15
2007-11-27
Schumaier Daniel R
Bone conduction hearing assistance device

US20070053536A1
(en)

2005-08-24
2007-03-08
Patrik Westerkull
Hearing aid system

US7796771B2
(en)

2005-09-28
2010-09-14
Roberta A. Calhoun
Bone conduction hearing aid fastening device

WO2007053882A1
(en)

2005-11-10
2007-05-18
Cochlear Limited
Arrangement for the fixation of an implantable medical device

US7670278B2
(en)

2006-01-02
2010-03-02
Oticon A/S
Hearing aid system

US8246532B2
(en)

2006-02-14
2012-08-21
Vibrant Med-El Hearing Technology Gmbh
Bone conductive devices for improving hearing

US7844070B2
(en)

2006-05-30
2010-11-30
Sonitus Medical, Inc.
Methods and apparatus for processing audio signals

US8291912B2
(en)

2006-08-22
2012-10-23
Sonitus Medical, Inc.
Systems for manufacturing oral-based hearing aid appliances

US8512264B1
(en)

2007-04-06
2013-08-20
Wilson T. Asfora
Analgesic implant device and system

US8469908B2
(en)

2007-04-06
2013-06-25
Wilson T. Asfora
Analgesic implant device and system

US8189838B1
(en)

2007-04-13
2012-05-29
Rich Donna L
Oral hearing aid device and method of use thereof

SE0701242L
(en)

2007-05-24
2008-12-02
Cochlear Ltd

Vibrator

SE531177C2
(en)

2007-05-24
2009-01-13
Cochlear Ltd

Distance for implants

US8270638B2
(en)

2007-05-29
2012-09-18
Sonitus Medical, Inc.
Systems and methods to provide communication, positioning and monitoring of user status

US8433080B2
(en)

2007-08-22
2013-04-30
Sonitus Medical, Inc.
Bone conduction hearing device with open-ear microphone

US8224013B2
(en)

2007-08-27
2012-07-17
Sonitus Medical, Inc.
Headset systems and methods

US7682303B2
(en)

2007-10-02
2010-03-23
Sonitus Medical, Inc.
Methods and apparatus for transmitting vibrations

US8795172B2
(en)

2007-12-07
2014-08-05
Sonitus Medical, Inc.
Systems and methods to provide two-way communications

US7822479B2
(en)

2008-01-18
2010-10-26
Otologics, Llc
Connector for implantable hearing aid

US7974845B2
(en)

2008-02-15
2011-07-05
Sonitus Medical, Inc.
Stuttering treatment methods and apparatus

US8270637B2
(en)

2008-02-15
2012-09-18
Sonitus Medical, Inc.
Headset systems and methods

SE533430C2
(en)

2008-02-20
2010-09-28
Osseofon Ab

Implantable vibrator

US8023676B2
(en)

2008-03-03
2011-09-20
Sonitus Medical, Inc.
Systems and methods to provide communication and monitoring of user status

US8150075B2
(en)

2008-03-04
2012-04-03
Sonitus Medical, Inc.
Dental bone conduction hearing appliance

US20090226020A1
(en)

2008-03-04
2009-09-10
Sonitus Medical, Inc.
Dental bone conduction hearing appliance

US8852251B2
(en)

2008-03-31
2014-10-07
Cochlear Limited
Mechanical fixation system for a prosthetic device

US20090287038A1
(en)

2008-03-31
2009-11-19
Cochlear Limited
Implanted-transducer bone conduction device

US8737649B2
(en)

2008-03-31
2014-05-27
Cochlear Limited
Bone conduction device with a user interface

US8542857B2
(en)

2008-03-31
2013-09-24
Cochlear Limited
Bone conduction device with a movement sensor

AU2009324613B2
(en)

2008-12-10
2014-03-13
Med-El Elektromedizinische Geraete Gmbh
Skull vibrational unit

DE102009014770A1
(en)

2009-03-25
2010-09-30
Cochlear Ltd., Lane Cove

vibrator

USRE48797E1
(en)

2009-03-25
2021-10-26
Cochlear Limited
Bone conduction device having a multilayer piezoelectric element

DE102009014772A1
(en)

2009-03-25
2010-09-30
Cochlear Ltd., Lane Cove

hearing aid

EP2484125B1
(en)

2009-10-02
2015-03-11
Sonitus Medical, Inc.
Intraoral appliance for sound transmission via bone conduction

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

US8908891B2
(en)

2011-03-09
2014-12-09
Audiodontics, Llc
Hearing aid apparatus and method

US10039672B2
(en)

2011-03-23
2018-08-07
Ali Mohammad Aghamohammadi
Vibro-electro tactile ultrasound hearing device

US9107013B2
(en)

2011-04-01
2015-08-11
Cochlear Limited
Hearing prosthesis with a piezoelectric actuator

US10419861B2
(en)

2011-05-24
2019-09-17
Cochlear Limited
Convertibility of a bone conduction device

US9319810B2
(en)

2011-12-07
2016-04-19
Cochlear Limited
Implantable component of a hearing prosthesis

US9526810B2
(en)

2011-12-09
2016-12-27
Sophono, Inc.
Systems, devices, components and methods for improved acoustic coupling between a bone conduction hearing device and a patient’s head or skull

US9031274B2
(en)

2012-09-06
2015-05-12
Sophono, Inc.
Adhesive bone conduction hearing device

US9210521B2
(en)

2012-07-16
2015-12-08
Sophono, Inc.
Abutment attachment systems, mechanisms, devices, components and methods for bone conduction hearing aids

US9258656B2
(en)

2011-12-09
2016-02-09
Sophono, Inc.
Sound acquisition and analysis systems, devices and components for magnetic hearing aids

US9736601B2
(en)

2012-07-16
2017-08-15
Sophono, Inc.
Adjustable magnetic systems, devices, components and methods for bone conduction hearing aids

US9022917B2
(en)

2012-07-16
2015-05-05
Sophono, Inc.
Magnetic spacer systems, devices, components and methods for bone conduction hearing aids

US9119010B2
(en)

2011-12-09
2015-08-25
Sophono, Inc.
Implantable sound transmission device for magnetic hearing aid, and corresponding systems, devices and components

US9179228B2
(en)

2011-12-09
2015-11-03
Sophono, Inc.
Systems devices, components and methods for providing acoustic isolation between microphones and transducers in bone conduction magnetic hearing aids

US8891795B2
(en)

2012-01-31
2014-11-18
Cochlear Limited
Transcutaneous bone conduction device vibrator having movable magnetic mass

US9049527B2
(en)

2012-08-28
2015-06-02
Cochlear Limited
Removable attachment of a passive transcutaneous bone conduction device with limited skin deformation

US9516434B2
(en)

2013-05-09
2016-12-06
Cochlear Limited
Medical device coupling arrangement

US9998837B2
(en)

2014-04-29
2018-06-12
Cochlear Limited
Percutaneous vibration conductor

WO2015183725A1
(en)

2014-05-27
2015-12-03
Sophono, Inc.
Systems, devices, components and methods for reducing feedback between microphones and baseplates in bone conduction magnetic hearing devices

CN107427361B
(en)

2014-08-28
2021-05-07
科利耳有限公司
Bone fixation device for a medical prosthesis

WO2016130095A1
(en)

2015-02-12
2016-08-18
Mikro Protez Sanayi Ve Ticaret Ltd. Sti.
Wireless implantable bone conduction energy harvesting hearing aid device

AU2016233286C1
(en)

2015-03-18
2019-03-14
Med-El Elektromedizinische Geraete Gmbh
Fixation of a bone conduction floating mass transducer

GB201509283D0
(en)

2015-05-29
2015-07-15
Sonic Hearing Ltd
Hearing aid

US10321247B2
(en)

2015-11-27
2019-06-11
Cochlear Limited
External component with inductance and mechanical vibratory functionality

US10009698B2
(en)

2015-12-16
2018-06-26
Cochlear Limited
Bone conduction device having magnets integrated with housing

WO2017105511A1
(en)

2015-12-18
2017-06-22
Advanced Bionics Ag
Cochlear implants having mri-compatible magnet apparatus

US10207123B2
(en)

2016-08-30
2019-02-19
National Guard Health Affairs
Skull implanted magnet assembly for brain stimulation

WO2018190813A1
(en)

2017-04-11
2018-10-18
Advanced Bionics Ag
Cochlear implants with retrofit magnets

US11364384B2
(en)

2017-04-25
2022-06-21
Advanced Bionics Ag
Cochlear implants having impact resistant MRI-compatible magnet apparatus

EP3630265A1
(en)

2017-05-22
2020-04-08
Advanced Bionics AG
Methods and apparatus for use with cochlear implants having magnet apparatus with magnetic material particles

CN111344041A
(en)

2017-10-26
2020-06-26
领先仿生公司
Headgear and implantable cochlear stimulation system including the same

EP4008397B1
(en)

2018-02-15
2023-09-13
Advanced Bionics AG
Headpieces and implantable cochlear stimulation systems including the same

CN114866930A
(en)

2018-06-15
2022-08-05
深圳市韶音科技有限公司
Bone conduction loudspeaker

US10492011B1
(en)

2019-02-19
2019-11-26
Joel E. Haynes
Non-surgical bone conduction hearing aid

CN116112843B
(en)

2023-04-13
2023-06-16
深圳市鑫正宇科技有限公司
Bone conduction earphone extension audio amplifier

Citations (3)

* Cited by examiner, † Cited by third party

Publication number
Priority date
Publication date
Assignee
Title

GB553955A
(en)

1941-10-28
1943-06-11

Rudolf Goldschmidt

Improvements in or relating to electro-magnetic sound-transmission apparatus

AU2438145A
(en)

1945-10-30
1948-08-19

An improved hearing appliance for deaf persons

US4352960A
(en)

1980-09-30
1982-10-05

Baptist Medical Center Of Oklahoma, Inc.

Magnetic transcutaneous mount for external device of an associated implant

Family Cites Families (10)

* Cited by examiner, † Cited by third party

Publication number
Priority date
Publication date
Assignee
Title

US2832892A
(en)

1954-12-24
1958-04-29
Du Mont Allen B Lab Inc
Tuning device for ultra-high frequency circuits

US3209081A
(en)

1961-10-02
1965-09-28
Behrman A Ducote
Subcutaneously implanted electronic device

US3594514A
(en)

1970-01-02
1971-07-20
Medtronic Inc
Hearing aid with piezoelectric ceramic element

DE2044870C3
(en)

1970-09-10
1978-12-21
Dietrich Prof. Dr.Med. 7400 Tuebingen Plester

Hearing aid arrangement for the inductive transmission of acoustic signals

GB1440724A
(en)

1972-07-18
1976-06-23
Fredrickson J M
Implantable electromagnetic hearing aid

BE833809A
(en)

1975-09-25
1976-03-25

HEARING AID AND PROCESS FOR EXAMINATION AND PROTHETIC CORRECTION OF THE HEARING

DE2707038A1
(en)

1977-02-18
1978-08-24
Philips Patentverwaltung
Hearing perception tester using bone conductivity – has pressure piston set into oscillation by permanent magnet system and AC coil

US4284856A
(en)

1979-09-24
1981-08-18
Hochmair Ingeborg
Multi-frequency system and method for enhancing auditory stimulation and the like

US4419995A
(en)

1981-09-18
1983-12-13
Hochmair Ingeborg
Single channel auditory stimulation system

SE431705B
(en)

1981-12-01
1984-02-20
Bo Hakansson

COUPLING, PREFERRED FOR MECHANICAL TRANSMISSION OF SOUND INFORMATION TO THE BALL OF A HEARING DAMAGED PERSON

1985

1985-05-23
US
US06/737,188
patent/US4612915A/en
not_active
Expired – Fee Related

1986

1986-04-30
GB
GB08610605A
patent/GB2176078B/en
not_active
Expired

1986-05-02
CA
CA000508302A
patent/CA1251274A/en
not_active
Expired

1986-05-08
IL
IL78724A
patent/IL78724A/en
not_active
IP Right Cessation

1986-05-16
SE
SE8602251A
patent/SE468374B/en
not_active
IP Right Cessation

1986-05-21
NL
NL8601286A
patent/NL8601286A/en
not_active
Application Discontinuation

1986-05-21
DE
DE19863617089
patent/DE3617089A1/en
not_active
Withdrawn

1986-05-22
IT
IT67425/86A
patent/IT1189678B/en
active

1986-05-22
AU
AU57803/86A
patent/AU593251B2/en
not_active
Ceased

1986-05-22
DK
DK238086A
patent/DK238086A/en
not_active
Application Discontinuation

1986-05-22
JP
JP61116300A
patent/JPS61273100A/en
active
Granted

1986-05-22
BE
BE0/216695A
patent/BE904809A/en
not_active
IP Right Cessation

1986-05-22
FR
FR868607286A
patent/FR2582216B1/en
not_active
Expired – Fee Related

1986-05-23
ES
ES555252A
patent/ES8707067A1/en
not_active
Expired

Patent Citations (3)

* Cited by examiner, † Cited by third party

Publication number
Priority date
Publication date
Assignee
Title

GB553955A
(en)

1941-10-28
1943-06-11
Rudolf Goldschmidt
Improvements in or relating to electro-magnetic sound-transmission apparatus

AU2438145A
(en)

1945-10-30
1948-08-19

An improved hearing appliance for deaf persons

US4352960A
(en)

1980-09-30
1982-10-05
Baptist Medical Center Of Oklahoma, Inc.
Magnetic transcutaneous mount for external device of an associated implant

Cited By (1)

* Cited by examiner, † Cited by third party

Publication number
Priority date
Publication date
Assignee
Title

AU614616B2
(en)

1988-05-24
1991-09-05
Steen B. Rasmussen
Earplug for noise protected communication between the user of the earplug and surroundings

Also Published As

Publication number
Publication date

DK238086D0
(en)

1986-05-22

IL78724A
(en)

1992-06-21

US4612915A
(en)

1986-09-23

NL8601286A
(en)

1986-12-16

DE3617089A1
(en)

1986-11-27

JPS61273100A
(en)

1986-12-03

AU5780386A
(en)

1986-11-27

SE468374B
(en)

1992-12-21

FR2582216B1
(en)

1992-06-12

FR2582216A1
(en)

1986-11-28

SE8602251L
(en)

1986-11-24

ES555252A0
(en)

1987-07-16

GB2176078A
(en)

1986-12-10

DK238086A
(en)

1986-11-24

BE904809A
(en)

1986-09-15

JPH0552747B2
(en)

1993-08-06

IT8667425D0
(en)

1986-05-22

IL78724A0
(en)

1986-08-31

IT1189678B
(en)

1988-02-04

ES8707067A1
(en)

1987-07-16

SE8602251D0
(en)

1986-05-16

CA1251274A
(en)

1989-03-14

GB8610605D0
(en)

1986-06-04

GB2176078B
(en)

1989-01-05

Información de contacto