|Publication number||US3209081 A|
|Publication date||28 Sep 1965|
|Filing date||2 Oct 1961|
|Priority date||2 Oct 1961|
|Publication number||US 3209081 A, US 3209081A, US-A-3209081, US3209081 A, US3209081A|
|Inventors||Behrman A Ducote, Jr Louis E Adin|
|Original Assignee||Behrman A Ducote, Jr Louis E Adin|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (5), Referenced by (85), Classifications (21)|
|External Links: USPTO, USPTO Assignment, Espacenet|
United States Patent O 3,209,081 SUBCUTANEOUSLY IMPLANTED ELECTRONIC DEVICE Behrman A. Ducote, 418 Maple Ave., and Louis E. Adin, Jr., 3707 Gaston Ave., both of Dallas, Tex. Filed Oct. 2, 1961, Ser. No. 142,375 4 Claims. (Cl. 179-107) This invention is primarily concerned with a hearing aid to assist persons with defective hearing, and is particularly concerned with a hearing aid including a sound amplifier and transmitter unit arranged to be conveniently carried on the body of the user, and a remote receiver, unconnected physically with the sound amplifier-transmitter unit, which may be implanted subcutaneously against the skull of the user in concealed position, so that the hearing aid is completely invisible. The mastoid bone is a convenient part of the skull in which to irnplant the receiver, because it assures suicient thickness to recess the receiver therein.
Hearing aids have customarily included a sound amplier-transmitter unit carried on the person, with a wire connecting the transmitter to a receiver which is struck into the ear or is suspended to the ear. In some instances the speech amplifier-transmitter unit has been mounted in eyeglass frames with a wire connection between the eyeglass frames and a receiver unit inserted in the ear.
Bone conduction type receivers have not been entirely satisfactory, in that they do not make direct contact with the mastoid bone, but sound transmission is interfered with by skin and tissue therebetween, so that completely satisfactory reception is not attained.
The present invention includes among its objects the provision of a transistorized receiver unit molded into a plastic case, which may be sterilized, and subcutaneously implanted directly against the skull of the patient, so that the receiver makes a direct contact with the bone through which sound may be conducted to the inner ear via bone conduction, without interference by skin and tissue therebetween.
No wires or other physical connection is required between the speech amplifier-transmitter unit, and the implanted receiver, because of a lunique arrangement whereinpower for operating the electrical components in the implanted receiver is supplied by an RF transmitter carried in the speech amplifier-transmitter unit, which power is detected, rectified, and impressed upon a capacitance in the circuit of the implanted receiver in the form of a D.C. potential which is applied to the emitters of the transistor amplifiers in the implanted radio receiver.
The speech amplifier and transmitter unit are miniature transistorized circuits mounted in a convenient carrying case, in the form of a fountain pen or otherwise and carried on the person of the user in concealed position, so that in conjunction with the embedded receiver unit provides a hearing aid which is completely invisible in that there is nothing in the ear, behind the ear, in the hair, or worn in eyeglass frames, as in previous hearing aids and devices, and there are no cords, or other connections, between the speech amplifier-transmitter units and the receiver which could hinder normal activity of the patient.
In the use of the hearing aid receiver as herein deice anesthesia, and is so constructed that after normal postoperative care to allow the rather minor incision made to implant the receiver to heal, the receiver unit requires no further care, in that there is no battery carried therein which requires replacement, power is supplied thereto by remote transmission, and all circuit units are implanted and sealed in a protective coating of tissue tolerant plastic, and are not subject to deterioration by exposure to body fluids and elements. The volume control for the receiver is accomplished by a volume control knob on the speech amplifier-transmitter unit, which controls the amplitude of the input signal supplied to the speech amplier. Therefore, no direct volume control for the receiver is required, and it may be implanted in or on the skull in inaccessible position.
The implanted power supply, described herein, could be employed to supply power to other tissue implanted electronic devices than hearing aid receivers.
Other and further objects of the invention will become apparent upon reading the detailed specification hereinafter following, and by referring to the drawings annexed hereto.
A suitable embodiment of the invention is shown in the attached drawing wherein:
FIGURE I is a side elevational view of the speech amplifier transmitter unit case, which takes the form of a fountain pen with a clip thereon to be inserted in a concealed position in the pocket of the wearer;
FIGURE II is a side elevational view of the implanted receiver unit which, as shown, is approximately full size;
FIGURE III is an enlarged transverse, cross-sectional View of the receiver unit to be implanted;
FIGURE IV is a schematic view of the electrical circuit of a sound transmitter, power transmitter and speech amplifier, the components `of which are mounted in the fountain pen-like Icasing of FIGURE I;
FIGURE V is a schematic View of the implanted relceiver, the components of which are molded and encased in the receiver unit of FIGURES II and III; and
FIGURE VI is a schematic view of a modified form of remote power supply used with the implanted receiver but which could be used in conjunction with any body implanted electronic equipment, such as a cardiac pacer.
Numeral and letter references are employed to designate the various parts and components shown in the drawings, and like numerals indicate like parts throughout the various figures of the drawings.
The sound amplifier, sound transmitter, power transmitter units are shown in schematic form in FIGURE IV, and the components thereof are mounted in the fountain pen-like casing 24, shown in FIGURE I.
The sound amplifier unit is indicated by the letter A, and includes a conventional tr-ansistorized circuit including the microphone 10 which is coupled to the transistor amplifier 12 and therefrom to the transistor amplifier 13. The audio signal is picked up by the microphone 10, the amplitude thereof being controlled by the rheostat arm 35, which is operated by the knob control 41 on the casing section 24b shown in FIGURE I. The amplified signal is transferred across the output transformer 11 to the transistorized circuit of the sound transmitter unit B, where the audio signal modulates the radio frequency signal supplied by the crystal oscillator 36. The modulated signal is transmitted through space from the tank circuit 14, and is picked up by the tuned LC circuit 37 of the receiver F, which is tuned to the radio frequency of the sound transmitter, and is detected and rectilied by the soundreceiver solid state diode C. The rectified signal is fed through the transistor ampliers 15 and 16 to the -output transformer 17, and to the skull of the .patient from whence it is transferred through bone conduct-ion to the inner ear of the patient.
Power is suppliedto the amplifier transistors and 16 of the implanted radio receiver F from a power transmitter, indicated at D. This is a transistorized oscillator circuit which emits a radio frequency signal provided .by the crystal oscillator 3S and transistor 39. This amplified radio frequency signal is transmitted through space from the `output tank circuit 19, and is picked up by the tuned circuit 40 in the implanted receiver. This radio frequency signal is detected and rectified by the crystal diode E, and the electrical potential produced thereby is impressed across andstored in the capacitor 20.
The positive plate of the capacitor is connected to the emitters 21 and 22 of the amplifier transistors 15 and 16, so that a continuous voltage sufficient to cause the emission of the transistors 15 and 16 is applied thereto, and such voltage is continuously and constantly applied as long as the power transmitter D is functioning.
The power is supplied for the operation of the speech amplifier A, sound transmitter B, and power transmitter D, by a miniature 6-volt battery 23. The battery 23 is mounted in the casing 24, shown in FIGURE I, and su-ch constitutes the external power supply for the hearing aid, including the speech amplifier-transmitter unit, and the remote receiver unit.
The fountain pen-like casing, generally indicated at 24, includes a cap 24a and a base portion 24b :in which the various` physical components of the :speech amplifier, transmitter, battery and volume control are mounted. The microphone 10 is mounted in the top of cap 24a, and suitable perforations should be provided through the cap for admission of sound to the microphone. The cap 24a has a spring clip 24C thereon which may be clipped to the pocket of the wearer in a concealed position. The volume is controlled by rotation of the volume control knob, indicated at 41.
The implant receiver unit F is shown drawn to approximate full scale in FIGURE II, and is preferablyy generally elliptical in shape and is actually less in overall dimension than a dime, and is relatively thin.
The receiver components, shown schematically in VFIGURE V, are preferably mounted on a mounting board 26, the said receiver components being indicated diagrammatically in FIGURE III by the numeral 27. After the receiver components are mounted onthe board 26, they are thoroughly tested, to assure operability of the receiver circuit. After being tested, the board 26 with components 27 mounted thereon, are encased in a Vplastic: covering or casing, indicated generally at 28. The plastic covering may be applied about the board 26 and components 27 by any suitable method. However, the plastic material used would necessarily be of a type which is tissue tolerant, that is, it is not harmfull or destructive to-body tissues, and which may be embedded within the body tissues without causing infection or nerve, bone, or tissue damage. Several types of such plastic material are available, such as Polyethylene and certain epoxy resins which are tissue tolerant. A suitable epoxy resin material for this use is thatknown as Minnesota Mining Scotch Cast No. 5.
Before molding the receiver components in the plastic material 28, a layer of tantalum metal 29, or other suitable sound conducting metal is preferably affixed about the components, on the side of the implantreceiver device which will Contact the skull, and is molded therein. The actual molding of the plastic material 28 about the receiver components 2.7 may be accomplished by either .dipping the components in a iiuid state plastic material, and allowing the plastic material t-o harden and set thereabout or the components 27 may be molded in the plastic material under moderate heat and pressure,fso as not to damage the receiver components.
Preferably a layer of relatively soft plastic material, such as vinyl plastic or silicon rubber, is molded and formed about the plastic material 28. However, this last layer of plastic material could be tiliminated, without affecting the operation and utility of the implant receiver. Whatever plastic material is employed, it must be of a type W-hich will withstand sufficient heat for sterilization. Before implanting the completed receiver unit F, in the manner hereinbefore described, the said receiver unit must lbe sterilized so that it may be placed in the tissues in a sterile state.
The receiver unit F is implanted in the following manner:
The surgeon makes an incision through the skin and tissues overlying the skull, which may be the mastoid portion of the skull, sufficiently to drill a cavity of sufficient depth and size in the outer surface of the skull to receive the implant receiver F. Since the mastoid bone is insensitive, there is no pain involved in such procedure, except that attendant upon making the incision in the skin and tissue, and 4reclosing same. As a matter of fact, the operation can `be easily performed in the doctors office with local anesthesia.
After the receiver unit F has been placed in the cavity formed in the surface of the skull bone, the tissue and skin is sutured thereover to close the incision. Other than the application of antiseptic and dressing over the `sutured incision, the post-operative care is of slight consequence. Within a short time the bone will reform about, and adhere to, the implanted receiver, so that it is firmly set in place, and is, in effect, integrated with the bone by direct contact. The receiver unit could be effectively subcutaneously mounted against any portion of the skull without forming the cavity therein.
The receiver unit F will be thoroughly checked and tested for operability before subcutaneously implanting into or against the skull bone, so that there is slight chance that the receiver will become inoperable to such an extent as to have to be replaced, `but if replacement becomes necessary, only a minor operation would be required.
Since the receiver has a self-contained power supply charged from an external source as hereinbefore described, no wires or connections arev required between the transmitter and the receiver.
The remote implanted power supply of the type herein described could be employed in any application where an electrical or electronic device is required in or on the human body as a therapeutic agent. One example of another use of such an implanted power supply is in supplying power for the operation of a cardiac pacer. A cardiac pacer, which has come into recent use, is an electrical circuit which is implanted in the patients body to provide intermittent electrical impulses to the heart to regulate the hearts beat. Heretofore it has been necessary to provide an electrical connection between the cardiac pacer and a power supply externally of the body, such as a battery. With the use of the power supply herein described, same could be implanted in the body of the patient and supplied with power from a transmitter externally of the body without physical connection. A suitable form of such an implanted cardiac pacer is shown schematically in FIGURE VI, wherein a pickup transformer 31 picks up a radio frequency signal from a radio frequency transmitter of the type hereinbefore described, which signal is detected by the solid state diode rectifier 32 to charge the capacitor 33 and store the power therein for the operation ofthe cardiac pacer 34.
Thus it will be seen that the implanted power supply has other and separate uses from use in connection with a hearing aid receiver.
It will be understood that other and further uses and embodiments of our invention may be made without departing from the spirit and scope of the appended claims.
Having described our invention, we claim:
1. A hearing aid comprising an integral audio amplifier, audio transmitter and power transmitter unit encased within a common casing arranged to be carried on the person of the wearer of the hearing aid, said unit including an audio amplifier with an input for picking up audio signals for amplification; a volume control on the input including a volume control knob accessible from outside the casing, an audio transmitter connected to the output of the audio amplifier arranged to transmit signals picked up and amplified by the audio amplifier by electromagnetic impulse, a radio frequency oscillator and transmitter in said casing, said audio amplifier, audio transmitter and radio frequency transmitter being supplied by a common power supply within the casing; an audio receiver-amplier and a radio frequency receiver encased within a plastic, tissue tolerant material mounted in a cavity formed in the skull of the wearer of the hearing aid beneath the skin of the wearer, said radio frequency signal receiver including a detector to detect the signal transmitted by the radio frequency signal transmitter, and a capacitance in parallel therewith arranged to store the detected voltage of the radio frequency signal, said capacitance being connected to the audio receiver-amplifier unit to supply power thereto for operation thereof; and means to transfer the audio signal picked up and amplified by the audio receiver amplifier to the mastoid bone of the wearer.
2. A receiver-amplifier unit for use in a hearing aid including, an audio receiver-amplifier; a radio frequency signal receiver including a detector to detect a radio frequency transmitted by electromagnetic energy thereto; a capacitance in parallel with the detector arranged to store the detected voltage of the radio frequency signal, the said capacitance being connected to the audio receiver-ampliiier, to supply power thereto; a board member on which all of the components of the audio receiver-amplifier, radio frequency signal detector and capacitance are mounted; a quantity of tissue tolerant plastic material molded about the boa-rd and the components thereon to provide an audio receiver-amplifier and power supply permanently sealed within tissue tolerant material whereby it may be implanted underneath the skin of a wearer thereof.
3. The combination called for in claim 2 wherein a layer of metallic material such as tantalum is provided adjacent the exterior surface of the tissue tolerant material on one side thereof.
4. The combination called for in claim 2 wherein the tissue tolerant material is overlaid with a layer of relatively soft tissue tolerant plastic material such as vinyl plastic.
References Cited bythe Examiner UNITED STATES PATENTS 2,613,282 10/52 Scaife 179--107 2,777,057 1/57 Pankove 325-318 2,813,933 11/57 Williams 179-107 3,003,155 10/61 Mielznski 3-1 3,061,689 10/ 62 McCarr-ell et al 179-107 ROBERT H. ROSE, Primary Examiner. STEPHEN W. CAPELLI, Examiner.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US2613282 *||8 Sep 1949||7 Oct 1952||Alan M Scaife||Spectacle type hearing aid|
|US2777057 *||16 Dec 1952||8 Jan 1957||Rca Corp||Radiation powered transistor circuits|
|US2813933 *||26 May 1953||19 Nov 1957||Alan M Scaife||Hearing aid|
|US3003155 *||6 Jul 1956||10 Oct 1961||Mielzynski Felix C||Hair darts for implanting in live or artificial media|
|US3061689 *||27 May 1957||30 Oct 1962||Beltone Hearing Aid Company||Hearing aid|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US3294988 *||24 Sep 1964||27 Dec 1966||Hewlett Packard Co||Transducers|
|US3346704 *||27 Dec 1963||10 Oct 1967||Jack L Mahoney||Means for aiding hearing|
|US3557775 *||28 Aug 1967||26 Jan 1971||Jack Lawrence Mahoney||Method of implanting a hearing aid|
|US3594514 *||2 Jan 1970||20 Jul 1971||Medtronic Inc||Hearing aid with piezoelectric ceramic element|
|US3662758 *||30 Jun 1969||16 May 1972||Mentor Corp||Stimulator apparatus for muscular organs with external transmitter and implantable receiver|
|US3667477 *||17 Nov 1967||6 Jun 1972||Canadian Patents Dev||Implantable vesical stimulator|
|US3693627 *||14 Sep 1970||26 Sep 1972||American Optical Corp||Stimulator for treatment of tachycardia with a burst of stimuli having a continuously variable rate|
|US3698398 *||6 Nov 1970||17 Oct 1972||American Optical Corp||Rate-scanning pacer for treatment of tachycardia|
|US3751605 *||4 Feb 1972||7 Aug 1973||Beckman Instruments Inc||Method for inducing hearing|
|US3752939 *||4 Feb 1972||14 Aug 1973||Beckman Instruments Inc||Prosthetic device for the deaf|
|US3757794 *||19 Aug 1971||11 Sep 1973||American Optical Corp||Temporary power supply for a heart-stimulating device|
|US3764748 *||19 May 1972||9 Oct 1973||J Branch||Implanted hearing aids|
|US4155366 *||16 May 1977||22 May 1979||Ultra-Aids, Inc.||Method of percutaneous pain alleviation|
|US4250888 *||28 Nov 1978||17 Feb 1981||Carl Zeiss-Stiftung||Heartbeat monitoring process and device|
|US4284856 *||24 Sep 1979||18 Aug 1981||Hochmair Ingeborg||Multi-frequency system and method for enhancing auditory stimulation and the like|
|US4408607 *||13 Apr 1981||11 Oct 1983||Empi, Inc.||Capacitive energy source and circuitry for powering medical apparatus|
|US4432363 *||5 Jan 1981||21 Feb 1984||Tokyo Shibaura Denki Kabushiki Kaisha||Apparatus for transmitting energy to a device implanted in a living body|
|US4441210 *||18 Sep 1981||3 Apr 1984||Hochmair Erwin S||Transcutaneous signal transmission system and methods|
|US4462407 *||5 May 1982||31 Jul 1984||Cordis Corporation||Dual channel cardiac pacer isolation circuit|
|US4549547 *||27 Jul 1982||29 Oct 1985||Trustees Of The University Of Pennsylvania||Implantable bone growth stimulator|
|US4606329 *||22 May 1985||19 Aug 1986||Xomed, Inc.||Implantable electromagnetic middle-ear bone-conduction hearing aid device|
|US4612915 *||23 May 1985||23 Sep 1986||Xomed, Inc.||Direct bone conduction hearing aid device|
|US4629424 *||30 Aug 1984||16 Dec 1986||Integrated Ionics, Inc.||Intraoral ambient sensing device|
|US4774933 *||17 Nov 1987||4 Oct 1988||Xomed, Inc.||Method and apparatus for implanting hearing device|
|US4776322 *||18 Aug 1986||11 Oct 1988||Xomed, Inc.||Implantable electromagnetic middle-ear bone-conduction hearing aid device|
|US4918745 *||9 Oct 1987||17 Apr 1990||Storz Instrument Company||Multi-channel cochlear implant system|
|US5015225 *||17 Mar 1988||14 May 1991||Xomed, Inc.||Implantable electromagnetic middle-ear bone-conduction hearing aid device|
|US5303306 *||25 Nov 1991||12 Apr 1994||Audioscience, Inc.||Hearing aid with programmable remote and method of deriving settings for configuring the hearing aid|
|US5343532 *||9 Mar 1992||30 Aug 1994||Shugart Iii M Wilbert||Hearing aid device|
|US5420930 *||3 Mar 1994||30 May 1995||Shugart, Iii; M. Wilbert||Hearing aid device|
|US5591217 *||4 Jan 1995||7 Jan 1997||Plexus, Inc.||Implantable stimulator with replenishable, high value capacitive power source and method therefor|
|US5735887 *||10 Dec 1996||7 Apr 1998||Exonix Corporation||Closed-loop, RF-coupled implanted medical device|
|US5769877 *||10 Sep 1996||23 Jun 1998||Plexus, Inc.||High value capacitive, replenishable power source|
|US5807397 *||1 Aug 1996||15 Sep 1998||Plexus, Inc.||Implantable stimulator with replenishable, high value capacitive power source and method therefor|
|US6099495 *||30 Apr 1998||8 Aug 2000||Medtronic, Inc.||Implantable electrical transducer powered from capacitive storage energy source|
|US6277148||11 Feb 1999||21 Aug 2001||Soundtec, Inc.||Middle ear magnet implant, attachment device and method, and test instrument and method|
|US6354299 *||30 Jun 2000||12 Mar 2002||Neuropace, Inc.||Implantable device for patient communication|
|US6436028||28 Dec 1999||20 Aug 2002||Soundtec, Inc.||Direct drive movement of body constituent|
|US7372970 *||24 Feb 2005||13 May 2008||Siemens Audiologische Technik Gmbh||Pocket hearing aid|
|US7931582||9 Feb 2001||26 Apr 2011||Obtech Medical Ag||Controlled impotence treatment|
|US8096938||16 Oct 2002||17 Jan 2012||Obtech Medical Ag||Controlled anal incontinence disease treatment|
|US8096939||19 Nov 2009||17 Jan 2012||Obtech Medical Ag||Urinary incontinence treatment with wireless energy supply|
|US8126558||22 May 2006||28 Feb 2012||Obtech Medical Ag||Controlled penile prosthesis|
|US8147544||26 Oct 2002||3 Apr 2012||Otokinetics Inc.||Therapeutic appliance for cochlea|
|US8246532 *||14 Feb 2006||21 Aug 2012||Vibrant Med-El Hearing Technology Gmbh||Bone conductive devices for improving hearing|
|US8287444||29 Apr 2008||16 Oct 2012||Obtech Medical Ag||Mechanical impotence treatment apparatus|
|US8290594||19 Aug 2010||16 Oct 2012||Obtech Medical Ag||Impotence treatment apparatus with energy transforming means|
|US8313423||10 May 2007||20 Nov 2012||Peter Forsell||Hydraulic anal incontinence treatment|
|US8509894||12 Oct 2009||13 Aug 2013||Milux Holding Sa||Heart help device, system, and method|
|US8545384||1 Feb 2010||1 Oct 2013||Obtech Medical Ag||Anal incontinence disease treatment with controlled wireless energy supply|
|US8556796||15 Jan 2010||15 Oct 2013||Obtech Medical Ag||Controlled urinary incontinence treatment|
|US8600510||9 Oct 2009||3 Dec 2013||Milux Holding Sa||Apparatus, system and operation method for the treatment of female sexual dysfunction|
|US8602966||25 Apr 2008||10 Dec 2013||Obtech Medical, AG||Mechanical impotence treatment apparatus|
|US8636809||29 Jan 2009||28 Jan 2014||Milux Holding Sa||Device for treating obesity|
|US8678997||14 Mar 2006||25 Mar 2014||Obtech Medical Ag||Male impotence prosthesis apparatus with wireless energy supply|
|US8696745||12 Oct 2009||15 Apr 2014||Kirk Promotion Ltd.||Heart help device, system, and method|
|US8734318||28 Jun 2006||27 May 2014||Obtech Medical Ag||Mechanical anal incontinence|
|US8764627||10 Sep 2008||1 Jul 2014||Obtech Medical Ag||Penile prosthesis|
|US8874215||9 Oct 2009||28 Oct 2014||Peter Forsell||System, an apparatus, and a method for treating a sexual dysfunctional female patient|
|US8876689||2 Apr 2012||4 Nov 2014||Otokinetics Inc.||Hearing aid microactuator|
|US8929996||11 Mar 2009||6 Jan 2015||Codman Neuro Sciences Sarl||Dual power supply switching circuitry for use in a closed system|
|US8961448||28 Jan 2009||24 Feb 2015||Peter Forsell||Implantable drainage device|
|US9060771||29 Jan 2009||23 Jun 2015||Peter Forsell||Method and instrument for treating obesity|
|US9072907||12 Oct 2009||7 Jul 2015||Peter Forsell||Heart help device, system, and method|
|US9113277||10 Dec 2009||18 Aug 2015||Vibrant Med-El Hearing Technology Gmbh||Skull vibrational unit|
|US9264825||30 Aug 2012||16 Feb 2016||Vibrant Med-El Hearing Technology Gmbh||MRI safe actuator for implantable floating mass transducer|
|US9278158||16 Aug 2007||8 Mar 2016||Peter Forsell||Multi-material incontinence treatment construction device|
|US9370656||25 Aug 2014||21 Jun 2016||Peter Forsell||System, an apparatus, and a method for treating a sexual dysfunctional female patient|
|US9427301||19 Jun 2003||30 Aug 2016||Peter Forsell||Durable implant|
|US9526649||29 Jan 2009||27 Dec 2016||Peter Forsell||Method and instrument for treating obesity|
|US20020051550 *||27 Aug 2001||2 May 2002||Hans Leysieffer||Implantable hermetically sealed housing for an implantable medical device and process for producing the same|
|US20030055311 *||18 Oct 2002||20 Mar 2003||Neukermans Armand P.||Biocompatible transducers|
|US20030125768 *||9 Feb 2001||3 Jul 2003||Forsell Peter||Impotence treatment apparatus with energy transforming means|
|US20050190937 *||24 Feb 2005||1 Sep 2005||Siemens Audiologische Technik Gmbh||Pocket hearing aid|
|US20070191673 *||14 Feb 2006||16 Aug 2007||Vibrant Med-El Hearing Technology Gmbh||Bone conductive devices for improving hearing|
|US20080152173 *||20 Nov 2007||26 Jun 2008||Esonic Co., Ltd||Voice recorder pen|
|US20080200753 *||17 Apr 2008||21 Aug 2008||Potencia Medical Ag||Electrically operable incontinence treatment apparatus|
|US20080200965 *||17 Apr 2008||21 Aug 2008||Potencia Medical Ag||Electrically operable incontinence treatment apparatus|
|US20090228077 *||11 Mar 2009||10 Sep 2009||Codman Neuro Science Sarl||Dual power supply switching circuitry for use in a closed system|
|US20100145135 *||10 Dec 2009||10 Jun 2010||Vibrant Med-El Hearing Technology Gmbh||Skull Vibrational Unit|
|US20150157836 *||20 Feb 2015||11 Jun 2015||Peter Mats Forsell||Implantable drainage device|
|DE2844979A1 *||16 Oct 1978||17 Apr 1980||Mantel Juval||Hearing aid with signals modulated onto radio waves - may include optical radiation for transmission from microphone unit to loudspeaker unit|
|EP0021886A1 *||28 May 1980||7 Jan 1981||Thomson-Csf||Interphone system for radio connections|
|EP2369860B1||13 Feb 2007||23 Sep 2015||VIBRANT Med-El Hearing Technology GmbH||Bone conductive devices for improving hearing|
|WO1983003503A1 *||1 Apr 1982||13 Oct 1983||Norris, Elwood, G.||Pen-size radio|
|U.S. Classification||600/25, 455/100, 381/323, 455/39, 607/33, 381/321, 128/904, 455/351|
|International Classification||A61N1/378, A61N1/372, A61F11/04, H04R25/00|
|Cooperative Classification||A61N1/372, H04R25/502, A61N1/378, Y10S128/904, A61F11/04|
|European Classification||H04R25/50B, A61F11/04, A61N1/378, A61N1/372|