US3882285A - Implantable hearing aid and method of improving hearing - Google Patents

Implantable hearing aid and method of improving hearing Download PDF

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US3882285A
US3882285A US404339A US40433973A US3882285A US 3882285 A US3882285 A US 3882285A US 404339 A US404339 A US 404339A US 40433973 A US40433973 A US 40433973A US 3882285 A US3882285 A US 3882285A
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ear canal
ear
path
hearing device
mechanical
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James A Nunley
Jeremy A Agnew
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MEDICAL DEVICES GROUP Inc A CORP OF WIS
VICON INSTR CO
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VICON INSTR CO
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Assigned to SCHAEFER, DONALD reassignment SCHAEFER, DONALD ASSIGNMENT OF ASSIGNORS INTEREST. Assignors: JOHN C. EASTLACK, TRUSTEE APPOINTED IN THE BANKRUPTCY PROCEEDING OF T.H.C., INC., D/B/A THE VICON INSTRUMENT COMPANY
Assigned to MEDICAL DEVICES GROUP, INC., A CORP. OF WIS. reassignment MEDICAL DEVICES GROUP, INC., A CORP. OF WIS. ASSIGNMENT OF ASSIGNORS INTEREST. Assignors: SCHAEFER, DONALD
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    • 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
    • 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

  • ABSTRACT A self-contained hearing device made of components compatible with the human body is provided which is implanted in a hollowed-out portion of the skull adjacent the ear canal.
  • a microphone port is connected with the ear canal for receiving sound that enters the ear and transforming it to energies which are transmitted by a direct connection to the ossicular chain or to other mechanical movable portions of the middle ear.
  • a method of improving hearing is provided wherein a parallel hearing path is provided to augment the normal hearing path.
  • This invention relates to a hearing device, and more particularly to a hearing device which is totally implantable in the skull of a human being.
  • the device provides a parallel path for sound transmittal from the ear canal to the cochlea in addition to the normal hearing path to provide improved response at the oval window, to sound entering the ear canal.
  • a device utilizing a piezo-electric element is disclosed in U.S. Pat. No. 3,712,962 to Epley, which includes an implanted receiver and a piezo-electric element connected to the ossicular chain.
  • the receiver is responsive to an external transmitter worn on the body of the user.
  • this device has the disadvantage in that the entire device is not implanted in the ear and that many extraneous sounds may be transmitted to the receiver which distort the signal received by the ear.
  • the sounds received would not necessarily be the same as those passing through the ear canal causing distortion and confusion of sound transmitted both through the ear canal and through the hearing device to the cochlea, resulting in a garbled and possibly highly unintelligible sound sensed by the user.
  • the device depends upon the transformation of sound waves to mechanical movements which may or may not be in phase with sounds coming into the ear canal.
  • a novel method and apparatus for improving defective hearing wherein a self-contained miniature hearing device having a transducer, such as a microphone with a microphone port positionable in the ear canal, an amplifier and a transmitter which provides a mechanical response to the sound received by the microphone, is implanted in the skull just behind the ear with the microphone port positioned in the ear canal and the mechanical response means connected between the transmitter and mechanical drive structure within the ear.
  • a transducer such as a microphone with a microphone port positionable in the ear canal
  • an amplifier and a transmitter which provides a mechanical response to the sound received by the microphone
  • a parallel path provided by the implanted unit wherein sound is received in the ear canal and amplified by the hearing aid device andconverted to a mechanical response which is connected to a mechanical drive structure in the ear.
  • mechanical drive structure within the ear includes all movable elements of the ear, including the ear drum, all parts of the ossicular chain, and the oval window; and the term parallel path refers to a path providing an alternate route for sound to travel along at least a portion of the normal route of sound travel from the ear canal to the oval window and is not limited to a geometrically parallel arrangement.
  • the transmitter includes a piezo-electric crystal connected to one end of a rod which is moved by the piezoelectric crystal in response to sound waves picked up by the receiver, with the other end of the rod being connected to the ossicular chain, preferably to the stapes.
  • This attachment can be made in any medically suitable manner.
  • a distinct advantage of this invention is that the rod can be connected to different portions along the mechanical drive structure of the ear, depending upon the particular hearing defect of the person on which it is to be used. While the stapes is believed to be the most practical place to connect the wire, it could be connected to other portions of the chain, or, if the ossicular chain is entirely defective, it can be attached directly to the oval window.
  • FIG. 1 is a fragmentary section through a portion of a human skull adjacent the ear showing the location of the implantable hearing aid of this invention within the skull;
  • FIG. 2 is an enlarged longitudinal section through the implantable hearing aid of FIG. 1 showing further details of construction
  • FIG. 3 is a circuit diagram which can be used in the hearing aid of FIGS. 1 and 2.
  • an implantable hearing device H is implanted in the skull 2 in a recess 4 formed adjacent an ear canal 6.
  • the ear 8 is bent forward and an incision (not shown) made therebehind to expose the skull 2 whereupon it is hollowed-out to form the recess 4 and receive hearing device H which is made of a material which is compatible with the human body as is well understood in the art.
  • the hearing device H includes a housing 10 which contains a transducer, such as a microphone, an amplifier and a transmitter.
  • housing 10 includes three compartments l2, l4 and 16, as shown.
  • a microphone can be placed in compartment 12, an amplifier circuit in compartment 14 and a source of power, such as a battery, in compartment 16, after which housing 10 can be closed by lid 18 sealed thereto by suitable means.
  • compartment 12 has a microphone port 20 which, as shown in FIG. 1, is connected to ear canal 6 by means of a tube 22 so that the hearing device H receives all audio signals as they enter the ear.
  • the audio signal entering through tube 22 and port 20 is transmitted by a microphone in compartment 12 to an amplifier circuit in compartment 14 where the signal is amplified and used to power a piezo-electric crystal 24 which conveniently is mounted on a metal disc 26 connected to the end of housing 10, as by a silicon rubber mounting 28.
  • the signal causes movements of crystal 24 in response to the audio signal received by the microphone causing longitudinal movement of an elongated rigid element such as a metal wire or rod 30 which moves in response to the signal and has an outer end connected to a portion of the mechanical drive structure within the ear, such as the ossicular chain C.
  • the ossicular chain will be caused to move or vibrate in response to movement of the piezo-electric crystal and rod 30 and, therefore, transmit this response to the oval window 32 to provide suitable responses in the cochlea.
  • Other configurations can be used and certain modifications may be desirable for specific applications.
  • the ossicular chain C comprises a malleus 34, which normally moves in response to the tympanic membrane or car drum 36.
  • the malleus is in turn connected to the incus 38 which is connected to the stapes 40 which causes movement of the oval window 32.
  • wire 30 extends to the stapes 40, but it should be understood that the wire could be connected to any other portion of the ossicular chain C, or to the ear drum 36 or the oval window 32, depending upon the particular condition and problem causing deficiency in the hearing of the user.
  • hearing device H in the position shown, a parallel path of sound transmittal is provided in addition to the normal hearing path.
  • the hearing device does not interfere with normal hearing, but can be used to supplement and amplify the response so that the response perceived by the user is as nearly normal as is possible.
  • a typical circuit for hearing device H is shown in FIG. 3, but it will be understood that various other circuits can be used and certain modifications may be desirable for particular applications.
  • a low current gain microphone 42 having a resistance of 1K to K ohms can be used.
  • capacitor C l and C2 are of l mf having a low frequency response.
  • C3 is a 0.01 mf type with a high frequency roll off, and C4 is a mf decoupling capacitor.
  • R1 is a 470K ohm feed-back resistor, whereas R2 is a 100K ohm idle current set resistor.
  • R3 is a 5K ohm resistor for volume control purposes.
  • battery 44 is used as the power source. In some applications this battery may be a 1.5 volt mercury battery. Periodically it may be necessary to make an incision behind ear 8 and remove the hearing device H to replace power source 44 in compartment 16. After replacement, of course, the hearing device can be remounted in recess 4 as shown in FIG. 1. Some replacements may be avoided by use of rechargeable power sources.
  • a hearing device has been provided which is completely self-contained and can be implanted in the skull of the user so that there are no cosmetic drawbacks, as the device will be completely hidden.
  • a novel method of improving hearing is provided wherein only the sound that enters the ear is picked up and converted to a mechanical signal which is transmitted along a parallel path to aid the impaired hearing of the user so that the user may perceive the signal as nearly normal as is possible.
  • a self-contained implantable hearing device for positioning in a hollowed-out portion of the skull adjacent to the ear canal to provide a sound path parallel to the normal sound path to improve hearing, said unit comprising:
  • transducer means positionable adjacent the ear canal for receiving audio signals entering the ear canal and converting them to electrical signals; means for connecting said transducer means with the ear canal for transmission of the audio signal from the ear canal to said transducer means for transmission along a path parallel to the ear canal;
  • amplifier means coupled to said transducer means adjacent the ear canal for amplifying the electrical signal produced by said transducer means along said parallel path;
  • transmitter means coupled to said amplifier means adjacent the ear canal for converting the electrical signal to a mechanical response
  • mechanical response means coupled to said transmitter means adjacent the ear canal and connectable to a mechanical drive structure within the ear to complete said parallel path and to provide a mechanical movement of the structure in response to an acoustical signal received by said transducer, which augments and supports any signal produced by the transmission of sounds through the normal sound path of the ear to provide improved hearing.
  • said mechanical response means includes:
  • said mechanical response means is connected to the ossicular chain.
  • said mechanical response means is connected to the stapes.
  • An implantable hearing device unit as claimed in claim 1, wherein:
  • said mechanical response means is connected to the oval window.
  • a self-contained implantable hearing device for positioning in a hollowed-out portion of the skull adjacent to the ear canal to provide a sound path parallel to the normal sound path to improve hearing, said unit comprising:
  • transducer means positionable adjacent the ear canal for receiving audio signals entering the ear canal and converting them to electrical signals;
  • amplifier means coupled to said transducer means adjacent the ear canal for amplifying the electrical signal produced by said transducer means along said parallel path;
  • a piezo-electric crystal connected to said amplifier means adjacent the ear canal and providing a mechanical response proportional to the electrical signal from said amplifier means;
  • an elongated rigid element having one end connected to said piezo-electrical crystal adjacent the ear canal and the other end connectable to the ossicular chain to complete said parallel path and to provide a mechanical movement of the structure in response to an acoustical signal received by said transducer means, which augments and supports any signal produced by the transmission of sound through normal sound path of the ear to provide improved hearing.
  • a method of improving hearing by providing a sound path parallel to the normal sound path for reproducing sound and augmenting the sound entering an ear canal including the steps of:
  • said hearing device includes in series a microphone, an amplifier circuit, and a mechanical output responsive to an audio signal received by the microphone;
  • connection of the mechanical output is to the stapes.

Abstract

A self-contained hearing device made of components compatible with the human body is provided which is implanted in a hollowedout portion of the skull adjacent the ear canal. A microphone port is connected with the ear canal for receiving sound that enters the ear and transforming it to energies which are transmitted by a direct connection to the ossicular chain or to other mechanical movable portions of the middle ear. A method of improving hearing is provided wherein a parallel hearing path is provided to augment the normal hearing path.

Description

United States Patent 1191 Nunley et al.
1451 May 6,1975
[ IMPLANTABLE HEARING AID AND METHOD OF IMPROVING HEARING [75] Inventors: James A. Nunley; Jeremy A. Agnew,
both of Colorado Springs, C010.
[73] Assignee: The Vicon Instrument Company,
Colorado Springs, C010.
[22] Filed: Oct. 9, 1973 [21] Appl. No.: 404,339
[52] U.S. Cl. 179/107 E [51] Int. Cl. H04r 25/02 [58] Field of Search 179/107 R, l E
[56] References Cited UNITED STATES PATENTS 3,346,704 10/1967 Mahoney 179/107 R 3,712,962 l/l973 Epley 179/107 R 3,764,748 10/1973 Branch 179/107 E OTHER PUBLICATIONS American Academy of Ophtalmology &
Otolarynology, Course 319 Text, Oct. 1, 1966.
Primary Examiner-Ralph D. Blakeslee Attorney, Agent, or Firm-Sheridan, Ross & Fields [57] ABSTRACT A self-contained hearing device made of components compatible with the human body is provided which is implanted in a hollowed-out portion of the skull adjacent the ear canal. A microphone port is connected with the ear canal for receiving sound that enters the ear and transforming it to energies which are transmitted by a direct connection to the ossicular chain or to other mechanical movable portions of the middle ear. A method of improving hearing is provided wherein a parallel hearing path is provided to augment the normal hearing path.
10 Claims, 3 Drawing Figures PATENTEUHAY 61975 IMPLANTABLE HEARING AID AND METHOD OF IMPROVING HEARING BACKGROUND OF THE INVENTION 1. Field of the Invention This invention relates to a hearing device, and more particularly to a hearing device which is totally implantable in the skull of a human being. The device provides a parallel path for sound transmittal from the ear canal to the cochlea in addition to the normal hearing path to provide improved response at the oval window, to sound entering the ear canal.
2. Description of the Prior Art Various attempts have been made to miniaturize and conceal hearing devices to make them aesthetically acceptable. In addition, attempts have been made to place hearing devices inside the ear or even implant them within the skull. U.S. Pat. No. 3, 1 70,046 to Leale, discloses a hearing device which is entirely received within the ear canal. The difficulty with such a device is that it blocks out the normal passage of sound through the ear canal so that all sound must be transmitted through the device. Furthermore, it is still partially visible when looking at the ear from the side.
A device utilizing a piezo-electric element is disclosed in U.S. Pat. No. 3,712,962 to Epley, which includes an implanted receiver and a piezo-electric element connected to the ossicular chain. The receiver is responsive to an external transmitter worn on the body of the user. Obviously, this device has the disadvantage in that the entire device is not implanted in the ear and that many extraneous sounds may be transmitted to the receiver which distort the signal received by the ear.
A totally implantable hearing device and method for implanting the same is shown in U.S. Pat. Nos. 3,346,704 and 3,557,775, respectively, both to Mahoney. In these hearing devices, the microphone is located just under the skin behind the ear for receiving signals which are transmitted by means of a speaker tube to the middle ear where signals are transmitted by the round or oval window to the cochlea. With the microphone tube located just under the skin, there is a possibility of distortion of the sound and also, due to the position of the microphone behind the ear, all sound may not reach it. In addition, the sounds received would not necessarily be the same as those passing through the ear canal causing distortion and confusion of sound transmitted both through the ear canal and through the hearing device to the cochlea, resulting in a garbled and possibly highly unintelligible sound sensed by the user. Furthermore, the device depends upon the transformation of sound waves to mechanical movements which may or may not be in phase with sounds coming into the ear canal.
SUMMARY OF THE INVENTION In this invention, a novel method and apparatus for improving defective hearing has been provided wherein a self-contained miniature hearing device having a transducer, such as a microphone with a microphone port positionable in the ear canal, an amplifier and a transmitter which provides a mechanical response to the sound received by the microphone, is implanted in the skull just behind the ear with the microphone port positioned in the ear canal and the mechanical response means connected between the transmitter and mechanical drive structure within the ear. Thus, some hearing can be obtained in the normal manner, if a total hearing loss is not present, and this can be supplemented by a parallel path provided by the implanted unit wherein sound is received in the ear canal and amplified by the hearing aid device andconverted to a mechanical response which is connected to a mechanical drive structure in the ear. As used throughout the specification and claims herein, the term mechanical drive structure within the ear includes all movable elements of the ear, including the ear drum, all parts of the ossicular chain, and the oval window; and the term parallel path refers to a path providing an alternate route for sound to travel along at least a portion of the normal route of sound travel from the ear canal to the oval window and is not limited to a geometrically parallel arrangement.
In a preferred embodiment of the invention, the transmitter includes a piezo-electric crystal connected to one end of a rod which is moved by the piezoelectric crystal in response to sound waves picked up by the receiver, with the other end of the rod being connected to the ossicular chain, preferably to the stapes. This attachment can be made in any medically suitable manner.
A distinct advantage of this invention is that the rod can be connected to different portions along the mechanical drive structure of the ear, depending upon the particular hearing defect of the person on which it is to be used. While the stapes is believed to be the most practical place to connect the wire, it could be connected to other portions of the chain, or, if the ossicular chain is entirely defective, it can be attached directly to the oval window.
Additional advantages of this invention will become apparent from the description which follows, taken in conjunction with the accompanying drawings.
BRIEF DESCRIPTION OF THE DRAWINGS FIG. 1 is a fragmentary section through a portion of a human skull adjacent the ear showing the location of the implantable hearing aid of this invention within the skull;
FIG. 2 is an enlarged longitudinal section through the implantable hearing aid of FIG. 1 showing further details of construction; and
FIG. 3 is a circuit diagram which can be used in the hearing aid of FIGS. 1 and 2.
DESCRIPTION OF THE PREFERRED EMBODIMENT In accordance with this invention, an implantable hearing device H is implanted in the skull 2 in a recess 4 formed adjacent an ear canal 6. To accomplish this, the ear 8 is bent forward and an incision (not shown) made therebehind to expose the skull 2 whereupon it is hollowed-out to form the recess 4 and receive hearing device H which is made of a material which is compatible with the human body as is well understood in the art. Conveniently, the hearing device H includes a housing 10 which contains a transducer, such as a microphone, an amplifier and a transmitter. As best seen in FIG. 2, housing 10 includes three compartments l2, l4 and 16, as shown. Conveniently, a microphone can be placed in compartment 12, an amplifier circuit in compartment 14 and a source of power, such as a battery, in compartment 16, after which housing 10 can be closed by lid 18 sealed thereto by suitable means. Conveniently, compartment 12 has a microphone port 20 which, as shown in FIG. 1, is connected to ear canal 6 by means of a tube 22 so that the hearing device H receives all audio signals as they enter the ear.
As described more fully below, the audio signal entering through tube 22 and port 20 is transmitted by a microphone in compartment 12 to an amplifier circuit in compartment 14 where the signal is amplified and used to power a piezo-electric crystal 24 which conveniently is mounted on a metal disc 26 connected to the end of housing 10, as by a silicon rubber mounting 28. Thus, the signal causes movements of crystal 24 in response to the audio signal received by the microphone causing longitudinal movement of an elongated rigid element such as a metal wire or rod 30 which moves in response to the signal and has an outer end connected to a portion of the mechanical drive structure within the ear, such as the ossicular chain C. By this means, the ossicular chain will be caused to move or vibrate in response to movement of the piezo-electric crystal and rod 30 and, therefore, transmit this response to the oval window 32 to provide suitable responses in the cochlea. Other configurations can be used and certain modifications may be desirable for specific applications.
As is well known in the art, the ossicular chain C comprises a malleus 34, which normally moves in response to the tympanic membrane or car drum 36. The malleus is in turn connected to the incus 38 which is connected to the stapes 40 which causes movement of the oval window 32. At present, it is believed that the device will operate more satisfactorily if wire 30 extends to the stapes 40, but it should be understood that the wire could be connected to any other portion of the ossicular chain C, or to the ear drum 36 or the oval window 32, depending upon the particular condition and problem causing deficiency in the hearing of the user.
From the arrangement shown, it is apparent that by inserting hearing device H in the position shown, a parallel path of sound transmittal is provided in addition to the normal hearing path. Thus, the hearing device does not interfere with normal hearing, but can be used to supplement and amplify the response so that the response perceived by the user is as nearly normal as is possible.
A typical circuit for hearing device H is shown in FIG. 3, but it will be understood that various other circuits can be used and certain modifications may be desirable for particular applications. In the present circuit, a low current gain microphone 42 having a resistance of 1K to K ohms can be used. Conveniently, capacitor C l and C2 are of l mf having a low frequency response. C3 is a 0.01 mf type with a high frequency roll off, and C4 is a mf decoupling capacitor. R1 is a 470K ohm feed-back resistor, whereas R2 is a 100K ohm idle current set resistor. R3 is a 5K ohm resistor for volume control purposes. Conveniently, battery 44 is used as the power source. In some applications this battery may be a 1.5 volt mercury battery. Periodically it may be necessary to make an incision behind ear 8 and remove the hearing device H to replace power source 44 in compartment 16. After replacement, of course, the hearing device can be remounted in recess 4 as shown in FIG. 1. Some replacements may be avoided by use of rechargeable power sources.
From the foregoing, the advantages of this invention are readily apparent. A hearing device has been provided which is completely self-contained and can be implanted in the skull of the user so that there are no cosmetic drawbacks, as the device will be completely hidden. In addition, a novel method of improving hearing is provided wherein only the sound that enters the ear is picked up and converted to a mechanical signal which is transmitted along a parallel path to aid the impaired hearing of the user so that the user may perceive the signal as nearly normal as is possible.
The invention has been described in detail with particular reference to a preferred embodiment thereof, but it will be understood that variations and modifications can be effected within the spirit and scope of this invention.
What is claimed is:
l. A self-contained implantable hearing device for positioning in a hollowed-out portion of the skull adjacent to the ear canal to provide a sound path parallel to the normal sound path to improve hearing, said unit comprising:
transducer means positionable adjacent the ear canal for receiving audio signals entering the ear canal and converting them to electrical signals; means for connecting said transducer means with the ear canal for transmission of the audio signal from the ear canal to said transducer means for transmission along a path parallel to the ear canal;
amplifier means coupled to said transducer means adjacent the ear canal for amplifying the electrical signal produced by said transducer means along said parallel path;
transmitter means coupled to said amplifier means adjacent the ear canal for converting the electrical signal to a mechanical response; and
mechanical response means coupled to said transmitter means adjacent the ear canal and connectable to a mechanical drive structure within the ear to complete said parallel path and to provide a mechanical movement of the structure in response to an acoustical signal received by said transducer, which augments and supports any signal produced by the transmission of sounds through the normal sound path of the ear to provide improved hearing.
2. An implantable hearing device unit, as claimed in claim 1, wherein said mechanical response means includes:
an elongated rigid element.
3. An implantable hearing device unit, as claimed in claim 1, wherein said transmitter means is:
a pieZo-electric crystal.
4. An implantable hearing device unit, as claimed in claim 1, wherein:
said mechanical response means is connected to the ossicular chain.
5. An implantable hearing device unit, as claimed in claim 1, wherein:
said mechanical response means is connected to the stapes.
6. An implantable hearing device unit, as claimed in claim 1, wherein:
said mechanical response means is connected to the oval window.
7. A self-contained implantable hearing device for positioning in a hollowed-out portion of the skull adjacent to the ear canal to provide a sound path parallel to the normal sound path to improve hearing, said unit comprising:
transducer means positionable adjacent the ear canal for receiving audio signals entering the ear canal and converting them to electrical signals;
means for connecting said transducer means with the ear canal for transmission of the audio signal from the ear canal to said transducer means for transmission along a path parallel to the ear canal;
amplifier means coupled to said transducer means adjacent the ear canal for amplifying the electrical signal produced by said transducer means along said parallel path;
a piezo-electric crystal connected to said amplifier means adjacent the ear canal and providing a mechanical response proportional to the electrical signal from said amplifier means; and
an elongated rigid element having one end connected to said piezo-electrical crystal adjacent the ear canal and the other end connectable to the ossicular chain to complete said parallel path and to provide a mechanical movement of the structure in response to an acoustical signal received by said transducer means, which augments and supports any signal produced by the transmission of sound through normal sound path of the ear to provide improved hearing.
8. A method of improving hearing by providing a sound path parallel to the normal sound path for reproducing sound and augmenting the sound entering an ear canal, including the steps of:
implanting a hearing device in the skull bone adjacent the ear canal, wherein said hearing device includes in series a microphone, an amplifier circuit, and a mechanical output responsive to an audio signal received by the microphone;
connecting the microphone in audio communication with the ear canal; and
connecting the mechanical output of the hearing device to a mechanical drive structure within the car so that sound entering the ear can pass along a parallel path through said hearing device to augment sound passing along the normal path.
9. The method as claimed in claim 8, wherein the connecting of the mechanical output is made to the ossicular chain.
10. A method as claimed in claim 8, wherein the connection of the mechanical output is to the stapes.

Claims (10)

1. A self-contained implantable hearing device for positioning in a hollowed-out portion of the skull adjacent to the ear canal to provide a sound path parallel to the normal sound path to improve hearing, said unit comprising: transducer means positionable adjacent the ear canal for receiving audio signals entering the ear canal and converting them to electrical signals; means for connecting said transducer means with the ear canal for transmission of the audio signal from the ear canal to said transducer means for transmission along a path parallel to the ear canal; amplifier means coupled to said transducer means adjacent the ear canal for amplifying the electrical signal produced by said transducer means along said parallel path; transmitter means coupled to said amplifier means adjacent the ear canal for converting the electrical signal to a mechanical response; and mechanical response means coupled to said transmitter means adjacent the ear canal and connectable to a mechanical drive structure within the ear to complete said parallel path and to provide a mechanical movement of the structure in response to an acoustical signal received by said transducer, which augments and supports any signal produced by the transmission of sounds through the normal sound path of the ear to provide improved hearing.
2. An implantable hearing device unit, as claimed in claim 1, wherein said mechanical response means includes: an elongated rigid element.
3. An implantable hearing device unit, as claimed in claim 1, wherein said transmitter means is: a piezo-electric crystal.
4. An implantable hearing device unit, as claimed in claim 1, wherein: said mechanical response means is connected to the ossicular chain.
5. An implantable hearing device unit, as claimed in claim 1, wherein: said mechanical response means is connected to the stapes.
6. An implantable hearing device unit, as claimed in claim 1, wherein: said mechanical response means is connected to the oval window.
7. A self-contained implantable hearing device for positioning in a hollowed-out portion of the skull adjacent to the ear canal to provide a sound path parallel to the normal sound path to improve hearing, said unit comprising: transducer means positionable adjacent the ear canal for receiving audio signals entering the ear canal and converting them to electrical signals; means for connecting said transducer means with the ear canal for transmission of the audio signal from the ear canal to said transducer means for transmission along a path parallel to the ear canal; amplifier means coupled to said transducer means adjacent the ear canal for amplifying the electrical signal produced by said transducer means along said parallel path; a piezo-electric crystal connected to said amplifier means adjacent the ear canal and providing a mechanical response proportional to the electrical signal from said amplifier means; and an elongated rigid element having one end connected to said piezo-electrical crystal adjacent the ear canal and the other end connectable to the ossicular chain to complete said parallel path and to provide a mechanical movement of the structure in response to an acoustical signal received by said transducer means, which augments and supports any signal produced by the transmission of sound through normal sound path of the ear to provide improved hearing.
8. A method of improving hearing by providing a sound path parallel to the normal sound path for reproducing sound and augmenting the sound entering an ear canal, including the steps of: implanting a hearing device in the skull bone adjacent the ear canal, wherein said hearing device includes in series a microphone, an amplifier circuit, and a mechanical output responsive to an audio signal received by the microphone; connecting the microphone in audio communication wIth the ear canal; and connecting the mechanical output of the hearing device to a mechanical drive structure within the ear so that sound entering the ear can pass along a parallel path through said hearing device to augment sound passing along the normal path.
9. The method as claimed in claim 8, wherein the connecting of the mechanical output is made to the ossicular chain.
10. A method as claimed in claim 8, wherein the connection of the mechanical output is to the stapes.
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US4776322A (en) * 1985-05-22 1988-10-11 Xomed, Inc. Implantable electromagnetic middle-ear bone-conduction hearing aid device
WO1989005559A1 (en) * 1987-12-04 1989-06-15 Claus Jansen Electroacoustic transducer
US4850962A (en) * 1984-12-04 1989-07-25 Medical Devices Group, Inc. Implantable hearing aid and method of improving hearing
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
US5277694A (en) * 1991-02-13 1994-01-11 Implex Gmbh Electromechanical transducer for implantable hearing aids
US5390254A (en) * 1991-01-17 1995-02-14 Adelman; Roger A. Hearing apparatus
WO1995017078A1 (en) * 1993-12-14 1995-06-22 Hill Frank C Hearing aid
US5456654A (en) * 1993-07-01 1995-10-10 Ball; Geoffrey R. Implantable magnetic hearing aid transducer
US5554096A (en) * 1993-07-01 1996-09-10 Symphonix Implantable electromagnetic hearing transducer
US5624376A (en) * 1993-07-01 1997-04-29 Symphonix Devices, Inc. Implantable and external hearing systems having a floating mass transducer
EP0806884A1 (en) * 1996-05-10 1997-11-12 IMPLEX GmbH Spezialhörgeräte Apparatus for the electro-mechanical stimulation and for the examination of the ears
US5702342A (en) * 1993-10-14 1997-12-30 Otologics Llc. Directionally-controllable mounting apparatus
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
US5814095A (en) * 1996-09-18 1998-09-29 Implex Gmbh Spezialhorgerate Implantable microphone and implantable hearing aids utilizing same
US5881158A (en) * 1996-05-24 1999-03-09 United States Surgical Corporation Microphones for an implantable hearing aid
US5897486A (en) * 1993-07-01 1999-04-27 Symphonix Devices, Inc. Dual coil floating mass transducers
US5913815A (en) * 1993-07-01 1999-06-22 Symphonix Devices, Inc. Bone conducting floating mass transducers
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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
USH1875H (en) * 1996-07-22 2000-10-03 Microtronic A/S Electroacoustic transducer
US6137889A (en) * 1998-05-27 2000-10-24 Insonus Medical, Inc. Direct tympanic membrane excitation via vibrationally conductive assembly
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US6473651B1 (en) 1999-03-02 2002-10-29 Advanced Bionics Corporation Fluid filled microphone balloon to be implanted in the middle ear
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
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
US6540661B1 (en) 1999-10-07 2003-04-01 Phonak Ag Arrangement for coupling of a driver to a coupling site of the ossicular chain
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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
US6592512B2 (en) 2000-08-11 2003-07-15 Phonak Ag At least partially implantable system for rehabilitation of a hearing disorder
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
US6726618B2 (en) 2001-04-12 2004-04-27 Otologics, Llc Hearing aid with internal acoustic middle ear transducer
US6730015B2 (en) 2001-06-01 2004-05-04 Mike Schugt Flexible transducer supports
EP1439737A2 (en) 2003-01-15 2004-07-21 Med-El Elektromedizinische Geräte Ges.m.b.h. Implantable electromechanical transducer
US20050102006A1 (en) * 2003-09-25 2005-05-12 Whitehurst Todd K. Skull-mounted electrical stimulation system
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
US20050203557A1 (en) * 2001-10-30 2005-09-15 Lesinski S. G. Implantation method for a hearing aid microactuator implanted into the cochlea
US20050259840A1 (en) * 1999-06-08 2005-11-24 Insound Medical, Inc. Precision micro-hole for extended life batteries
US20060050914A1 (en) * 1998-11-25 2006-03-09 Insound Medical, Inc. Sealing retainer for extended wear hearing devices
US20060058573A1 (en) * 2004-09-16 2006-03-16 Neisz Johann J Method and apparatus for vibrational damping of implantable hearing aid components
US7016504B1 (en) 1999-09-21 2006-03-21 Insonus Medical, Inc. Personal hearing evaluator
US20060189841A1 (en) * 2004-10-12 2006-08-24 Vincent Pluvinage Systems and methods for photo-mechanical hearing transduction
US20060251278A1 (en) * 2005-05-03 2006-11-09 Rodney Perkins And Associates Hearing system having improved high frequency response
US20060293723A1 (en) * 2003-12-19 2006-12-28 Whitehurst Todd K Skull-mounted electrical stimulation system and method for treating patients
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
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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
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US5015225A (en) * 1985-05-22 1991-05-14 Xomed, Inc. Implantable electromagnetic middle-ear bone-conduction hearing aid device
EP0263254A1 (en) * 1986-08-11 1988-04-13 Medical Devices Group, Inc. Implantable hearing aid
US4774933A (en) * 1987-05-18 1988-10-04 Xomed, Inc. Method and apparatus for implanting hearing device
WO1989005559A1 (en) * 1987-12-04 1989-06-15 Claus Jansen Electroacoustic transducer
US5085628A (en) * 1988-09-09 1992-02-04 Storz Instrument Company Implantable hearing aid coupler device
US5390254A (en) * 1991-01-17 1995-02-14 Adelman; Roger A. Hearing apparatus
US6041129A (en) * 1991-01-17 2000-03-21 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
US5857958A (en) * 1993-07-01 1999-01-12 Symphonix Devices, Inc. Implantable and external hearing systems having a floating mass transducer
US5624376A (en) * 1993-07-01 1997-04-29 Symphonix Devices, Inc. Implantable and external hearing systems having a floating mass transducer
US5800336A (en) * 1993-07-01 1998-09-01 Symphonix Devices, Inc. Advanced designs of floating mass transducers
US6676592B2 (en) 1993-07-01 2004-01-13 Symphonix Devices, Inc. Dual coil floating mass transducers
US5456654A (en) * 1993-07-01 1995-10-10 Ball; Geoffrey R. Implantable magnetic hearing aid transducer
US6475134B1 (en) 1993-07-01 2002-11-05 Symphonix Devices, Inc. Dual coil floating mass transducers
US5554096A (en) * 1993-07-01 1996-09-10 Symphonix Implantable electromagnetic hearing transducer
US5897486A (en) * 1993-07-01 1999-04-27 Symphonix Devices, Inc. Dual coil floating mass transducers
US5913815A (en) * 1993-07-01 1999-06-22 Symphonix Devices, Inc. Bone conducting floating mass transducers
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AU686299B2 (en) * 1993-12-14 1998-02-05 Frank C. Hill Hearing aid
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US5951601A (en) * 1996-03-25 1999-09-14 Lesinski; S. George Attaching an implantable hearing aid microactuator
US5833626A (en) * 1996-05-10 1998-11-10 Implex Gmbh Spezialhorgerate Device for electromechanical stimulation and testing of hearing
EP0806884A1 (en) * 1996-05-10 1997-11-12 IMPLEX GmbH Spezialhörgeräte Apparatus for the electro-mechanical stimulation and for the examination of the ears
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
USH1875H (en) * 1996-07-22 2000-10-03 Microtronic A/S Electroacoustic transducer
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
US5814095A (en) * 1996-09-18 1998-09-29 Implex Gmbh Spezialhorgerate Implantable microphone and implantable hearing aids utilizing same
US6214046B1 (en) 1996-11-25 2001-04-10 St. Croix Medical, Inc. Method of implanting an implantable hearing assistance device with remote electronics unit
US6235056B1 (en) 1996-11-25 2001-05-22 St. Croix Medical, Inc. Implantable hearing assistance device with remote electronics unit
US6315710B1 (en) 1997-07-21 2001-11-13 St. Croix Medical, Inc. Hearing system with middle ear transducer mount
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
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
US20080137892A1 (en) * 1998-11-25 2008-06-12 Insound Medical, Inc. Semi-permanent canal hearing device and insertion method
US20100098281A1 (en) * 1998-11-25 2010-04-22 Insound Medical, Inc. Sealing retainer for extended wear hearing devices
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US6940988B1 (en) 1998-11-25 2005-09-06 Insound Medical, Inc. Semi-permanent canal hearing device
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US6277148B1 (en) 1999-02-11 2001-08-21 Soundtec, Inc. Middle ear magnet implant, attachment device and method, and test instrument and method
US7676372B1 (en) 1999-02-16 2010-03-09 Yugen Kaisha Gm&M Prosthetic hearing device that transforms a detected speech into a speech of a speech form assistive in understanding the semantic meaning in the detected speech
US6473651B1 (en) 1999-03-02 2002-10-29 Advanced Bionics Corporation Fluid filled microphone balloon to be implanted in the middle ear
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
US7379555B2 (en) 1999-06-08 2008-05-27 Insound Medical, Inc. Precision micro-hole for extended life batteries
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