US3557775A - Method of implanting a hearing aid - Google Patents

Method of implanting a hearing aid Download PDF

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US3557775A
US3557775A US663603A US3557775DA US3557775A US 3557775 A US3557775 A US 3557775A US 663603 A US663603 A US 663603A US 3557775D A US3557775D A US 3557775DA US 3557775 A US3557775 A US 3557775A
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ear
implanting
mastoid
human body
signal
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Jack Lawrence Mahoney
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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
    • H04R2225/31—Aspects of the use of accumulators in hearing aids, e.g. rechargeable batteries or fuel cells
    • 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

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  • Shapiro Att0rneylsler and Qmstein ABSTRACT A method is described of implanting a hearing improvement device within the human body, in which a postauricular incision is made in the skin of the anatomical area behind the auricular appendage of the external ear, to thereby expose the bony structure overlying the body of the mastoid, removing a predetermined area of bone down to the antrum cell of the mastoid, implanting the device in the cavity formed, and then closing the incision.
  • the device has a portion which extends into the middle ear space.
  • SHEET 2 OF 2 SKIN POSTERIOR TO AURICLE
  • MICROPHONE TUBE ll
  • AMPLIFIER UNIT IOI SPEAKER TUBE (IZI MIDDLE EAR CAVITY ROUND WINDOW DUCT TO COCHLEA I NVEN TOR.
  • This invention relates generally to a method of implanting a hearing aid in the human body, but has reference more particularly to a method in which the hearing aid is so implanted as to be completely enclosed within the head of the individual utilizing the hearing aid.
  • Hearing aids which are presently available on the market are usually worn outside of the body, and are therefore objectionable from an esthetic, cosmetic or functional viewpoint.
  • the present invention has as its primary object the provision of a method whereby an audio implant in the nature of a miniaturized system for amplifying sound, is placed directly in the structure of the ear and utilizes the impaired or-damaged, but still functioning, normal channels for transmission of sound to the brain.
  • Another object of the invention is to provide a method wherein an implant of the character described, is disposed in its entirety within the head structure of the user, and is entirely concealed from view, thereby eliminating any and all objections to its use from an esthetic or cosmetic point of view.
  • a further object of the invention is to provide a method wherein the implant utilizes a battery which is enclosed within the head structure.
  • FIG. I is a vertical cross-sectional view of aportion of a human head taken through theright side of the head.
  • FIG. 2 is a fragmentary elevational view showing a portion of the right side of the head, and with theexternal ear pulled forwardly to show or indicate where the implant and microphone tube are placed;
  • FIG. 3 is a tabulation of the means utilizing the implantiof the present invention, whereby sound is transmitted tothe temporal lobe of the brain, where the sound is heard.
  • FIG. 1 An understand ing of FIG. 1 can be gained if the observer can imagine he is inside the head of the person depicted in FIG. '1, and is looking outwardly and through the right ear.
  • the observer will see the auditory canal l, thetympanic membrane 2, the malleus 3, theincus 4. and themastoid antrum 5.
  • the tip of the mastoid is' indicated by reference numeral 6, the chorda tympani by reference numeral 7, a facial nerve by reference numeral 8 and thesquama by reference numeral 9.
  • I provide axhearing improvement device which Iterm an audio implant," and which consists of several components, including mainly a microphone, a battery, an amplifying system and a speaker,
  • the unit 10 is rectangular in shape, measuring approximately l cm. X l c'm., and a few millimeters in thickness, and is provided with a silicone rubber tube 11 extending centrally from one en'd'of the unit 10, and a similar tube '12 extending centrally from one side of the unit 10.
  • the tubes 11 and 12 are approximately IV: cm. in length, and approximately 2 mm. in diameter.
  • the tube 11, which I term the microphone tube, is attached to the microphone within the unit 10, and both ends of the tube are sealed with a very thin membrane of silicone rubber.
  • the tube 12, which I term the speaker tube is attached to the speaker within the unit 10, and both ends of this tube are sealed with a very thin membrane of silicone rubber.
  • a postauricular incision is made adjacent the auricular appendage of the external ear, in the skin of the anatomical area of the ear. This incision is approximately three centimeters in length, and is carried out under local anesthesia.
  • the bony structure overlying the body of the mastoid is exposed, and an area of bone, i.e., an area of approximately 2 square centimeters, is removed down to the antrum cell of the mastoid. A few of the air cells of the mastoid are then removed to enlarge the antrum cell to accommodate the unit 10.
  • the unit 10 is then placed directly into this space in the manner shown in FIG. I, and the speaker tube 12 is then placed in a passageway which extends from the antrum cell of the mastoid into the middle'ear space behind the ear drum. More specifically, the speaker tube is brought up through a small opening near the introitus of the ear canal, and to a point closely adjacent to what is commonly referred to as the ""round window The wave motion is transmitted to the cochlea, which startsthe electrical impulses to the temporal lobe'of the brain.
  • the microphone'tube '11 is then extended externally from -"the'ant'rum cell of the mastoid and is covered with skin and i will be disposed just beneath the skin behind the ear. The incision is th'en closed, and the ear again completely sealed. Since the'skin inc'isio'nis made in a hidden area adjacent the car, no noticeable scar will be produced, after healing.
  • the unit l0 is preferably a silver-cadmium battery'and'ca'n becharged by a magnetic induction coil which is attaehedto a head-band, which can be worn on the head while sleeping, or at anyother time which is convenient.
  • the induction coil is connected to a wire which leads to a transistorized charging'unit'which is energized from a conventional electrical outlet'ln charging the battery, the induction coil'onthehead'band' is placed directly over the main structure of the mastoid.
  • the implant' will function for approximately eight days before it becomes necessary to recharge such a battery with the magnetic induction coilf'Recharging of the battery requires approximately 6 hours.
  • One of theadvant'ages of the use of such an implant is that it is embeddedsolidly in the bone of the skull, and is so situated that it'c'an' drive' the sound directly into the inner car, without the necessity" of driving the's'ound'through the'tympanic mem brane, which offers considerable resistance to transmission of sound in cases of conductive deafness where the oval window and'stapesarefused by abnormal bone closure called otosclerosis.
  • Another advantage is that there are no parts which are disposed-externally of the head'or are'visible, so' that objec tions to use ofthe device, based on psychological factors, and cosmet'i'c'view'points'are eliminated.
  • a further advantage lies in the fact that the replacement batteries, and itsattendant costs, are eliminated.
  • a still further advantage resides in the elimination of the rushing andclothing noise which is a constant source of annoyance to individuals from movement across the microphones of hearing aids which are carried about the body.
  • the device is also of particular advantage for children who require the use of a hearing aid to hear sufficiently to carry on their school work, while finding it necessary to remove these aids during play and physical activity since external hearing aids and devices are easily dislodged or broken during such play or physical activity.
  • l have provided an audio implant in the nature of a miniaturized system for amplifying sound, which is placed directly in the structure of the ear and utilizes the impaired or damaged, but still functional, normal channels for transmission of sound to the brain.
  • the method of implanting a self-contained hearing improvement device within the human body in which said device contains a microphone, a battery, an amplifying system, which is neutral to the adjacent portions of the body, a microphone tube extending from the microphone in said unit; a speaker and a speaker tube extending therefrom including the steps of making an incision adjacent the auricular appendage of the external ear, in the skin'of the anotomical area of the ear, exposing the bony structure overlying the body of the mastoid, removing a predetermined area of bone down to the antrum cell of the mastoid, implanting the self-contained hearing improvement device in said antrum cell, situating an outer end of the microphone tube into position and adjacent the skin behind the auricular appendage and situating an outer end of said speaker tube into the middle ear space behind the ear drum through the antrum-inner ear passage; and thereafter closing the incision.
  • a hearing improvement device including signal-receiving means for receiving an incoming signal representative of a sound wave existing outside of the human body, intermediate means for converting said incoming signal to an audiofrequency electrical signal, output means including electrical-mechanical transducer means to generate mechanical motion from said electrical signal, an operative connection between said signal-receiving means, said intermediate means and between said intermediate means and said output means, said method comprising the steps of.making an incision in the skin in the auricular area of the ear adjacent the auricular appendage of the external ear; exposing the bony structure overlying the body of the mastoid; removing an area of bony structure to expose the an trum cell cavity; positioning said hearing improvement device within said cavity and with at least part of said output means in the middle ear space to deliver said generated mechanical motion directly thereinto; and then closing the incision.
  • a hearing improvement device in a human body, said device including signal-receiving means for receiving an incoming signal representative of a sound wave existing outside of said human body, intermediate means for converting said incoming signal to an audiofrequency electrical signal, output means including electrical-mechanical transducer means adapted to generate mechanical motion from the electrical signal, and operative connections from said signal-receiving means to said intermediate means and from the intermediate means to the output means; said method comprising the steps of surgically positioning at least a portion of said output means within the human body in the middle ear space at the round window to permit said generated mechanical motion to pass from said output means directly to the middle ear space behind the area of the tympanic membrane; concurrently positioning said signal-receiving means within the human body in position to receive said incoming signal; and further, surgically positioning said intermediate means within the human body at a locus removed from the middle ear space but adjacent the area of the auricular appendage of the ear and in operative relationship to said signal-receiving means
  • the method of implanting a hearing improvement device within the human body comprising the steps of: making an incision adjacent the auricular appendage of the external ear in the skin of the anatomical area of the ear; exposing the bony structure overlying the body of the mastoid; removing a predetermined area of bone down to the antrum cell of the mastoid; implanting a hearing improvement device in the cavity formed by the bone removal and mastoid antrum cell with at least a portion of the device extending into the middle ear space; and closing the incision.

Abstract

A method is described of implanting a hearing improvement device within the human body, in which a postauricular incision is made in the skin of the anatomical area behind the auricular appendage of the external ear, to thereby expose the bony structure overlying the body of the mastoid, removing a predetermined area of bone down to the antrum cell of the mastoid, implanting the device in the cavity formed, and then closing the incision. The device has a portion which extends into the middle ear space.

Description

United States Patent [72] Inventor Jack Lawrence Mahoney Carmel, Calif. (90] Pacific St., Monterey, Calif., 93940) [21] Appl. No. 663,603
Filed Aug. 28, 1967 Division of 338,858, Dec. 27, 1963, Patent No. 3,346,704. [45] Patented Jan. 26, 1971 [54] METHOD OF IMPLANTING A HEARING AID 5 Claims, 3 Drawing Figs.
[52] U.S.Cl 128/1, 179/107 [51] Int. Cl A6lf 11/04, H04r 25/00 [50] Field of Search 128/1,2,
2.1; 179/l07(all); 181/23 [56] References Cited UNITED STATES PATENTS 2,641,328 6/1953 Beaudry 181/23 2,967,913 [/1961 Aubert et al 179/107(E) 3,170,046 2/1965 Leale 179/107(E) 2,611,829 9/1952 Hazard 179/107(BC) 3,209,081 9/1965 Ducote et a1. 179/107(BC) Primary Examiner-Richard C. Pinkham Assistant Examiner-Paul E. Shapiro Att0rneylsler and Qmstein ABSTRACT: A method is described of implanting a hearing improvement device within the human body, in which a postauricular incision is made in the skin of the anatomical area behind the auricular appendage of the external ear, to thereby expose the bony structure overlying the body of the mastoid, removing a predetermined area of bone down to the antrum cell of the mastoid, implanting the device in the cavity formed, and then closing the incision. The device has a portion which extends into the middle ear space.
PATENTEDJANZBIQYI 3557.775
SHEET 1 [IF 2 JMCROPHONE TUBE -AMPLIFIER UNIT INVENTOR.
JACK L. MAHONEY LLC H ATTORNEYS PATENIEflJAnzslsn I $557,775
SHEET 2 OF 2 SKIN (POSTERIOR TO AURICLE) MICROPHONE TUBE (ll) AMPLIFIER UNIT (IOI SPEAKER TUBE (IZI MIDDLE EAR CAVITY ROUND WINDOW DUCT TO COCHLEA I NVEN TOR.
F/'g 3 JACK L. mmousv M ram ATTORNEYS METHOD OF IMPLANTING AHEARING AID This application is a division of my copending application, Ser. No. 333,858, filed Dec. 27, 1963, for MEANS FOR AID- ING HEARING and since matured into Pat. No. 3,364,704.
This invention relates generally to a method of implanting a hearing aid in the human body, but has reference more particularly to a method in which the hearing aid is so implanted as to be completely enclosed within the head of the individual utilizing the hearing aid.
Hearing aids which are presently available on the market are usually worn outside of the body, and are therefore objectionable from an esthetic, cosmetic or functional viewpoint.
Although attempts have been made to utilize such hearing aids in a manner to conceal them from view, as, for example, within the temples of spectacles, it is'virtually impossible to conceal certain portions of the hearing aid, such as wires, etc., and fort for this reason, many persons whose hearing facilities can be improved do not avail themselves of such aids.
The present invention has as its primary object the provision of a method whereby an audio implant in the nature of a miniaturized system for amplifying sound, is placed directly in the structure of the ear and utilizes the impaired or-damaged, but still functioning, normal channels for transmission of sound to the brain.
Another object of the invention is to provide a method wherein an implant of the character described, is disposed in its entirety within the head structure of the user, and is entirely concealed from view, thereby eliminating any and all objections to its use from an esthetic or cosmetic point of view.
A further object of the invention is to provide a method wherein the implant utilizes a battery which is enclosed within the head structure.
Other objects and advantages of the invention willbecome apparent in the course of the following'description, taken in conjunction with the accompanying drawings wherein:
FIG. I is a vertical cross-sectional view of aportion of a human head taken through theright side of the head. and
passing through the mastoid antrum and middle ear in a plane parallel to a plane passing through the nose and the back of the head, and showing the components of the audio implant of the present invention in'position;
FIG. 2 is a fragmentary elevational view showing a portion of the right side of the head, and with theexternal ear pulled forwardly to show or indicate where the implant and microphone tube are placed; and
FIG. 3 is a tabulation of the means utilizing the implantiof the present invention, whereby sound is transmitted tothe temporal lobe of the brain, where the sound is heard.
Referring more particularly to the drawings,-an understand ing of FIG. 1 can be gained if the observer can imagine he is inside the head of the person depicted in FIG. '1, and is looking outwardly and through the right ear.
The observer will see the auditory canal l, thetympanic membrane 2, the malleus 3, theincus 4. and themastoid antrum 5. The tip of the mastoid is' indicated by reference numeral 6, the chorda tympani by reference numeral 7, a facial nerve by reference numeral 8 and thesquama by reference numeral 9.
Normal hearing in an individual is accomplished by the help i of the external car, which concentrates'thesonorous vibrations of the air upon the tympanic membrane,--causing the latter to vibrate. The chain of bones in the middleeannamely the malleus, incus and stapes, transmitsthese vibrations to the internal ear, where, wholly or chiefly through the hair cells in t the organ of corti, they stimulate the fibers of theauditory nerve, which then carries the sound impulses to the temporal lobe of the brain.
In accordance with my invention, I provide axhearing improvement device which Iterm an audio implant," and which consists of several components, including mainly a microphone, a battery, an amplifying system and a speaker,
such as are found in a conventional hearing aidhThese-components are encased in a silicone rubber sponge. with a hardened coat of silicone rubber to form a unit, designated by reference numeral 10 in FIGS. 1 and 2.
The unit 10 is rectangular in shape, measuring approximately l cm. X l c'm., and a few millimeters in thickness, and is provided with a silicone rubber tube 11 extending centrally from one en'd'of the unit 10, and a similar tube '12 extending centrally from one side of the unit 10. The tubes 11 and 12 are approximately IV: cm. in length, and approximately 2 mm. in diameter. The tube 11, which I term the microphone tube, is attached to the microphone within the unit 10, and both ends of the tube are sealed with a very thin membrane of silicone rubber. The tube 12, which I term the speaker tube, is attached to the speaker within the unit 10, and both ends of this tube are sealed with a very thin membrane of silicone rubber.
When the device is to be implanted, a postauricular incision is made adjacent the auricular appendage of the external ear, in the skin of the anatomical area of the ear. This incision is approximately three centimeters in length, and is carried out under local anesthesia. The bony structure overlying the body of the mastoid is exposed, and an area of bone, i.e., an area of approximately 2 square centimeters, is removed down to the antrum cell of the mastoid. A few of the air cells of the mastoid are then removed to enlarge the antrum cell to accommodate the unit 10.
The unit 10 is then placed directly into this space in the manner shown in FIG. I, and the speaker tube 12 is then placed in a passageway which extends from the antrum cell of the mastoid into the middle'ear space behind the ear drum. More specifically, the speaker tube is brought up through a small opening near the introitus of the ear canal, and to a point closely adjacent to what is commonly referred to as the ""round window The wave motion is transmitted to the cochlea, which startsthe electrical impulses to the temporal lobe'of the brain.
The microphone'tube '11 is then extended externally from -"the'ant'rum cell of the mastoid and is covered with skin and i will be disposed just beneath the skin behind the ear. The incision is th'en closed, and the ear again completely sealed. Since the'skin inc'isio'nis made in a hidden area adjacent the car, no noticeable scar will be produced, after healing.
Referring to FIG. 3 of the drawing, it is seen that through theuseof the hearingaid of this invention, sound vibrations aretransmit'ted through the skin, posterior to the auricle, hence to themicrophone tube 11, amplifier unit 10, speaker tube 12,-middle ear cavity, round window, and duct to choclea, thence in the normal manner to the temporal lobe of the brain.
'I'he'batterywithin the unit l0 is preferably a silver-cadmium battery'and'ca'n becharged by a magnetic induction coil which is attaehedto a head-band, which can be worn on the head while sleeping, or at anyother time which is convenient. The induction coil is connected to a wire which leads to a transistorized charging'unit'which is energized from a conventional electrical outlet'ln charging the battery, the induction coil'onthehead'band' is placed directly over the main structure of the mastoid.
The implant' will function for approximately eight days before it becomes necessary to recharge such a battery with the magnetic induction coilf'Recharging of the battery requires approximately 6 hours.
One of theadvant'ages of the use of such an implant is that it is embeddedsolidly in the bone of the skull, and is so situated that it'c'an' drive' the sound directly into the inner car, without the necessity" of driving the's'ound'through the'tympanic mem brane, which offers considerable resistance to transmission of sound in cases of conductive deafness where the oval window and'stapesarefused by abnormal bone closure called otosclerosis.
Another advantage is that there are no parts which are disposed-externally of the head'or are'visible, so' that objec tions to use ofthe device, based on psychological factors, and cosmet'i'c'view'points'are eliminated.
A further advantage lies in the fact that the replacement batteries, and itsattendant costs, are eliminated.
A still further advantage resides in the elimination of the rushing andclothing noise which is a constant source of annoyance to individuals from movement across the microphones of hearing aids which are carried about the body.
The device is also of particular advantage for children who require the use of a hearing aid to hear sufficiently to carry on their school work, while finding it necessary to remove these aids during play and physical activity since external hearing aids and devices are easily dislodged or broken during such play or physical activity.
It is thus seen that l have provided a means of aiding hearing of individuals whose hearing is. not remediable medically or surgically, but who require amplification of sound for hearing.
it is also seen that l have provided an audio implant in the nature of a miniaturized system for amplifying sound, which is placed directly in the structure of the ear and utilizes the impaired or damaged, but still functional, normal channels for transmission of sound to the brain.
It is'further seen that l have provided an implant which is disposed in its entirety within the head structure of the user, and is entirely concealed from view, thereby eliminating any and all objections to its use from an esthetic or cosmetic point of view.
It will be understood that various changes may be made in the details of the invention, as described, without departing from the spirit of the invention, or the scope of the appended claims.
Iclaim:
l. The method of implanting a self-contained hearing improvement device within the human body, in which said device contains a microphone, a battery, an amplifying system, which is neutral to the adjacent portions of the body, a microphone tube extending from the microphone in said unit; a speaker and a speaker tube extending therefrom including the steps of making an incision adjacent the auricular appendage of the external ear, in the skin'of the anotomical area of the ear, exposing the bony structure overlying the body of the mastoid, removing a predetermined area of bone down to the antrum cell of the mastoid, implanting the self-contained hearing improvement device in said antrum cell, situating an outer end of the microphone tube into position and adjacent the skin behind the auricular appendage and situating an outer end of said speaker tube into the middle ear space behind the ear drum through the antrum-inner ear passage; and thereafter closing the incision.
2. The method of implanting in the human body a hearing improvement device including signal-receiving means for receiving an incoming signal representative of a sound wave existing outside of the human body, intermediate means for converting said incoming signal to an audiofrequency electrical signal, output means including electrical-mechanical transducer means to generate mechanical motion from said electrical signal, an operative connection between said signal-receiving means, said intermediate means and between said intermediate means and said output means, said method comprising the steps of.making an incision in the skin in the auricular area of the ear adjacent the auricular appendage of the external ear; exposing the bony structure overlying the body of the mastoid; removing an area of bony structure to expose the an trum cell cavity; positioning said hearing improvement device within said cavity and with at least part of said output means in the middle ear space to deliver said generated mechanical motion directly thereinto; and then closing the incision.
3. The method specified in claim 2 and the step'of removing sufficient air cells of the mastoid to enlarge the antrum cell cavity to accommodate the implanting of said hearing improvement device, said step being performed before the step of positioning said output means.
4. The method of implanting a hearing improvement device in a human body, said device including signal-receiving means for receiving an incoming signal representative of a sound wave existing outside of said human body, intermediate means for converting said incoming signal to an audiofrequency electrical signal, output means including electrical-mechanical transducer means adapted to generate mechanical motion from the electrical signal, and operative connections from said signal-receiving means to said intermediate means and from the intermediate means to the output means; said method comprising the steps of surgically positioning at least a portion of said output means within the human body in the middle ear space at the round window to permit said generated mechanical motion to pass from said output means directly to the middle ear space behind the area of the tympanic membrane; concurrently positioning said signal-receiving means within the human body in position to receive said incoming signal; and further, surgically positioning said intermediate means within the human body at a locus removed from the middle ear space but adjacent the area of the auricular appendage of the ear and in operative relationship to said signal-receiving means and said output means.
5. The method of implanting a hearing improvement device within the human body, said method comprising the steps of: making an incision adjacent the auricular appendage of the external ear in the skin of the anatomical area of the ear; exposing the bony structure overlying the body of the mastoid; removing a predetermined area of bone down to the antrum cell of the mastoid; implanting a hearing improvement device in the cavity formed by the bone removal and mastoid antrum cell with at least a portion of the device extending into the middle ear space; and closing the incision.

Claims (5)

1. The method of implanting a self-contained hearing improvement device within the human body, in which said device contains a microphone, a battery, an amplifying system, which is neutral to the adjacent portions of the body, a microphone tube extending from the microphone in said unit; a speaker and a speaker tube extending therefrom including the steps of making an incision adjacent the auricular appendage of the external ear, in the skin of the anotomical area of the ear, exposing the bony structure overlying the body of the mastoid, removing a predetermined area of bone down to the antrum cell of the mastoid, implanting the self-contained hearing improvement device in said antrum cell, situating an outer end of the microphone tube into position and adjacent the skin behind the auricular appendage and situating an outer end of said speaker tube into the middle ear space behind the ear drum through the antrum-inner ear passage; and thereafter closing the incision.
2. The method Of implanting in the human body a hearing improvement device including signal-receiving means for receiving an incoming signal representative of a sound wave existing outside of the human body, intermediate means for converting said incoming signal to an audiofrequency electrical signal, output means including electrical-mechanical transducer means to generate mechanical motion from said electrical signal, an operative connection between said signal-receiving means, said intermediate means and between said intermediate means and said output means, said method comprising the steps of making an incision in the skin in the auricular area of the ear adjacent the auricular appendage of the external ear; exposing the bony structure overlying the body of the mastoid; removing an area of bony structure to expose the antrum cell cavity; positioning said hearing improvement device within said cavity and with at least part of said output means in the middle ear space to deliver said generated mechanical motion directly thereinto; and then closing the incision.
3. The method specified in claim 2 and the step of removing sufficient air cells of the mastoid to enlarge the antrum cell cavity to accommodate the implanting of said hearing improvement device, said step being performed before the step of positioning said output means.
4. The method of implanting a hearing improvement device in a human body, said device including signal-receiving means for receiving an incoming signal representative of a sound wave existing outside of said human body, intermediate means for converting said incoming signal to an audiofrequency electrical signal, output means including electrical-mechanical transducer means adapted to generate mechanical motion from the electrical signal, and operative connections from said signal-receiving means to said intermediate means and from the intermediate means to the output means; said method comprising the steps of surgically positioning at least a portion of said output means within the human body in the middle ear space at the round window to permit said generated mechanical motion to pass from said output means directly to the middle ear space behind the area of the tympanic membrane; concurrently positioning said signal-receiving means within the human body in position to receive said incoming signal; and further, surgically positioning said intermediate means within the human body at a locus removed from the middle ear space but adjacent the area of the auricular appendage of the ear and in operative relationship to said signal-receiving means and said output means.
5. The method of implanting a hearing improvement device within the human body, said method comprising the steps of: making an incision adjacent the auricular appendage of the external ear in the skin of the anatomical area of the ear; exposing the bony structure overlying the body of the mastoid; removing a predetermined area of bone down to the antrum cell of the mastoid; implanting a hearing improvement device in the cavity formed by the bone removal and mastoid antrum cell with at least a portion of the device extending into the middle ear space; and closing the incision.
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Cited By (52)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4352960A (en) * 1980-09-30 1982-10-05 Baptist Medical Center Of Oklahoma, Inc. Magnetic transcutaneous mount for external device of an associated implant
US4706682A (en) * 1985-08-21 1987-11-17 Minnesota Mining And Manufacturing Company External ear canal electrode to be placed proximate the tympanic membrane
US4729366A (en) * 1984-12-04 1988-03-08 Medical Devices Group, Inc. Implantable hearing aid and method of improving hearing
USRE32947E (en) * 1980-09-30 1989-06-13 Baptist Medical Center Of Oklahoma, Inc. Magnetic transcutaneous mount for external device of an associated implant
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
US4944301A (en) * 1988-06-16 1990-07-31 Cochlear Corporation Method for determining absolute current density through an implanted electrode
WO1991012783A1 (en) * 1990-03-02 1991-09-05 Roger Tari Heraing assistance device comprising a self-contained direct bone conduction hearing aid implant
US5239588A (en) * 1988-12-21 1993-08-24 Davis Murray A Hearing aid
US5390254A (en) * 1991-01-17 1995-02-14 Adelman; Roger A. Hearing apparatus
US5430801A (en) * 1993-12-14 1995-07-04 Hill; Frank C. Hearing aid
US5707338A (en) * 1996-08-07 1998-01-13 St. Croix Medical, Inc. Stapes vibrator
EP0831673A2 (en) * 1996-09-18 1998-03-25 IMPLEX GmbH Spezialhörgeräte Implantable microphone
US5762583A (en) * 1996-08-07 1998-06-09 St. Croix Medical, Inc. Piezoelectric film transducer
US5772575A (en) * 1995-09-22 1998-06-30 S. George Lesinski Implantable hearing aid
US5814095A (en) * 1996-09-18 1998-09-29 Implex Gmbh Spezialhorgerate Implantable microphone and implantable hearing aids utilizing same
US5836863A (en) * 1996-08-07 1998-11-17 St. Croix Medical, Inc. Hearing aid transducer support
US5842967A (en) * 1996-08-07 1998-12-01 St. Croix Medical, Inc. Contactless transducer stimulation and sensing of ossicular chain
US5881158A (en) * 1996-05-24 1999-03-09 United States Surgical Corporation Microphones for an implantable hearing aid
US5879283A (en) * 1996-08-07 1999-03-09 St. Croix Medical, Inc. Implantable hearing system having multiple transducers
US5951601A (en) * 1996-03-25 1999-09-14 Lesinski; S. George Attaching an implantable hearing aid microactuator
US5954628A (en) * 1997-08-07 1999-09-21 St. Croix Medical, Inc. Capacitive input transducers for middle ear sensing
US5977689A (en) * 1996-07-19 1999-11-02 Neukermans; Armand P. Biocompatible, implantable hearing aid microactuator
US5984859A (en) * 1993-01-25 1999-11-16 Lesinski; S. George Implantable auditory system components and system
US5997466A (en) * 1996-08-07 1999-12-07 St. Croix Medical, Inc. Implantable hearing system having multiple transducers
US6001129A (en) * 1996-08-07 1999-12-14 St. Croix Medical, Inc. Hearing aid transducer support
US6005955A (en) * 1996-08-07 1999-12-21 St. Croix Medical, Inc. Middle ear transducer
US6010532A (en) * 1996-11-25 2000-01-04 St. Croix Medical, Inc. Dual path implantable hearing assistance device
US6171229B1 (en) 1996-08-07 2001-01-09 St. Croix Medical, Inc. Ossicular transducer attachment for an implantable hearing device
US6198971B1 (en) 1999-04-08 2001-03-06 Implex Aktiengesellschaft Hearing Technology Implantable system for rehabilitation of a hearing disorder
US6214046B1 (en) 1996-11-25 2001-04-10 St. Croix Medical, Inc. Method of implanting an implantable hearing assistance device with remote electronics unit
US6261224B1 (en) 1996-08-07 2001-07-17 St. Croix Medical, Inc. Piezoelectric film transducer for cochlear prosthetic
US6264603B1 (en) 1997-08-07 2001-07-24 St. Croix Medical, Inc. Middle ear vibration sensor using multiple transducers
US6315710B1 (en) 1997-07-21 2001-11-13 St. Croix Medical, Inc. Hearing system with middle ear transducer mount
US20020012438A1 (en) * 2000-06-30 2002-01-31 Hans Leysieffer System for rehabilitation of a hearing disorder
US20020051550A1 (en) * 2000-08-25 2002-05-02 Hans Leysieffer Implantable hermetically sealed housing for an implantable medical device and process for producing the same
US6387039B1 (en) * 2000-02-04 2002-05-14 Ron L. Moses Implantable hearing aid
US6516228B1 (en) 2000-02-07 2003-02-04 Epic Biosonics Inc. Implantable microphone for use with a hearing aid or cochlear prosthesis
US6537200B2 (en) 2000-03-28 2003-03-25 Cochlear Limited Partially or fully implantable hearing system
US20030063764A1 (en) * 2001-10-03 2003-04-03 Maltan Albert A. Personal sound link module
US6565503B2 (en) 2000-04-13 2003-05-20 Cochlear Limited At least partially implantable system for rehabilitation of hearing disorder
US6575894B2 (en) 2000-04-13 2003-06-10 Cochlear Limited At least partially implantable system for rehabilitation of a hearing disorder
US6629923B2 (en) 2000-09-21 2003-10-07 Phonak Ag At least partially implantable hearing system with direct mechanical stimulation of a lymphatic space of the inner ear
US6689045B2 (en) 1998-09-24 2004-02-10 St. Croix Medical, Inc. Method and apparatus for improving signal quality in implantable hearing systems
US6697674B2 (en) 2000-04-13 2004-02-24 Cochlear Limited At least partially implantable system for rehabilitation of a hearing disorder
US6730015B2 (en) 2001-06-01 2004-05-04 Mike Schugt Flexible transducer supports
US6736770B2 (en) 2000-08-25 2004-05-18 Cochlear Limited Implantable medical device comprising an hermetically sealed housing
US20040133066A1 (en) * 2001-10-03 2004-07-08 Mann Alfred E. Implanted outer ear canal hearing aid
US6786860B2 (en) 2001-10-03 2004-09-07 Advanced Bionics Corporation Hearing aid design
US20050203557A1 (en) * 2001-10-30 2005-09-15 Lesinski S. G. Implantation method for a hearing aid microactuator implanted into the cochlea
US20180063658A1 (en) * 2016-08-31 2018-03-01 Marcus ANDERSSON Intracutaneous implantation techniques
US10319963B2 (en) * 2013-06-12 2019-06-11 Shinko Electric Industries Co., Ltd. Battery and method for producing the same

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Cited By (73)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4352960A (en) * 1980-09-30 1982-10-05 Baptist Medical Center Of Oklahoma, Inc. Magnetic transcutaneous mount for external device of an associated implant
USRE32947E (en) * 1980-09-30 1989-06-13 Baptist Medical Center Of Oklahoma, Inc. Magnetic transcutaneous mount for external device of an associated implant
US4729366A (en) * 1984-12-04 1988-03-08 Medical Devices Group, Inc. Implantable hearing aid and method of improving hearing
US4850962A (en) * 1984-12-04 1989-07-25 Medical Devices Group, Inc. Implantable hearing aid and method of improving hearing
US4706682A (en) * 1985-08-21 1987-11-17 Minnesota Mining And Manufacturing Company External ear canal electrode to be placed proximate the tympanic membrane
WO1989005559A1 (en) * 1987-12-04 1989-06-15 Claus Jansen Electroacoustic transducer
US4944301A (en) * 1988-06-16 1990-07-31 Cochlear Corporation Method for determining absolute current density through an implanted electrode
US5239588A (en) * 1988-12-21 1993-08-24 Davis Murray A Hearing aid
WO1991012783A1 (en) * 1990-03-02 1991-09-05 Roger Tari Heraing assistance device comprising a self-contained direct bone conduction hearing aid implant
FR2659009A1 (en) * 1990-03-02 1991-09-06 Tari Roger HEARING AID DEVICE COMPRISING AN IMPLANTED AND AUTONOMOUS HEARING AID WITH DIRECT BONE CONDUCTION.
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
US5984859A (en) * 1993-01-25 1999-11-16 Lesinski; S. George Implantable auditory system components and system
US5430801A (en) * 1993-12-14 1995-07-04 Hill; Frank C. Hearing aid
US5772575A (en) * 1995-09-22 1998-06-30 S. George Lesinski Implantable hearing aid
US5951601A (en) * 1996-03-25 1999-09-14 Lesinski; S. George Attaching an implantable hearing aid microactuator
US5881158A (en) * 1996-05-24 1999-03-09 United States Surgical Corporation Microphones for an implantable hearing aid
US6153966A (en) * 1996-07-19 2000-11-28 Neukermans; Armand P. Biocompatible, implantable hearing aid microactuator
US5977689A (en) * 1996-07-19 1999-11-02 Neukermans; Armand P. Biocompatible, implantable hearing aid microactuator
US5842967A (en) * 1996-08-07 1998-12-01 St. Croix Medical, Inc. Contactless transducer stimulation and sensing of ossicular chain
US6001129A (en) * 1996-08-07 1999-12-14 St. Croix Medical, Inc. Hearing aid transducer support
US6261224B1 (en) 1996-08-07 2001-07-17 St. Croix Medical, Inc. Piezoelectric film transducer for cochlear prosthetic
US6488616B1 (en) 1996-08-07 2002-12-03 St. Croix Medical, Inc. Hearing aid transducer support
US5836863A (en) * 1996-08-07 1998-11-17 St. Croix Medical, Inc. Hearing aid transducer support
US5707338A (en) * 1996-08-07 1998-01-13 St. Croix Medical, Inc. Stapes vibrator
US5997466A (en) * 1996-08-07 1999-12-07 St. Croix Medical, Inc. Implantable hearing system having multiple transducers
US5879283A (en) * 1996-08-07 1999-03-09 St. Croix Medical, Inc. Implantable hearing system having multiple transducers
US6005955A (en) * 1996-08-07 1999-12-21 St. Croix Medical, Inc. Middle ear transducer
US20040181117A1 (en) * 1996-08-07 2004-09-16 Adams Theodore P. Piezoelectric film transducer
US6171229B1 (en) 1996-08-07 2001-01-09 St. Croix Medical, Inc. Ossicular transducer attachment for an implantable hearing device
US6050933A (en) * 1996-08-07 2000-04-18 St. Croix Medical, Inc. Hearing aid transducer support
US5762583A (en) * 1996-08-07 1998-06-09 St. Croix Medical, Inc. Piezoelectric film transducer
US5814095A (en) * 1996-09-18 1998-09-29 Implex Gmbh Spezialhorgerate Implantable microphone and implantable hearing aids utilizing same
EP0831673A3 (en) * 1996-09-18 2006-08-09 Phonak Ag Implantable microphone
EP0831673A2 (en) * 1996-09-18 1998-03-25 IMPLEX GmbH Spezialhörgeräte Implantable microphone
US6235056B1 (en) 1996-11-25 2001-05-22 St. Croix Medical, Inc. Implantable hearing assistance device with remote electronics unit
US6214046B1 (en) 1996-11-25 2001-04-10 St. Croix Medical, Inc. Method of implanting an implantable hearing assistance device with remote electronics unit
US6491722B1 (en) 1996-11-25 2002-12-10 St. Croix Medical, Inc. Dual path implantable hearing assistance device
US6010532A (en) * 1996-11-25 2000-01-04 St. Croix Medical, Inc. Dual path implantable hearing assistance device
US6315710B1 (en) 1997-07-21 2001-11-13 St. Croix Medical, Inc. Hearing system with middle ear transducer mount
US6264603B1 (en) 1997-08-07 2001-07-24 St. Croix Medical, Inc. Middle ear vibration sensor using multiple transducers
US5954628A (en) * 1997-08-07 1999-09-21 St. Croix Medical, Inc. Capacitive input transducers for middle ear sensing
US6689045B2 (en) 1998-09-24 2004-02-10 St. Croix Medical, Inc. Method and apparatus for improving signal quality in implantable hearing systems
US6198971B1 (en) 1999-04-08 2001-03-06 Implex Aktiengesellschaft Hearing Technology Implantable system for rehabilitation of a hearing disorder
US6387039B1 (en) * 2000-02-04 2002-05-14 Ron L. Moses Implantable hearing aid
US6516228B1 (en) 2000-02-07 2003-02-04 Epic Biosonics Inc. Implantable microphone for use with a hearing aid or cochlear prosthesis
US6537200B2 (en) 2000-03-28 2003-03-25 Cochlear Limited Partially or fully implantable hearing system
US6697674B2 (en) 2000-04-13 2004-02-24 Cochlear Limited At least partially implantable system for rehabilitation of a hearing disorder
US6575894B2 (en) 2000-04-13 2003-06-10 Cochlear Limited At least partially implantable system for rehabilitation of a hearing disorder
US6565503B2 (en) 2000-04-13 2003-05-20 Cochlear Limited At least partially implantable system for rehabilitation of hearing disorder
US20040172102A1 (en) * 2000-04-13 2004-09-02 Cochlear Limited At least partially implantable system for rehabilitation of a hearing disorder
US7376563B2 (en) 2000-06-30 2008-05-20 Cochlear Limited System for rehabilitation of a hearing disorder
US20020012438A1 (en) * 2000-06-30 2002-01-31 Hans Leysieffer System for rehabilitation of a hearing disorder
US6736770B2 (en) 2000-08-25 2004-05-18 Cochlear Limited Implantable medical device comprising an hermetically sealed housing
US20020051550A1 (en) * 2000-08-25 2002-05-02 Hans Leysieffer Implantable hermetically sealed housing for an implantable medical device and process for producing the same
US6629923B2 (en) 2000-09-21 2003-10-07 Phonak Ag At least partially implantable hearing system with direct mechanical stimulation of a lymphatic space of the inner ear
US6730015B2 (en) 2001-06-01 2004-05-04 Mike Schugt Flexible transducer supports
US20040133066A1 (en) * 2001-10-03 2004-07-08 Mann Alfred E. Implanted outer ear canal hearing aid
US7853033B2 (en) * 2001-10-03 2010-12-14 Advanced Bionics, Llc Hearing aid design
US6879695B2 (en) 2001-10-03 2005-04-12 Advanced Bionics Corporation Personal sound link module
US20050157896A1 (en) * 2001-10-03 2005-07-21 Maltan Albert A. Hollow tube enclosing an implantable personal sound link module
US20050031145A1 (en) * 2001-10-03 2005-02-10 Maltan Albert A. Novel hearing aid design
US6786860B2 (en) 2001-10-03 2004-09-07 Advanced Bionics Corporation Hearing aid design
US7127078B2 (en) 2001-10-03 2006-10-24 Advanced Bionics Corporation Implanted outer ear canal hearing aid
US7224815B2 (en) 2001-10-03 2007-05-29 Advanced Bionics Corporation Hearing aid design
US20070217640A1 (en) * 2001-10-03 2007-09-20 Advanced Bionics Corporation Hearing Aid Design
US20030063764A1 (en) * 2001-10-03 2003-04-03 Maltan Albert A. Personal sound link module
US20050203557A1 (en) * 2001-10-30 2005-09-15 Lesinski S. G. Implantation method for a hearing aid microactuator implanted into the cochlea
US8147544B2 (en) 2001-10-30 2012-04-03 Otokinetics Inc. Therapeutic appliance for cochlea
US8876689B2 (en) 2001-10-30 2014-11-04 Otokinetics Inc. Hearing aid microactuator
US10319963B2 (en) * 2013-06-12 2019-06-11 Shinko Electric Industries Co., Ltd. Battery and method for producing the same
US20180063658A1 (en) * 2016-08-31 2018-03-01 Marcus ANDERSSON Intracutaneous implantation techniques
US11943588B2 (en) * 2016-08-31 2024-03-26 Cochlear Limited Intracutaneous implantation techniques

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