US3764748A - Implanted hearing aids - Google Patents

Abstract

Several hearing aid configurations for implantation within the middle ear cavity are disclosed. Each hearing aid is minute in size and is joined in operative relationship interiorly of the ear drum to the ossicle bone chain situated within the middle ear cavity. Each hearing aid is characterized by: (1) picking up or ''''reading'''' auditory signals off the ear drum, (2) subsequently amplifying and/or transmitting such signals directly to appropriate sound receiving mechanisms, natural or solid-state or both, located on the oval window, the round window, or the promontory leading into the inner ear, and (3) relying upon the automatic gain control (AGC) function performed by the tensors and flexors of the ossicle bone chain to prevent loud sounds from damaging the ear drum.

Description

waited States Patent [19] Branch et al.

[ 4] IMPLANTED HEARING AIDS [76] Inventors: Jack P. Branch, PO. Box 17435,

Memphis, Tenn. 381 17; Noel 0. Durham, Charlotte, NC.

[22] Filed: May 19, 1972 [21] Appl. No.: 254,930

Primary Examiner-Ralph D. Blakeslee Att0rneyEric P. Schellin et al.

[57] ABSTRACT Several hearing aid configurations for implantation within the middle ear cavity are disclosed. Each hearing aid is minute in size and is joined in operative relationship interiorly of the ear drum to the ossicle bone chain situated within the middle ear cavity. Each hearing aid is characterized by: l) picking up or reading auditory signals off the ear drum, (2) subsequently amplifying and/or transmitting such signals directly to appropriate sound receiving mechanisms, natural or solid-state or both, located on the oval window, the round window, or the promontory leading into the inner ear, and (3) relying upon the automatic gain control (AGC) function performed by the tensors and flexors of the ossicle bone chain to prevent loud sounds from damaging the ear drum.

26 Claims, 22 Drawing Figures Patented Oct. 9, 1973 6 Sheets-Sheet 1 F/G. lA.

Patented Oct. 9, 1973 3,764,748

6 Sheets-Sheet :3

Patented Oct. 9, 1973 3,764,74g

Patented Oct. 9, 1973 6 Sheets-Sheet 4 F/GZ MIDDLE EAR OUTER EAR AREA A. 240;; AUDIO AMPLIFIER CIRCUIT CONTROL LIGHT LIGHT EMITTING DEVICE BATTERY/ Patented Oct. 9, 1973 6 Sheets-Sheet L IMPLANTED HEARING AIDS BACKGROUND OF THEINVENTION 1. Field of the Invention The instant invention relates to surgically implantable hearing aids for stimulating the auditory system of the human body.

2. Description of the Prior Art In recent years the medical arts have been, to a large extent, directed to surgical means for the correction of human bodily defects, i.e., those defects which occur in the human body due to injury, congenital malfunction, or the like. Thus, for example, there have been disclosed in the medical arts a variety of elements capable of implantation within the human body. These elemerits in many instances comprise transplanted human organs. In many other instances, they comprise artificial members or prosthetic devices, such as, artificial hearts, heart valves, artificial kidneys, artificial limbs, and the like.

The population of the United States, as of the date of this invention, is approximately 210,000,000 people. Of such number, approximately percent over 30,000,000 persons, have some form of inability to adequately perceive auditory information by means of their auditory sensory powers.

These forms of inability may be classified as follows: first, a conductive loss; secondly, a nerve loss; thirdly, a mixed type loss including body nerve and conductive losses; and fourthly, a psychogenic loss.

A conductive loss usually is attributable to excessive calcium or cartilaginous deposits on the joints on the ossicle bone chain of the middle ear. These deposits restrain movement of the conductive bone chain, and in most instances, also restrict movement of the ovular window leading to the inner ear. Other conductive losses may be caused by damage to the ear drum or tympanum through subjection to concussion, extreme atmospheric pressure, or the like. Additionally, the ossicle bone chain may be eroded by chronic infection, congenital conditions, or the like.

Nerve loss is the most common type of hearing inability. Such loss may be attributable to deterioration of the auditory nerves through heredity, disease, noise damage or the like.

The third type of hearing inability, designated above as mixed nerve-conductive loss, includes those instances in which an individual has present in his auditory system a combination of the losses described above.

Referring again to condition one, the conductive loss, there are cases wherein the ear drum is eroded, ruptured, or otherwise impaired, and/or the bone movement is restricted through hardening and malfunction. Thus, in effect, the auditory signals received are reduced in intensity due to this loss of transmission effectiveness. Therefore, the necessary threshold level of desirable signals which must be transmitted to the brain by means of the auditory nerves is not achieved. Consequently, the signals perceived by the brain are inadequate to allow the brain to translate such signals into intelligible information.

Referring again to condition two, the nerve loss, it should be understood that such nerve damage may occur when fibers of the auditory nerves are damaged through disease or hereditary congenital defects. The cochlea within the inner ear functions as a receiving mechanism similar to piano keyboard. When the cochlea or any other portion of the auditory nervous system is damaged, only a portion of the auditory energy which is received thereby is transmitted to the brain. These losses occur particularly in the upper end of the range of audible sounds, because of subjection to industrial noises, jet noises, explosions, atrophy age or the like.

Certain infectious conditions, such as scarlet fever, measles, sinusitis, or the like, are also known as common causes of the three above noted types of auditory losses.

A fourth type of loss, generally designated as psychogenic, usually occurs when there is a loss in energy transmission due to a mental blockage.

While the present invention is primarily directed to the correction of the first three hearing loss conditions described above, it will be understood that there may be instances in which the fourth condition may be corrected or alleviated by the insettion or implantation of the present devices.

Each of the above described conditions may be caused by congenital defects occurring within the human body, these defects usually being apparent within two and one-half decades from the birth of the individual, and at that time, generally perceivable by skilled examination.

The prior art has disclosed various means for aiding in the correction of the above-identified and described auditory defects. These corrective devices have fallen into three basic categories. First, those devices which mechanically direct to the human ear, by means of filtration or the like, that portion of received auditory oscillations which contain intelligible information. Secondly, those devices which convey to the inner ear, via insertion within the outer ear and ear canal or via bone transmission, electrical and/or mechanical amplification of received auditory signals. Thirdly, corrective or prosthetic devices which are intended to be substituted for various elements of the human auditory system. Broadly speaking, the implanted transducer of the instant invention is a hybrid of the second and third categories of corrective devices.

The ear trumpet is deemed to be representative of the first category of corrective devices, for the trumpet merely funnels the sound received in the outer ear down the ear canal toward the ear drum without mechanically or electrically amplifying such auditory energy.

The majority of the hearing aids or corrective devices utilized today fall within the second category, for such hearing aids rely upon a sound amplifier-transmitter unit carried upon the person, with a wire connecting the transmitter to a receiver unit which is stuck into the outer ear and extends inwardly into the ear canal. With the advent of solid-state electronics, the sound amplifier-transmitter unit has been mounted in eyeglass frames, earrings, necklaces or the like, with a wire connection between the eyeglass frames, earrings, necklace, etc., and the receiver unit inserted within the ear usually through the use of an earmold.

Many persons, however, despite their need for a corrective device to overcome their hearing loss, refuse to wear a hearing aid for esthetic or cosmetic reasons. Other persons cannot tolerate the distortions in tone caused by the transmission between the amplifiertransmitter unit and the receiver unit, in addition to the distracting buzzing sound of the device itself. Furthermore, conventional hearing aids may not provide effective relief for certain persons since their hearing loss may be attributable to auditory problems in the mddle ear and/or inner ear.

Consequently, an alternative type of corrective device of the second category has been evolved. This corrective device relies upon a surgically planted receiver that conducts auditory energy through the bones of the ossicular chain or the bones of the'skull to the inner ear. The speech amplifier-transmitter, which supplies the power to the receiver via remote transmission without interconnecting wires, can be encased in a fountain pen shape, cigarette pack shape, standard hearing aid shape or similar object. Although the bone-conductive type of corrective device does overcome the widespread esthetic or cosmetic objection to the more conventional hearing aid, is has not met with complete accpetance for numerous reasons. United States Pat. Nos. 2,402,392 3,209,081 and 3,346,704, granted to Goldschmidr, Ducote et al., and Mahoney, respectively, disclose illustrative ear implants that rely upon bone conduction to achieve improved hearing.

As previously noted, there has been constantly increasing attention focused upon the utilization of artificial body members or prosthetic devices. Hence, prosthetic stapes of stainless steel, polyethylene, Teflon, platinum or other inert materials that are autoclavable, have been fabricated; for example, see US. Pat. Nos. 3,l9l,l88 and 3,196,462, granted to Mercandino et al., and Robinson, respectively.

Such prosthetic devices, which fall within the third category of corrective devices as outlined above, enable the recipient of such implant to hear in the same fashion as a person with normal hearing ability. Thus, the recipient can distinguish sounds clearly over a wider range of frequencies and with greater fidelity than can be obtained by a hearing aid of the second category for the prosthetic device is operatively associated with the oval window leading into the inner ear.

One of the major drawbacks of such prosthetic stapes, however, is that the hearing loss may be attributable to defects in the malleus, the incus, or the stapes or the oval window area, or any combination of these elements. Accordingly, the implantation of the stapes may have limited success in alleviating hearing losses attributable to diseases of the middle ear. Furthermore, prior prosthetic stapes are merely substitutive in nature and cannot amplify the sound energy received at the inner ear.

More recently, attempts have been made to surgically implant a hearing aid within the body of the person suffering from a hearing loss. For example, US. Pat. No. 3,557,775 granted to Mahoney, discloses the implantation of a microphone tube, amplifier unit and a speaker tube in the antrum cell of the mastoid adjacent to the auricular appendage of the external ear. The unit is powered by a rechargeable battery, and the sound picked up by the microphone is fed into the speaker tube and thence to a point closely adjacent to the round window leading into the inner ear. The wave motion casued in the inner ear is transmitted to the cochlea, which initiates the electrical impulses to the brain which are translated into intelligible sound.

U.S. Pat. No. 3,594,514, granted to Wingrove, also discloses an implantable hearing aid including a piezoelectric ceramic element. One end of the element is implanted in an area of the body that can provide a stable platform, such as the mastoid bone. The opposite end of the element is then placed adjacent one of the ossicle bones in the middle ear or the oval window leading into the inner ear. The piezoelectric crystal bends or vibrates in response to avarying voltage signal delivered thereto over a receiving coil and a related to circuit responsive to varying sound waves. A microphone preferably located externally to the body. picks up sound waves and changes such waves into modulated RF signals through appropriate circuitry. The modulated RF signals are transmitted by a transmitting coil to the above noted receiving coil, and thence to the piezoelectric crystal.

Whereas Mahoney and Wingrove may suggest ways to resolve some of the problems previously encountered in designing hearing aids, both patents pick up sound at a point exterior of the middle ear cavity. Additionally, both patents attempt to substitute electronic components for the sound receiving function normally performed with great accuracy by the ear drum and for the sound transmitting function performed by the ossicle bone chain. Accordingly, whatever sound receiving and transmitting capability still resides in one's auditory system may work at cross-purposes to the electronic implant suggested by Mahoney and Wingrove. The naturally received sound energy may clash with the electronically received and transmitted sound energy to produce distortion, and the automatic gain control provided by the tensors and flexors of the ossicle bone chain is totally overlooked.

SUMMARY In light of the magnitude of the problem of hearing losses and in view of the limited success of prior devices in correcting this problem, the instant invention contemplates numerous configurations of implanted transducers that combine the most desirable features of the seond and third category of corrective devices. More particlarly, the instant invention contemplates a transducer implanted within the middle ear cavity so that it can pick up the sound energy striking the ear drum and can amplify such energy without distortion by causing the ossicle bone chain to mechanically vibrate and transmit such energy to the oval window, round window or promontory leading to the inner ear. Alternatively, in those instances where the ossicle bone chain is damaged, the instant invention contemplates numerous simple methods for reading the vibrations of the ear drum and translating such vibrations into electrical signals for application to the oval window, round window or promontory leading to the inner ear. Furthermore, the instant invention relies upon the natural automatic gain control of the tensors and flexors of the ossicle bone chain to prevent loud sounds from injuring the wearer to the implant, and also utilizes the natural distortion-free transmission of sound through the ossicle bone chain whenever possible.

Furthermore, the instant invention contemplates surgically drilling through the mastoid bone to position the transducer in operative relationship to the bones of the ossicle chain and/or the oval window, round window or promontory leading into the inner ear while minimizing the irritation to the ear drum.

Additionally, the implanted transducer constitutes an all-in-the-ear device and does not require an external, visible interconnection between the amplifiertransmitter and receiver units, thus overcoming the current widespread objection to existing unsightly corrective devices because of cosmetic or esthetic reasons. Furthermore, the implanted hearing aids minimize, if not eliminate, the distortion and buzzing and may be used to treat other diseases of the ear, such as tinnitus.

Also the transducer can be fabricated in sundry shapes and from diverse materials that are pre-selected in accordance with the dimension of the bones within the inner ear of the recipient. Ear molds with appropriate tuning and recharging circuits can be utilized to periodically externally re-tune the implanted hearing aid without resorting to a second operation or surgical procedure. I-Iearing aids utilizing means for converting audio impulses into light are also envisioned. Yet, additional significant advantages of the implanted transducer, and the surgical techniques employed therewith, will become apparent in light of the following description of the invention when construed in conjunction with the accompanying sheets of drawings.

DESCRIPTION OF THE DRAWINGS FIG. 1 is a cross-sectional view of the basic human auditory system;

FIG. 1A is a front elevational view of the osseous labyrinth of the human auditory system;

FIG. 1B is a horizontal cross-sectional view of a fragment of the labyrinth, such view being taken along line 1B-1B in FIG. 1A in the direction indicated;

FIG. 2 shows a preferred embodiment of the hearing aid implanted in operative relationship to the ossicle bone chain within the middle ear cavity, such hearing aid being sound powered and constructed in accordance with the principles of the instant invention;

FIG. 3 shows, on an enlarged scale, details of the hearing aid of FIG. 2;

FIGS. 4, 5, 6, 7 and 8 show five alternative embodiments of the sound powered hearing aid;

FIG. 9 shows a hearing aid comprising a transmitting unit and a receiving unit for delivering an electrical stimulus to the inner ear to assist the natural hearing function;

FIG. 10 shows, in schematic fashion, the remotely situated control circuitry utilized in conjunction with the various embodiments of the hearing aid;

FIG. 11 shows a firt embodiment of the hearing aid utilizing sensing means positioned within the middle ear to read or pick-up the vibrations of the ear drum when sound strikes such member;

FIG. 12 shows a second embodiment ofa hearing aid utilizing magnetically responsive means to read the vibrations of the ear drum;

FIG. 12a is a detaled view of that portion of the embodiment of FIG. 12 that is located within the viewing circle;

FIGS. 13-15 diagrammatically show three alternative sensing circuits that are responsive to the variations in magnetic field transmitted by a magnet affixed to the ear drum in the manner shows in FIG. 12;

FIG. 16 shows a first, or preferred, embodiment, of a hearing aid utilizing light emitting means; and

FIG. 17 shows, in schematic fashion, the control cir- DESCRIPTION OF THE INVENTION Referring now in detail to the drawings in which similar reference numerals refer to similar parts, FIG. 1 depicts the basic structure of the human auditory system, such system being indicated generally byreference numeral 10. It is understood that the following description includes only those basic components of the human auditory system which are essential to hearing. For further reference to the exact details of the human auditory system, reference may be made to any standard text, such as The Physics of the Ear" by T.S. Littler, published in I965 by Pergamon Press, Ltd., of London, England; see particularly pages 1-14.

The human auditory system comprises the outer ear, indicated generally byreference numeral 10, and including an auricle II, anauditory canal 15 extending inwardly toward an ear drum ortympanum 16; a middle ear 12 including therein a malleus 17', an incus I8, and a stapes l9 and aninner ear 13. The bones of the middle ear collectively comprise the energy transmitting bone chain orossicle chain 20. These bones are sometimes, respectively, referred to as thehammer 17, the anvil I8, and thestirrup 15. The stirrup is connected to, in vibratory relation, the ovular window orfenestra 30 of a fluid filledsac 40, known as the labyrinth. Theovular window 30, which is a membrane, separates the middle ear 12 from theinner car 13.

Referring particularly to 1A, it will be appreciated thatovular window 30 forms the entry to the inner car 11, which is enclosed within the labyrinth. Thelabyrinth 40 consists of two parts, the membranous labyrinth and the osseous labyrinth. The membranous labyrinth is a system of interconnected canals and pouches within the osseous labyrinth, or protective casing. Consequently, FIG. 1A depicts the configuration of the osseous labyrinth, whereas FIG. IB illustrates a portion of the membranous labyrinth. The space between the membranous labyrinth and the osseous labyrinth is filled with a water-like fluid known as perilymph. The membranous labyrinth contains another fluid known as endolymph.

Furthermore, as indicated by the appropriate reference numerals in FIG. 1A, the osseous labyrinth is divided into three parts; the vestibule 35, thecochlea 43, and thesemi-circular canals 45. There are three semicircular canals disposed at right angles to another and filled with fluid. These canals regulate the individuals sense of balance and are not directly involved in the hearing process.

The vestibule 35 is the central part of the osseous labyrinth and thecochlea 43 is that porton of the labyrinth concerned specifically with hearing. Thecochlea 43 is snail-shaped and lies horizontally in front of the vestibule 35. Such spacial relationships can be best understood by realizing that FIG. ]IA is a front elevational view of the osseous labyrinth taken on a plane substantially parallel to the plane ofear drum 16 in FIG. I.

As shown by the cut-away section of the cochlea illustrated in FIG. 1B, the membranous cochlea is divided throughout the greater portion of its spiral length into two passages by thebasilar membrane 44. The upper passage of the membranous cochlea terminates atovular window 30 while the lower passage terminates atround window 42, which is a membrane similar toovular window 30. The windows are separated from each other bypromontory 41. Thebasilar member 44 has alarge number of specialized hair cells 44A disposed thereon; these cells collectively form the organ of Corti. These hair cells respond to the sound waves passing through the fluid in the cochlea and transmit such sound waves by way ofacoustic nerves 46 to the brain.

The outer ear or auricle 11 serves as a horn for directing sound vibrations into theauditory canal 15, thus impessing these sound vibrations on the tympanum orcar drum 16. This member converts such vibrations to mechanically transmittable energy via theossicle bone chain 20 thereby transmitting through the midle ear cavity impulses capable of subsequent translation by the brain. As previously noted, that portion of the human auditory apparatus positioned anteriorly, i.e., towards the source of external auditory energy from thetympanum 16, is generally designated as the outer ear 11. The middle ear 12 is operatively connected to the outer ear 11 through the auditory canal l and thetympanum 16. The tympanum serves as the dividing line between the outer car 11 and the middle ear 12.

As explained above, the middle ear l2 incluces a cavity which contains therein the above describedossicle bone chain 20. The bone chain forms a linkage for transmitting sound vibrations from thetympanum 16 to cause mechanical movement for pulsating or vibrating theovular window 30. The stapes is hinged at its upper end at 19a so that the foot plate is pivoted or rockedaganst window 30. In turn,window 30 pulses the fluids in theinner ear 13 to stimulate the organ of Corti and transmit impulses to the brain viaacoustic nerves 46.

Thus, the hearing process can be characterized as a chain reaction involving the following four steps. First, sound vibrations are caught by the external car 11 and passed throughauditory canal 15 to the tympanum orear drum 16. Second, the vibrations oftympanum 16 are conducted byossicle bone chain 20 toovular window 30. Third, movement of window disturbs the perilymph between the membranous labyrinth and the osseous labyrinth, which in turn, disturbs the endolymph within the membranous labyrinth. Lastly, the organ of Corti translates these liquid vibrations into electrical impulses that are transmitted byacoustic nerves 46 to the brain.

Referring now to FIGS. 2-8, it will be appreciated that the instant invention comprises diverse transducers adapted to be implanted or inserted within the human auditory system in operative relationship to the middle ear structure. Obviously, the present invention is intended to be so implanted by simple surgical procedures.

Keeping in mind the above description of the basic components of the human auditory system, as shown in FIGS. I, 1A and 1B, reference is now made to the geometrical configurations, materials and metods for surgical implantation of the transducers constructed in accordance with the instant invention.

As explained above, the ear consists of anouter ear portion 10, a middle ear portion 12, and aninner portion 13. Contained within the middle ear portion 12, whose boundaries are roughly defined by the tympanum l6 and theovular window 30, there is the ossicle bone chain consisting of the hammer I7, anvil I8, andstirrup 19. The stirrup, in the normal human auditory system, is in operative mechanical vibratory relationship to theovular window 30. All of these elements are contained within the middle ear cavity and operate in the manner described above to coact with the other above-described members of the human auditory system.Tensor muscles 16b are disposed within the cavity to maintain the tympanum l6 properly tensioned, as shows in FIGS. 2, 4 and 5-8, and thechorda tympanum 16a maintains thebone chain 20 in proper orientation.Flexors 16c are also shown in FIGS. 2, 4 and 5-8; the tensors and flexors work in concert with each other to prevent loud noises from damaging the ear drum I6 and the other members of the auditory system.

Referring now to FIGS. 2 and 3, a preferred embodiment of the hearing aid is implanted in the middle ear cavity and is identified generally byreference numeral 60. The stapes has been removed from the ossicle bone chain, either through a simple surgical procedure or through deterioration attributable to diseases of the auditory system.

Hearing aid 60 includes astylus 62 with an annularupper end 64 with aslot 66 passing therethrough; the slot enablesstylus 62 to be slipped onto, and retained in position upon,anvil 18 by applying a crimping pressure to end 64. The point of the stylus bears against the base of a pressuresensitive device 68. A suitable pressure sensitive device is the Pitran piezojunction transducer produced by Stow Laboratories, Inc. of Hudson, Massachusetts; such transducer assumes the form of a planar NPN transistor in which the emitter-base junction is responsive to the application of a pressure or a point force to produce a linear, amplified voltage. Nu-

merous other pressure sensitive devices could be utilized in place of the Pitran piezoelectric transducer; such devices include piezoelectric crystals, diodes, strain gage transducers or electrically conductive wires.

The variable voltage generated by the variable pressure upondevice 68 is conducted byappropriate lead 70 to remotely situated tuningcircuit 72.Circuit 72, which is encased in a suitable housing, is implanted in the mastoid bone near auricle or outer ear 11. Arepresentative circuit 72 may include a high gain FET circuit with automatic gain control to provide external volume tuning forimplant 60. The variable amplified voltage signal is conducted overlead 74 to one side of a pair of piezoelectric crystals retained between the bottom face of pressuresensitive device 68 andoval window 30. The crystals may be oriented either horizontally, as shown in FIG. 3, or vertically, as shown in FIG. 4. The signals are impressed upon the crystals, which may be benders, stretchers, twisters, or combinations thereof, and the crystals vibrate against or in proximity to theoval window 30 orcochlea 43.

Although the pressure of the stylus upon the pressuresensitive device 68 may produce sufficient voltage to effectively vibrate the crystals againstoval window 30, an auxiliary power source may be utilized to insure sufficient voltage for efficiently vibrating the crystals for a prolonged period of time. The auxiliary power source, which is designated byreference numeral 80, may assume the form of a minute rechargable nickelcadmium battery or other suitable rechargable miniature power supply; power source may also be implanted in the mastoid bone at a location remote from the middle ear cavitity. A chargingcircuit 82 is operatively associated withpower supply 80 and could be encased in the same housing implanted in the mastoid bone.Power supply 80 and chargingcircuit 82 are operatively associated withtransducer 68 andcrystals 76,

78 byleads 84 and 86. The voltage frompower supply 80 is impressed upon the crystals vialead 86, and tuningcircuit 72 adjusts the frequency at which the crystals will deform or vibrate.

FIG. 4 showsthe first alternative embodiment of the instant implanted, sound powered hearing aid. The term sound powered indicates that the ear drum is intact and that the vibrations from the sound striking same are transmitted mechanically through the ossicle bone chain toward the inner ear. It will be noted that the hearing aids shown in FIGS. 2, 4, 5, 6, 7 and 8 fall within the broad category of sound powered devices.

In the embodiment of FIGS. 2 and 3 the piezoelectric crystals are horizontally oriented whereas in the embodiment of FIG. 4, identical crystals are vertically oriented in operative relationship tooval window 30; the

stapes orstirrup 19 has not been removed from the ossicle bone chain, and no external control circuits are utilized. The crystals are situated in operative relationship to the footplate of stapes l9 and the vibrations of the crystals assist the footplate in rocking the stapes abouthinge point 19. By virtue of leaving the ossicle bone chain intact, the auditory energy striking the ear drum and passing through the bone chain is distortionfree and hearingaid 88 need only supply minimal assistance to the hearing process.Aid 88 is well suited for overcoming mild hearing losses. Alternatively, thestapes 19 can be removed and theaid 88 placed in its place where conditions permit; consequently, stapes 19 is shown in dotted outline in FIG. 4.

FIG. shows a second alternative sound poweredhearing aid 92 that is located within the middle ear cavity in operative relationship to the ossicle bone chain. As in the embodiment of FIGS. 2 and 3, the stapes is removed from the ossicle bone chain, thus allowing the end ofincus 18 to be free hanging.Hearing aid 92 includes an elongatedpiezoelectric crystal bar 94 that is clipped onto the free end ofincus 18 by means of crimpable rings 96, 98. A pin orstylus 100 is secured to the lower end ofbar 94 and extends inwardly into contact with pressuresensitive device 102 situated in proximity to acrystalline device 103 situated onpromontory 41, adjacent to, or near,oval window 30. Pressuresensitive device 102, which may be a Pitran piezoelectric transducer, a piezoelectric crystal, a pressure sensitive diode, a strain gage transducer or the like produces a voltage that stimulates theoval window 30, and/or thecochlea 43, thus raising the threshold of hearing.Crystalline device 103 may be a bucker, bender, or twister crystal, or combinations thereof.

In addition to serving as a part of the mechanical linkage that produces a significant mechanical advantage in transmitting forces fromear drum 16 tooval window 30, the stresses placed upon pressuresensitive device 102 produce a variable voltage which is conducted bylead 101 to a remotely situated, highgain amplifying circuit 104. The frequency of the voltage is adjusted to the desired rate bycircuit 104 and is then returned overlead 105 tocrystal 103 to cause same to vibrate or deform at the selected frequency.

Although the pressure upon the pressuresensitive device 102 may produce sufficient voltage to effectively vibratecrystal 103 againstoval window 30, anauxiliary power supply 106 may be connected overleads 107, 109 to opposite faces ofcrystal 103. Furthermore, a charging circuit (not shown), similar to chargingcircuit 82 of FIG. 3, could be implanted in the mastoid bone in operative relationship toauxiliary power supply 106.

Sincebar 94 is a piezoelectric crystal, a variable voltage is also produced at opposite faces thereof when it is mechanically stressed by the ossicle bone chain. Such voltage may be added to the voltage produced by the pressuresensitive device 102 and theauxiliary power supply 106, and the sum of the voltages may be applied tocrystal 103 for more efficient operation.

A diode could be utilized in lieu of the crystalline device situated in proximity tooval window 30 in the hearing aid embodiments of FIGS. 2-5. Such diode would receive the voltage produced by pressuresensitive device 68 and rectify same into pulsating D.C. voltage that could be applied directly to the oval window, thus providing electrical stimulus to the auditory nerve. Alternatively, the diode and the crystalline device could be omitted, and the voltage from pressure sensitive device 6'8 could be led over electrically conductive wires directly to the oval window to shock same.

FIG. 6 shows a third alternative embodiment of the sound powered hearing aid, such embodiment being indicated generally byreference numeral 108. The ossicle bone chain is intact, andhearing aid 108 assumes the form of a pressure sensitive device of substantially rectangular shape with a small stylus bearing thereagainst. One corner of the pressure sensitive device is secured to the footplate ofstapes 19 to assist the stapes in rocking or pivoting againstwindow 30 abouthinge 190. The pressure transmitted through the ossicle bone chain presses against the stylus ofdevice 108 with sufficient intensity to generate a voltage onleads 109 that stimulate the area ofoval window 30. If need be, additional voltage may be supplied to pressuresensitive device 102 from a remote power supply situated in the mastoid bone near auricle 11.

FIG. 7 shows a fourth alternative embodiment of the sound powered hearing aid, such embodiment being indicated generally bereference numeral 1 10. The stapes has been removed from the ossicle bone chain, so that the inwardly extending, free end ofanvil 18 can be utilized to transmit vibrations from the ear drum tohearing aid 110. Acollar 112 on hearing aid is slipped over the free end ofanvil 18, so that the movement of the anvil causes movement ofstylus 114 situated on the underside ofcollar 112. The stylus bears upon a pressure sensitive device 116, such as the Pitran transducer described above, and produces a voltage proportional to the force pressing thereagainst. The voltage is led overappropriate leads 118 to a remotely situatedtuning circuit 119 and/or anauxiliary power source 121. The voltage after appropriate tuning andlor amplification, is returned vialeads 120 to opposite faces of a crystalline device 122, such as a piezoelectric crystal. The crystal rests atop a fluid filledsack 124 that is secured tooval window 30 by alayer 126 of plastic jelly-like foam known commercially as .Iel-Foam.

Consequently, sound striking the ear drum and passing through the hammer to the free end of the anvil, produces a variable pressure bearing against pressure sensitive device 116. Device 116, in turn, generates a voltage proportional to the pressure applied thereto; the voltage is led overleads 118 to the remote tuning and/oramplification circuits 119 and 121, respectively, and then returned overleads 120 for application to the opposite faces of crystal 122. The crystal, which may be a bender, twister, or bucker, or any combination thereof, flexes and such movement is transmitted through the fluid medium insack 124 tooval window 30.

If desired, sack 124 may be designed as a truncated cone with the broader surface providing increased support for crystalline device 122. The parallel, narrower surface would be affixed tooval window 30. The cone shape of the sack might well enhance the effectiveness of the vibrations transmitted therethrough. Additionally, the voltage produced by pressure sensitive device 116 may be amplified, tuned, clipped, etc., by conventional circuits before being applied to crystal 122.

FIG. 8 shows a fifth alternative embodiment of the sound powered hearing aid, such embodiment being indicated generally byreference numeral 125.Hearing aid 125 is similar to thehearing aid 110 of FIG. 7 and includes acollar 126, astylus 128, a pressureresponsive device 130, leads 132 and 134,control circuits 136 and 138,crystalline device 140, and a fluid filledsack 142 positioned atopoval window 30. While hearingaid 1 in FIG. 7 requires the removal ofstapes 19,hearing aid 125 takes full advantage of the ossicle bone chain and leaves same intact.

Pressuresensitive device 130, which is a minute element, is slipped between anvil l8 andstirrup 19 at their juncture, and sack 142 is positioned between the footplate of stirrup l9 andoval window 30. The movement of the inner end ofanvil 18, in response to sound striking the ear drum, thus pressesstylus 128 against pressureresponsive device 128 to produce a variable voltage output across leads 132, 134. The variable voltage is tuned bycontrol circuit 136, and the variable voltage is amplified bycontrol circuit 138. The voltage is then applied across the opposite faces ofcrystalline device 140, and the resultant movement ofdevice 140 is transmitted bysack 142 tooval window 30. The sack may be adhered to the oval window by a suitable surgically acceptable jelly, or the depth of the oval window with respect topromontory 41 may be such that the sack is retained in place, without adhesive, by the surrounding walls of the promontory. The sack and the pressure sensitive device are designated to take up any slack in the ossicle bone chain, and thus maximize the effectiveness of the sound conduction through the ossicle bone chain.

Variants ofhearing aid 125 are equally feasible. For example, sack 142 may be omitted andcrystalline device 140 may be positioned againstoval window 30. Alternatively,crystalline device 140 may be implanted in the mastoid bone surrounding the middle ear cavity and rely upon bone conduction techniques to send sound into the inner ear. Additionally, the pressure sensitive device may be slipped under the footplate ofstapes 19 to take advantage of the rocking motion of the stapes. As yet another variant, a first pressure sensitive device may be slipped between teh anvil l8 and the stirrup l9, and a second device may be slipped beneath the footplate. In all instances,such hearing aids 125 are particularly effective in overcoming hearing deficiencies attributable to conductive losses.

Although the operation of hearingaids 60, 88, 92, 108, 110, and 125 has already been described in detail above, it is believed to be expedient to briefly reiterate the salient features of such hearing aids at this juncture. In all embodiments, sound passing down ear canal l5 andstriking ear drum 16, is, in normal sequence, amplifled twenty-two times by the fulcrum action of the ossicle bone chain before reachingoval window 30. The

stylus or the pin function in the same capacity as the stapes without any reduction in the mechanical amplification. Furthermore, the tensors and flexors function as a natural automatic gain control circuit to cushion the impact of loud sounds upon the auditory system.

Additionally, in all the above described soundpowered embodiments, either thestapes 19 or the stylus that cooperates with the pressure sensitive device, converts the movement of the ear drum and the ossicle bones to movement of the pressure sensitive device positioned over, or in operative relationship, tooval window 30. The varied pressure of the sound striking the ear drum thus produces a varied output voltage that may be fed directly tooval window 30 for electrical stimulus, or may be amplified and then impressed upon a crystalline device, such as a piezoelectric crystal, adjacent to, or atop, the oval window. External tuning and volume control circuits may also be utilized. In summary, the ear drum and the ossicle bone chain replace the microphone in the receiving unit of conventional hearing aids, for the sound from the ear drum is mechanically amplified through the natural functions of the ossicle bone chain; such variations in the bone chain are pressed upon a pressure sensitive device to produce a correspondingly varied electrical output that is sent to a high gain amplifying circuit and then to a crystalline device operatively associated with the oval window. Alternatively, the high gain amplifying circuit may be omitted. The above described hearing aids are considered to be sound powered devices, and will probably correct one-half of the mild hearing losses. Approximately, per cent of those persons suffering from hearing losses fall within this extremely broad category.

In all of the embodiments of the instant hearing aid, the crystalline devices, diodes and conductive wires (see FIG. 9) are described and illustrated for the sake of clarity as if they were in direct contact withoval window 30 orpromontory area 41. However, the actual implantation of the hearing aids has shown that an alternative method of fixation is more desirable. Such method relies upon a pliable substance, such as a Jel Foam, to be packed about the innermost end of the device to be coupled tooval window 30. The pliable substance dissolves partially and leaves a protective sac of minute dimension, the sac functioning in much the same manner as a balloon loosely filled with water. This resilience helps to adjust the linkage differential in the bone displacement of the ossicle bone chain. The sac also reduces the danger of rupturing the oval window, and does prevent electrical shock or stimulus from passing therethrough to the oval window.

FIG. 9 shows a hearing aid that delivers an electrical stimulus tooval window 30, such hearing aid comprising two units, a first, or transmittingunit 144 and a second, or receiving,unit 146.Unit 144, which is encased withinplastic housing 148 and has an outwardly extendingpull tab 150, is situated withinear canal 15.Unit 144 includes amicrophone 152, such as an electret microphone, abattery 154 or other suitable power source; a volume control circuit 156; and a transmittingcoil 158. Transmittingcoil 158 can radiate RF energy or magnetic vibrations through the skin to energize receivingunit 146.

Unit 146, which is implanted just beneath the skin in the mastoid bone defining the ear canal, includes a receivingcoil 160, aconducting wire 162, and an electrically stimulateddevice 164 affixed topromontory 41 between the oval and round windows leading into the inner ear.Device 164 may be a piezoelectric crystal, a diode or may merely be a continuation ofconducting wire 130. In all instances, the electric stimulation cooperates with the natural functioning of the ossicle bone chain to increase the hearing of the wearer of this two unit hearing aid.

FIG. shows a pressuresensitive device 166 and an actuating button ordiaphragm 168 positioned immediately adjacent thereto. The button is implanted just under the skin behind auricle l l. The pressure sensitive device may well be a Pitran transducer of the type discussed above, so that manual pressure applied tobutton 168 will press thestylus 170 postioned therebelow against the transducer and produce a variable voltage. Such voltage can be fed into the implanted battery orpower source 172 to recharge same, whenever needed. Asecond button 174 and a second pressuresensitive device 176 can produce a voltage to be fed tovolume control circuit 178; when such circuit is sensitive to voltage levels. Ifcircuit 178 is not so responsive,button 174 and second pressuresensitive device 176 can be omitted without serious impairment to the efficiency of the implanted hearing aid.

FIG. 11 shows a first, or preferred, embodiment of a hearing aid that utilizes transmitting means secured to the inner side ofear drum 16 to transmit signals through the air in the middle ear cavity to sensing means disposed adjacent to theoval window 30,promontory 41, orround window 42. Whereas the sound powered embodiments of FIGS. 2-9 utilize mechanical transmission of sounds through the ossicle bone chain, and the embodiment of FIG. 10 relies upon electrical stimulation, the embodiments of FIGS. 11-17 focus primarily upon transmission between the ear drum and implanted sensing means and pay only incidental attention to the sound mechanically transmitted through the ossicle bone chain.

The hearing aid of FIG. 11 is identified generally byreference character 180 and includes asmall transmitter 182 which assumes the form of a charged piece of material on the inner side ofear drum 16; the transmitter may be a magnet, a fragment of phosphor, a radio active isotope or a charged particle. The receiving unit includes either anelectret microphone 184, a magnetic diode, or a transistor gate that is sensitive to magnetic variations, and apiezoelectric crystal 186 positioned in the area ofpromontory 41. The electret microphone might be one-eighth inch in diameter, and can be obtained from Bell Laboratories and numerous other commercial sources; the magnetic diodes are also available from similar sources. It will be noted that the ossicle bone chain can be left intact while utilizinghearing aid 180.

The negatively or postively charged piece ofmaterial 182 serves to vary the output ofelectret microphone 184. The electret inmicrophone 184 has a static potential, and the plus or minus charge held bypiece 182 will repel, or attract, the electret at the same rate that sound is strikingdrum 16. The minute voltage variations produced by the electret are sent via appropriate leads (not shown) to a remotely situated highgain amplifier circuit 188; after suitable amplification, the voltage is returned overlead 190 and is impressed uponcrystal 186 situated adjacent tooval window 30 to cause same to vibrate. Additionally,hearing aid 180 may employ a remotely locatedpower source 192 with, or without, a remote volume control circuit; the power source and the volume control are implanted in the mastoid bone at locations removed from one another. Bothpower source 192 and high gain amplifier circuit 188 (if such circuit employs a PET or other magnetic responsive device) are recharged by magnetic induction in a manner that has already been explained in connection with FIG. 10. Areed switch 194 is inserted into the circuitry of FIG. 11 to cut off the power tocrystal 186 while the battery orpower source 192 is being recharged.

FIG. 12 shows an alternative form of hearing aid, designated generally byreference numeral 196, that relies upon transmitting means affixed to the inner side of the ear drum and sensing means disposed adjacent to theoval window 30,promontory 41, or round window. The distance between the transmitting means on the eardrum and the sensing means on the promontory is approximately one-quarter' of an inch; obviously, effectively bridging such a small distance without transmission loss or distortion is a relatively simple task for existing solid-state devices.

Hearing aid 196 includes afirst minute magnet 198 with ahook 200 that is slipped over the malleus or hammer 17 near its point of contact with the inner face ofear drum 16.Hook 200 might also be anchored in the vicinity of chorda typanum 16a; see FIG. 1. Continuing interiorly through the middle ear cavity,hearing aid 196 further includes asecond magnet 202 that is operatively associated with astylus 204 affixed todiaphragm 206. The stylus is positioned in operative relationship to a pressuresensitive device 208, such as a Pitran transducer, which produces a variable voltage proportional to the pressure applied thereto by the stylus. The voltage output fromdevice 208 is led overleads 210 and 212 to a remote tuning and amplifyingcircuit 212 and aremote charging circuit 214, respectively. The output fromcontrol circuits 212 and 214 is applied to crystalline situated in the area ofpromontory 41, which device may be a piezoelectric crystal capable of bucking, twisting or bending. Under certain circumstances controlcircuits 212 and 214 may be omitted. In either event, the motion of the crystalline device is related directly to the sound striking ear drum l6 and the ossicle bone chain is left intact, thus leaving the natural automatic gain control (AGC) facility of the ossicle bone chaim unimpaired.

FIG. 13 diagrammatically shows another sensing circuit that will respond to the variations in the magnetic field transmitted thereto bymagnet 198. The circuit of FIG. 13 also includes thesecond magnet 202 which is secured to thediaphragm 218 of an electret microphone 220. The movement ofmagnet 198 as sound energy strikes the ear drum causesmagnet 202 to move in response to changes in the magnetic field established therebetween. The movement ofmagnet 202 pumps electret microphone 220 and produces a variable voltage output that is led, over appropriate leads, toremote tuning circuit 222 andremote charging circuit 224. After the voltage has been properly regulated, it is applied tocrystalline device 226, which vibrates in the area ofpromontory 41.

FIG. 14 diagrammatically shows another sensing circult that will respond to the variations in the magnetic field transmitted thereto bymagnet 198 affixed to the inner side of the ear drum. The second or receivingmagnet 202 utilized in the ambodiments of FIGS. 12 and 13 is replaced by atransistor gate 228 that is responsive to changes in the intensity and polarity of magnetic fields; one common type ofgate 228 is a fieldeffect transistor (F E.T.). The small output voltage acrossgate 228 is suitable regulated bycontrol circuits 222, 224, before being applied to acrystalline device 229 situated in the area ofpromontory 41.

FIG. 15 diagrammatically shows yet another sensing circuit that will respond to the variations in the magnetic field transmitted thereto bymagnet 198 affixed to the inner side of the ear drum. The second or receivingmagnet 202 utilized in the embodiments of FIGS. 12 and 13, or thetransistor gate 228 of FIG. 14, is replaced by a Hall-effect device 231) that is responsive to changes in the intensity and polarity of magnetic fields. The small output voltage acrossdevice 230 is suitably regulated bycontrol circuits 222, 224 before being applied to acrystalline device 231 situated in the area ofpromontory 41.

Numerous modifications can readily be effectuated in the hearing aid depicted in FIGS. 12-15. For example, a small fragment of phosphor or other radio-active isotope could be substituted formagnet 198. Also,crystalline devices 216 and 226 (FIGS. 12 and 13, re spectively) could be eliminated, and the variable voltage appearing across the receiving means could be utilized directly to stimulate, or shock, the oval window, promontory, or round window. Alternatively, the crystalline devices could be eliminated and a diode substituted therefore; such diode would receive the voltage produced by the sensing means and rectify same into pulsating DC. voltage that could be applied directly tooval window 30, thus providing electrical stimulus to the auditory nerves of the inner ear.

FIGS. 16-17 disclose a two unit hearing aid that employs an audio responsive light emitting unit and light sensing means on opposite sides of the ear drum that respond to sounds striking the ear drum. The audio responsive unit is identified byreference numeral 230 and is encased in aplastic housing 232 that fits withinear canal 15; the housing has apull tab 234 for removing the unit. Withinhousing 232 is aminiature microphone 236, a long-livedrechargable battery 238, anamplifier 240 and acircuit 242 for energizinglight source 244 that extends through the housing and emits a beam of collimated light down the ear canal.

The light sensing means is disposed on the opposite side ofear drum 16 in the area ofpromontory 41 and in substantial alignment withlight source 244. The light sensing means includes a lightresponsive resistor 246 connected to anamplifier 248, the output of such amplifier being fed toremote control circuits 250, 252 and thence tocrystalline device 254. Asuitable resistor 246 would be a cadmium sulphide cell or photocell or a selenium cell. The vibration ofdevice 254 in the area ofpromontory 41 augments the sound energy mechanically transmitted from the ear drum through the ossicle bone chain. If desired,crystalline device 254 could be omitted and the output voltage fromamplifier 248 could be impressed directly upon the area ofpromontory 41 to electrically stimulate the auditory nerves. Alternatively,crystalline device 254 could be omitted and the output voltage fromamplifier 248 could be fed to a diode that would convert the voltage into a pulsating D. C. stimulus.

The transmittingunit 230 converts the sound or audioenergy striking microphone 236 into light pulses emanating fromlight source 244. Sinceear drum 16 is opaque and the ear canal is dark, the light pulses are easily detected bydiode 246 and the circuitry associ ated therewith for converting the light energy into electrical energy.

FIG. 18 shows yet another embodiment of a hearing aid constructed in accordance with the principles of the instant invention. This embodiment also comprises two units, a first or transmittingunit 256, and a second or receivingunit 258.Unit 256, which is encased withinplastic housing 260 and has an outwardly extendingpull tab 262, is situated withinear canal 15.Unit 256 includes amicrophone 264 for receiving auditory energy, abattery 266 or other suitable power source, an amplifyingcircuit 268, and atransmitting device 270, such as a coil.Unit 258 comprises areceiver 272 operatively associated with a small,rechargeable battery 274 and acrystalline device 276. The receiver, the battery and the crystalline device are implanted within the mastoid bone a short distance fromear canal 15.Unit 256 sends RF, magnetic or elecrostatic signals to implanted receivingunit 258.Unit 258 then converts the signal into vibratory movement ofcrystalline device 276; such movement is transmitted to the cochlea by bone conduction through the mastoid bone.

The hearing aid embodiment of FIG. 18 is particularly well suited to overcome tinnitus, a physical and/or mental disease associated with the auditory system that produces a sensation of ringing, whistling or buzzing in the ears of the person so afflicted. The transmitting units can be removed from the ear canal and tuned so as to transmit various sounds to the ear nerve, the characteristics of the transmitted sound being selected so as to mask the unpleasant sounds associated with tinnitus.

FIG. 19 illustrates anear mold 278 that fits into auricle 11 and extends intoear canal 15 towardsear drum 16.Ear mold 278, which may be utilized in connection with the manually operable recharging devices of FIG. 10 or in lieu thereof, is a custom-made, hollow shell with afirst charging coil 280 secured therein in a fixed position consistent with the fixed position of implantedpower source 172 which has a receivingcoil 173.Charging coil 280 radiates energy tocoil 173 for implantedpower source 172 to thereby recharge same. Asecond charging coil 282 may be used to adjust the implanted volume and/orfrequency tuning circuit 178; however, care must be exercised to position the coils as far apart as space will permit, thus isolating the coils and circuits from one another.

A chargingmagnet 284, or other polarizing device, is situated at the innermost end ofear mold 278, which is reduced in diameter to avoid discomfort to the person temporarily wearing same during the fitting process. The charging magnet or polarizing device causes variations in the polarity and intensity of the magnet or radioactive fragment attached to the inner side ofear drum 16, as shown in FIGS. 11-15. The charging coils 280 and 282 inear mold 278 are powered over appropriate leads from a remote,adjustable control device 284 that is simply plugged into a conventional wall outlet.

At periodic intervals, the wearer of the hearing aid will visit a clinic and have the ear mold inserted into his ear. Trained personnel will then readjust the control circuits for the hearing aid without resort to surgical procedures.

Many of the above described hearing aids can be implanted in the first instance by the simple surgical procedure of cutting and laying back the ear drum to expose the middle ear cavity. Other hearing aids can be implanted by drilling through the mastoid bone behind the ear toward the middle ear cavity; an accurately drilled hole will be aligned with the area of theoval window 30,promontory 41 and the round window so that the various sensing devices can be positioned thereagainst. Drilling through the mastoid leaves the ear drum intact and reduces the potential side-effects of such initial surgical procedure.

Since sundry additional modifications may be made in the configuration and materials of the instant implanted hearing aids, it is to be understood that all matter herein set forth or shown in the accompanying drawings is to be interpreted as illustrative in nature and not in a limiting sense.

We claim:

1. An implantable, sound powered hearing aid comprising:

a. transducer means positioned interiorly of the ear drum in proximity to the oval window within the middle ear cavity,

b. said transducer means being pressure sensitive so as to generate a variable voltage output in response to the application of pressure thereto,

c. stylus means secured to either the hammer, anvil or stirrup of the ossicle bone chain located inthe middle ear cavity in operative relationship to said pressure sensitive transducer means, said stylus means being pressed against said transducer means by the ossicle bone chain with a variable force when sound strikes the ear drum to thereby produce a variable voltage, and

e. conducting means to lead said variable voltage to the area of the oval window to electrically stimulate same.

2. The hearing aid as defined inclaim 1 further including a piezoelectric crystal positioned in the area of the oval window, said conducting means impressing said variable voltage upon said crystal to cause same to vibrate and thus stimulate the auditory nerve.

3. The hearing aid as defined inclaim 1 further including a diode positioned in the area of the oval window, said conducting means leading said variable voltage to said diode which rectifies same into pulsating D. C. voltage and thus stimulates the auditory nerve.

4. The hearing aid as defined in claim 2 further including an amplifying circuit connected between said pressure sensitive transducer means and said piezoelectric crystal, said amplifying circuit amplifying the variable voltage produced by said transducer means before said voltage is impressed upon said crystal.

5. The hearing aid as defined in claim 2 further including an auxiliary power supply, connected to said piezoelectric crystal, to impress its voltage thereupon.

6. The hearing aid as defined in claim 5 further including a tuning circuit connected between said pressure sensitive transducer means and said piezoelectric crystal and in operative relationship to said power supply, said tuning circuit adjusting the frequency at which said crystal will vibrate.

7. The hearing aid as defined in claim 5 further including recharging means for said auxiliary power supply, said recharging means comprising a button under the skin of the wearer of the hearing aid, a stylus secured to said button, and a pressure sensitive transducer means situated in operative relationship to said transducer means, said transducer means connected to said auxiliary power supply to supply a variable voltage thereto, said button being manually depressed to press the stylus against the transducer means whenever said auxiliary power supply requires recharging.

8. The hearing aid as defined in claim 2 wherein said stylus means comprises a piezoelectric bar with a pin extending outwardly therefrom.

9. The hearing aid as defined in claim 8 wherein said piezoelectric bar produces a variable voltage as said bar is stressed when sound striking the ear drum is transmitted through the ossicle bone chain, and circuit means for amplifying the variable voltage before applying same to the oval window area.

10. The hearing aid as defined inclaim 1 wherein the transducer means are held in a rectangular package, said package being positioned in the opening of the stapes of said ossicle bone chain with one corner of the package bearing against the footplate of the stapes.

11. The hearing aid as defined inclaim 1 further including a resilient fluid filled sack interposed between the ossicle bone chain and the area of the oval window and a piezoelectric crystal disposed thereupon, said conducting means impressing said variable voltage produced by said pressure sensitive device upon said crystal which vibrates atop the sack and transmits said vibrations therethrough to the area of the oval window.

12. The hearing aid as defined in claim 11 further including a collar situated atop said transducer means, said collar engaging the free end of the anvil of the ossicle bone chain.

13. The hearing aid as defined inclaim 1 wherein said transducer means and said stylus means are slipped between the joint formed by the anvil and stirrup of the ossicle bone chain.

14. An implanted hearing aid comprising:

a. a transmitting unit encased in a housing and positioned within the ear canal, said transmitting unit including:

1. a miniature microphone for producing a variable voltage proportional to the sound striking same,

2. a power source for energizing said microphone,

3. an amplifying circuit for increasing the voltage produced by said microphone,

4. a transmitting coil operatively connected to said microphone, said power source, and said amplifying circuit for radiating an electromagnetic field of variable intensity, and

b. a receiving unit including:

1. a receiving coil implanted in the mastoid bone in proximity to said transmitting coil, said coils being inductively coupled together, and

2. conducting means implanted in the mastoid bone to lead the variable voltage received by said coil to the area of the oval window to electrically stimulate same.

15. The hearing aid as defined in claim 14 further including a piezoelectric crystal positioned in the area of the oval window, said conducting means impressing said variable voltage upon said crystal to cause same to vibrate and thus stimulate the auditory nerve.

16. The hearing aid as defined in claim 14 further including a diode positioned in the area of the oval window, said conducting means leading said variable voltage to said diode which rectifies same into pulsating D. C. voltage and thus stimulates the auditory nerve.

17. An improved hearing aid comprising:

a. transmitting means secured to the inner surface of the eardrum in the area of the junction defined by the hammer and the ear drum, said transmitting means radiating magnetic waves into the middle ear cavity,

b. receiving means situated within the middle ear cavity on the promonotry promontory the area of the oval window, said receiving means including: 1. magnetically responsive means retained upon a flexible diaphragm,

2. a stylus connected to said diaphragm,

3. a pressure sensitive transducer for producing a variable voltage in response to the application of pressure thereto, said stylus being positioned in operative relationship to said transducer,

4. said stylus being pressed against said transducer when the transmitting moves relative to the receiving means as sound energy strikes the ear drum to thereby produce a variable voltage, and

c. conducting means to lead said variable voltage to the area of the oval window to electrically stimulate same.

18. The hearing aid ofclaim 17 wherein the transmitting means is a permanent magnet.

19. The hearing aid ofclaim 17 wherein the transmitting means is a fragment of phosphor.

20. The hearing aid as defined inclaim 17 wherein the transmitting means is a radioactive isotope.

21. The hearing aid as defined inclaim 17 wherein the magnetically responsive means is a field-effect transistor gate.

22. The hearing aid as defined inclaim 17 wherein the magnetically responsive means is a Hall-efiect element.

23. The hearing aid as defined inclaim 17 further including a piezoelectric crystal positioned in the area of the oval window, said conducting means impressing said variable voltage upon said crystal to cause same to vibrate and thus stimulate the auditory nerve.

24. The hearing aid as defined inclaim 17 further including a diode positioned in the area of the oval window, said conducting means leading said variable voltage to said diode which rectifies same into pulsating D. C. voltage and thus stimulates the auditory nerve.

25. An implanted hearing aid comprising:

a. a transmitting unit encased in a housing and positioned within the ear canal, said transmitting unit including:

l. a miniature microphone for producing a variable voltage proportional to the sound striking same,

2. a power source for energizing said microphone,

3. an amplifying circuit for increasing the voltage produced by said microphone,

4. a light emitting device connected to said microphone, said power source, and said amplifying circuit for projecting a light beam of variable intensity,

b. a receiving unit including:

1. a light responsive sensor implanted on the promontory in the area of the oval window, said light emitting device and said light responsive device being in substantial alignment with one another and on opposite sides of the opaque ear drum,

2. said sensor producing a variable voltage proportional to the intensity of the light beam falling thereupon,

3. amplifying means for increasing the voltage produced by said light responsive sensor, and

4. conducting means to lead the variable voltage produced by said sensor and said amplifying means to the area of the oval window to electrically stimulate same.

26. An implanted hearing aid for the treatment of tinnitus comprising:

a. a transmitting unit encased in a housing and positioned within the ear canal, said transmitting unit including:

1. a miniature microphone for producing a variable voltage proportional to the sound striking same,

2. a power source for energizing said microphone,

3. an amplifying circuit for increasing the voltage produced by said microphone,

4. a transmitting coil operatively connected to said microphone, said power source, and said amplifying circuit for radiating an electromagnetic field of variable intensity,

b. a receiving unit implanted in the mastoid bone surrounding the ear canal including:

1. a second miniature microphone responsive to the electromagnetic field radiated by the transmitting for producing a variable voltage,

2. a power source for energizing the second microphone, and a 3. crystalline device that vibrates in response to the voltage applied thereto by the second microphone, the vibrations being conducted through the mastoid bone to the inner ear to stimulate the auditory nerve.

Claims (44)

1. An implantable, sound powered hearing aid comprising: a. transducer means positioned interiorly of the ear drum in proximity to the oval window within the middle ear cavity, b. said transducer means being pressure sensitive so as to generate a variable voltage output in response to the application of pressure thereto, c. stylus means secured to either the hammer, anvil or stirrup of the ossicle bone chain located in the middle ear cavity in operative relationship to said pressure sensitive transducer means, d. said stylus means being pressed against said transducer means by the ossicle bone chain with a variable force when sound strikes the ear drum to thereby produce a variable voltage, and e. conducting means to lead said variable voltage to the area of the oval window to electrically stimulate same.

2. a power sourCe for energizing the second microphone, and a

2. a power source for energizing said microphone,

2. The hearing aid as defined in claim 1 further including a piezoelectric crystal positioned in the area of the oval window, said conducting means impressing said variable voltage upon said crystal to cause same to vibrate and thus stimulate the auditory nerve.

2. a power source for energizing said microphone,

2. said sensor producing a variable voltage proportional to the intensity of the light beam falling thereupon,

2. conducting means implanted in the mastoid bone to lead the variable voltage received by said coil to the area of the oval window to electrically stimulate same.

2. a stylus connected to said diaphragm,

2. a power source for energizing said microphone,

3. an amplifying circuit for increasing the voltage produced by said microphone,

3. an amplifying circuit for increasing the voltage produced by said microphone,

3. amplifying means for increasing the voltage produced by said light responsive sensor, and

3. crystalline device that vibrates in response to the voltage applied thereto by the second microphone, the vibrations being conducted through the mastoid bone to the inner ear to stimulate the auditory nerve.

3. a pressure sensitive transducer for producing a variable voltage in response to the application of pressure thereto, said stylus being positioned in operative relationship to said transducer,

3. an amplifying circuit for increasing the voltage produced by said microphone,

3. The hearing aid as defined in claim 1 further including a diode positioned in the area of the oval window, said conducting means leading said variable voltage to said diode which rectifies same into pulsating D.C. voltage and thus stimulates the auditory nerve.

4. The hearing aid as defined in claim 2 further including an amplifying circuit connected between said pressure sensitive transducer means and said piezoelectric crystal, said amplifying circuit amplifying the variable voltage produced by said transducer means before said voltage is impressed upon said crystal.

4. a light emitting device connected to said microphone, said power source, and said amplifying circuit for projecting a light beam of variable intensity, b. a receiving unit including:

4. a transmitting coil operatively connected to said microphone, said power source, and said amplifying circuit for radiating an electromagnetic field of variable intensity, and b. a receiving unit including:

4. said stylus being pressed against said transducer when the transmitting moves relative to the receiving means as sound energy strikes the ear drum to thereby produce a variable voltage, and c. conducting means to lead said variable voltage to the area of the oval window to electrically stimulate same.

4. a transmitting coil operatively connected to said microphone, said power source, and said amplifying circuit for radiating an electromagnetic field of variable intensity, b. a receiving unit implanted in the mastoid bone surrounding the ear canal including:

4. conducting means to lead the variable voltage produced by said sensor and said amplifying means to the area of the oval window to electrically stimulate same.

5. The hearing aid as defined in claim 2 further including an auxiliary power supply, connected to said piezoelectric crystal, to impress its voltage thereupon.

6. The hearing aid as defined in claim 5 further including a tuning circuit connected between said pressure sensitive transducer means and said piezoelectric cryStal and in operative relationship to said power supply, said tuning circuit adjusting the frequency at which said crystal will vibrate.

7. The hearing aid as defined in claim 5 further including recharging means for said auxiliary power supply, said recharging means comprising a button under the skin of the wearer of the hearing aid, a stylus secured to said button, and a pressure sensitive transducer means situated in operative relationship to said transducer means, said transducer means connected to said auxiliary power supply to supply a variable voltage thereto, said button being manually depressed to press the stylus against the transducer means whenever said auxiliary power supply requires recharging.

8. The hearing aid as defined in claim 2 wherein said stylus means comprises a piezoelectric bar with a pin extending outwardly therefrom.

9. The hearing aid as defined in claim 8 wherein said piezoelectric bar produces a variable voltage as said bar is stressed when sound striking the ear drum is transmitted through the ossicle bone chain, and circuit means for amplifying the variable voltage before applying same to the oval window area.

10. The hearing aid as defined in claim 1 wherein the transducer means are held in a rectangular package, said package being positioned in the opening of the stapes of said ossicle bone chain with one corner of the package bearing against the footplate of the stapes.

11. The hearing aid as defined in claim 1 further including a resilient fluid filled sack interposed between the ossicle bone chain and the area of the oval window and a piezoelectric crystal disposed thereupon, said conducting means impressing said variable voltage produced by said pressure sensitive device upon said crystal which vibrates atop the sack and transmits said vibrations therethrough to the area of the oval window.

12. The hearing aid as defined in claim 11 further including a collar situated atop said transducer means, said collar engaging the free end of the anvil of the ossicle bone chain.

13. The hearing aid as defined in claim 1 wherein said transducer means and said stylus means are slipped between the joint formed by the anvil and stirrup of the ossicle bone chain.

14. An implanted hearing aid comprising: a. a transmitting unit encased in a housing and positioned within the ear canal, said transmitting unit including:

15. The hearing aid as defined in claim 14 further including a piezoelectric crystal positioned in the area of the oval window, said conducting means impressing said variable voltage upon said crystal to cause same to vibrate and thus stimulate the auditory nerve.

16. The hearing aid as defined in claim 14 further including a diode positioned in the area of the oval window, said conducting means leading said variable voltage to said diode which rectifies same into pulsating D.C. voltage and thus stimulates the auditory nerve.

17. An improved hearing aid comprising: a. transmitting means secured to the inner surface of the eardrum in the area of the junction defined by the hammer and the ear drum, said transmitting means radiating magnetic waves into the middle ear cavity, b. receiving means situated within the middle ear cavity on the promontory in the area of the oval window, said receiving means including:

18. The hearing aid of claim 17 wherein the transmitting means is a permanent magnet.

19. The hearing aid of claim 17 wherein the transmitting means is a fragment of phosphor.

20. The hearing aid as defined in claim 17 wherein the transmitting means is a radioactive isotope.

21. The hearing aid as defined in claim 17 wherein the magnetically responsive means is a field-effect transistor gate.

22. The hearing aid as defined in claim 17 wherein the magnetically responsive means is a Hall-effect element.

23. The hearing aid as defined in claim 17 further including a piezoelectric crystal positioned in the area of the oval window, said conducting means impressing said variable voltage upon said crystal to cause same to vibrate and thus stimulate the auditory nerve.

24. The hearing aid as defined in claim 17 further including a diode positioned in the area of the oval window, said conducting means leading said variable voltage to said diode which rectifies same into pulsating D.C. voltage and thus stimulates the auditory nerve.

25. An implanted hearing aid comprising: a. a transmitting unit encased in a housing and positioned within the ear canal, said transmitting unit including:

26. An implanted hearing aid for the treatment of tinnitus comprising: a. a transmitting unit encased in a housing and positioned within the ear canal, said transmitting unit including:

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