WO1991012783A1 - Heraing assistance device comprising a self-contained direct bone conduction hearing aid implant - Google Patents

Heraing assistance device comprising a self-contained direct bone conduction hearing aid implant Download PDF

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Publication number
WO1991012783A1
WO1991012783A1 PCT/FR1991/000165 FR9100165W WO9112783A1 WO 1991012783 A1 WO1991012783 A1 WO 1991012783A1 FR 9100165 W FR9100165 W FR 9100165W WO 9112783 A1 WO9112783 A1 WO 9112783A1
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WO
WIPO (PCT)
Prior art keywords
hearing aid
hearing
means
characterized
prosthesis
Prior art date
Application number
PCT/FR1991/000165
Other languages
French (fr)
Inventor
Roger Tari
Roland Demartelaere
Original Assignee
Roger Tari
Roland Demartelaere
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority to FR90/02985 priority Critical
Priority to FR9002985A priority patent/FR2659009A1/en
Application filed by Roger Tari, Roland Demartelaere filed Critical Roger Tari
Publication of WO1991012783A1 publication Critical patent/WO1991012783A1/en

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Classifications

    • HELECTRICITY
    • H04ELECTRIC COMMUNICATION TECHNIQUE
    • H04RLOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/60Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
    • H04R25/604Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers
    • H04R25/606Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers acting directly on the eardrum, the ossicles or the skull, e.g. mastoid, tooth, maxillary or mandibular bone, or mechanically stimulating the cochlea, e.g. at the oval window
    • HELECTRICITY
    • H04ELECTRIC COMMUNICATION TECHNIQUE
    • H04RLOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2460/00Details of hearing devices, i.e. of ear- or headphones covered by H04R1/10 or H04R5/033 but not provided for in any of their subgroups, or of hearing aids covered by H04R25/00 but not provided for in any of its subgroups
    • H04R2460/13Hearing devices using bone conduction transducers

Abstract

A hearing assistance device comprising a direct bone conduction hearing aid (6) operating on an electrical supply and including a means (10) for generating vibrations and transmitting them directly to the mastoid bone, and a means for receiving and converting sounds (5) into analog signals, then processing these signals according to the needs of the hearing-impaired person before their transmission to said vibration generator (10). Said hearing aid (6) is self-contained, can be implanted and positioned beneath the skin, and includes rechargeable accumulator batteries (12) combined with a receptive induction coil to carry out said recharging by means of an alternating magnetic field generator (13) which is preiodically placed next to said hearing aid (6).

Description

"An hearing aid comprising a hearing aid implanted, self-contained direct bone conduction"

DESCRIPTION

The present invention relates to a hearing aid device having an implanted hearing aid, self-contained direct bone conduction.

The technical scope of the invention is the manufacturing of hearing aids by stimulating vibrations scalp in the mastoid region.

various types of hearing aids that can be classified in effect are known in three categories: those for correcting profound deafness include electrodes implanted in the cochlea and transmitting electrical signals to the auditory nerve fibers located therein ; these prostheses called bionic ears are made for that one hand of an external device equipped with a microphone that picks up sound, and the electronics that break them into electrical signals of different frequencies, and also of these electrodes are connected to said electronic circuit either directly or by induction through the skin, and which are placed on a gate electrode located outside or inside the cochlea during surgery. Mention may be made in the settlements intracochlear Patent Application GB 2,383,657 A. (Bertin et Cie and Al), which describes an electronic equipment hearing aid comprising an external transmitter which is inductively coupled to a receiver implant comprising an electrode carrier intracochlear.

Also known is patent application EP 0007157 A3 (University of Melbourne) which discloses electrode carrier for implantation in the human cochlea, comprising a flexible tube, around which are wound regularly spaced electrodes made, for example, platinum sheets.

In the area of ​​extracochlear settlements, there is also the patent application FR 2587221 Mr A. H0URI filed January 31, 1985 an "implant system extracochlear to change the amount of excitation current by pulse width modulation. these types of implants are very difficult to implement e share the necessary surgical precision and technicality of the effectiveness of the electrode: they are reserved for living beings profound deafness with which the sensory hair cells of the cochlea are deficient and why hearing aids of the following categories that have the effe increase acoustic energy have no effect.

The acoustic waves that may be recalled indeed SLA are picked up by the pinna and returned by the eardrum that transmits the bones and the liquid of the inner ear that exitent to "turn said sensory hair cells of cochlea.

- those intended in particular to correct the presbycusis (sensorineural hearing loss in the elderly) are air conduction and consist of an amplification of the sound signa from a microphone to a speaker disposed in the bottom external auditory CONDUCT BEHAVIOR. Their disadvantages of being visible e irritate 'the ear canal.

Some systems, however, were developed to mitigate c problem by improving speech understanding by adapting the frequency of it at the optimum field understanding of the person can be cited in this regard the patent application FR 2294606 filed 09 December 1974 by MESSIEUR Guberina and ARAMBASIN. But even if these prostheses are effective in the case of sensorineural hearing loss and presbycusis, they prove no suitable in transmission deafness for which we used the last category below in which the present invention is located. - those using the principle of osseus conduction are shown only in the deafness of transmission. Even within these prostheses, there are:

- prostheses which the vibrator is disposed in contact with the scalp cui in the mastoid region held by a device typ headband or branches of spectacles. Their effectiveness Etan proportional to the pressure exerted it is therefore before u dual problem. good efficiency results in poor tolerance (pain and skin lesions)

. good tolerance reduces efficiency. In addition, they are unsightly in all cases. - bone prostheses direct transmission of which the vibrator is disposed against or in the mastoid bone require major surgery (devices screwed into the bone) .. In addition, all the prostheses of this type existing to date, consist of two parts, an implanted comprising the vibratory device, and a non-implanted external comprising the active portion of the prosthesis (micro feeding settings and amplification).

for example include in this category the US patent application 3870832 filed on 29.07.1974 under priority of a British patent by Mr. J. FREDICKSON on "Electromagnetic implaήtable hearing aid" and patents FR 2,586,557 and 2,586,216 deposited 21 and 22 March, 1986 under priority US BRISTOL MYERS CY respectively on the one hand an "electromagnetic device implantable in the temporal bone (which approximates actually of the first type in this case) of hearing aid by bone conduction in the middle ear ", and secondly a" hearing aid to direct bone conduction "screwed into the bone and that the external device is in a housing carried, for example in a pocket of the person concerned.

It appears in this last category that interests us no device to date is fully implanted and autonomous, with all the elements necessary for its operation and its autonomy: this requires in particular passages son or parts through the skin, which is of infection and discomfort points. The problem is therefore to provide a device for hearing aid that allows the implementation of all these elements and ensuring good efficacy of hearing aid.

A solution to the problem is a hearing aid device with a hearing aid to direct bone conduction, operating with a power supply and comprising a vibration generating means transmitted directly to the mastoid bone and receiving means and converting sounds into analog signals, then processing these to be adapted to the needs of hearing handicap before being transmitted to said vibration generator; said hearing aid is self-contained, implantable and placed in subcutaneous position, and comprises a rechargeable battery associated with a receiving inductor for charging said through an alternating magnetic field generator positioned episodically proximate said prosthesis .

In one embodiment, said prosthesis comprises means for receiving signals from a remote control transmitter. and one of said signal processing circuit for modifying the characteristics of the prosthesis according to the needs of hearing handicap wearer.

Preferably the means for receiving sounds is a microphone that is placed under the front of the skin of the bowl of the ear, to the location of a piece of cartilage removed beforehand to allow slot.

And in a preferred embodiment the means for receiving sounds is the same as that of reception of remote control signals.

The result is new assistive listening devices comprising a hearing aid, implanted, self-contained direct bone conduction.

The indication of this bone conduction implant in cases of sensorineural hearing loss, ie with anatomical and functional integrity of tympanoossicular system allows:

- not to be influenced by the recruitment phenomenon, which is formed by the narrowing of the gap between the lininaire tonal threshold and the contraction threshold stirrup muscle (protective phenomenon of the inner ear). This is still very troublesome in the case of air conduction prosthesis and does not always provide sufficient gain.

- in the frequency range most commonly affected and most useful (> 1kHz). to use the bone conduction by compression and not the bone conduction by inertia (<500 Hz) and therefore use very advantageously inertia vibration of the whole of the ossicular chain. Interesting solutions provided by the present invention and as described below are of two types:

- solutions linked to its implantability

- electronic solutions related to its functioning and its autonomy.

The advantages of these solutions bring ease of use to their users with undisturbed external physical appearance. Indeed, nothing is detectable outside a small change in the area since there are no external wire, which also removes the risk of infection.

In addition, the system is autonomous for a certain period and can be easily recharged 1'extérieur without surgery. The subject is free to move, unhindered by external power. The preferred position of the microphone in the headliner or bowl of the ear is a discrete sides most effective part since the shape of the ear is naturally optimum to capture the sounds again, the subject then keeps concept of directivity of the origin of these, whereas for microphones placed in other parts of his body, they capture some all sounds and can hinder the subject in its concentration directive listening.

Another advantage is to be able to dissociate the acoustic vibration generating means by fixing the removable on an intermediate piece which itself is fixed permanently to said mastoid bone, which in case of repair avoids trauma again this bone and can be achieved without major surgery.

One could cite other advantages of the present invention, but those mentioned above already suffice to demonstrate the novelty and interest. The description, drawings and figures below represent one embodiment of the invention but have no limiting character: other embodiments are possible from the claims which define the scope and extent of this invention. Figure 1 is a horizontal section of an outer ear.

Figure 2 is a vertical section of an outer ear.

FIG 3 is a diagram of the prosthesis and its external devices. ,

Figure 1 shows the area implantability 1 horizontal section of an ear 2. Being a bone conduction aid, the vibratory device must be in contact with the mastoid bone 3. implantation area is the mastoid area behind the ear.

Surgical of this double-ear area is known first and it shows in the form of an osteochondral dihedral angle.

Bone face 3 of this dihedral angle will be to receive the vibratory device 10. cartilage 4 face will receive the microphone 5. The microphone fits in a housing created by resection or removal of a cartilage disc the same diameter respecting anterior skin of the concha as figured in section in Figure 2.

The prosthesis thus fills this dihedral angle. Its entirety as described in Figure 3 and their protection are embedded in a flexible material, non-traumatic and biocompatible, such as that designated by the trademark "silastene".

Opposite the active elements that are the vibratory device 10 (buzzer or vibrator) and the microphone 5, the thickness of the biocompatible material forming the shell will be reduced so as not to interfere with their operation. In another variation, the biocompatible material with respect to these elements will advantageously be replaced by a still biocompatible film of a different nature than that above.

The vibrator 10 to be intimately fixed to the bone will be fixed or removable hinged on a device stuck to the bone to its removability, or in another variant, if not possible, directly bonded to the bone.

Figure 3 shows a diagram of the device with the implanted prosthesis 6 includes all the elements necessary for its operation and its autonomy, and external devices allow it autonomy and setup.

The implanted unit 6 is composed of: a device 7 for supplying electric power to ensure the autonomy the prosthesis 6,

- the microphone 5,

- a preamplifier assembly 8 and an amplifier 9 as well known type,

- the vibrateu-r 10,

- a remote control receiver 11.

A hearing aid requires electrical power which is usually supplied by a battery. The consumption of the prosthesis' first, and secondly miniaturization worries, lead to the use of batteries whose capacity allows only range of about 48 H. In addition, it is necessary replaced.

This obviously can not be considered for an implanted device and the device according to the invention to remedy. It comprises in fact, according to these characteristics, a rechargeable battery 12 providing a range of a few tens of hours.

According to another characteristic of the invention, the battery charging is carried out as follows: an outer device 13 mainly composed of an electric oscillator 14 supplying an induction coil 15 produces an alternating magnetic flux.

The prosthesis includes an induction coil 16 and electronic rectifying circuits 17 connected to the battery 12.

The alternating magnetic flux produced by the external device 13 induced in this winding an alternating electrical power which, when rectified, recharge the battery 12.

The winding of the external device and the coil 6 located in the prosthesis are in fact the primary and the secondary of a transformer static. This charging can be done during the night, the winding of the external device being placed in proximity of the prosthesis, for example in a pillow.

According to particular embodiments:

- the primary winding 15 emitter of magnetic flux can be small in size, placed in position on the skin side to the secondary winding 16, magnetic flux receiver in the prosthesis 6, - the primary winding may be maintained in its position on -cutanée by adhesive means,

- primary winding can be maintained in its position on the skin by magnetic means: a permanent magnet is in place in the prosthesis, another permanent magnet is in place in the transmitting device. The poles of each magnet facing opposed, attraction now produced the transmitter in place. One of the two magnets can be replaced by a ferromagnetic element. - the external device 13, the transmitter magnetic flux can be supplied by a rechargeable battery 18 and comprises the circuits necessary to recharge the battery on the network. The advantage of this system is to provide a safe and an additional guarantee for charging of the prosthesis in case of power failure or non-availability of the electricity grid.

The microphone 5 type broadband picks up sounds to be amplified, but also can capture ultrasound for the remote. According to another characteristic of the invention, the microphone being protected by a thin protective film of a biocompatible material, picks up sound waves through the thin skin depth of the concha without significant attenuation in the usable frequency band. In addition, placed in the shell, it will keep its physiological role in roof-sensor locator sounds. The electrical signals produced by the microphone are transmitted to the preamplifier amplifier 8 and 9, the amplification and frequency compensation characteristics allow the vibrator 10 to provide electrical signals of magnitude as required by the hearing aid to perform . Optional. this electronic assembly may include a safety device according to: a pressure switch with two stable positions (start-stop) placed in series with the battery 12 allowing the user a complete disconnection of the battery.

This switch is covered with the protection of the biocompatible material and activated by finger pressure on the skin.

In addition, this electronic assembly may include an automatic disconnection device of the amplifier, while the absence of sounds picked up by the microphone for a few seconds and return to service of the amplifier in the presence of sounds.

This device allows an important saving of energy provided by the battery 12. The electrical signals from the amplifier, analogically reproduce sounds are transmitted to the vibrator 10 of the type for example piezoelectric via a device impedance transformer.

In a preferred embodiment, the vibrator 5 is mounted detachably on a piece of biocompatible metal material (orthopedic prosthesis material type), which piece. it is screwed or glued to the mastoid by using a bone cement, allowing removability of the prosthesis. In another variation, if not possible at the discretion of the skilled person, it will be directly screwed or glued to the bone.

The vibrator 10 which may be piezoelectric or electromagnetic type. usually circular. may advantageously have a surface of different shape, for example lliptique for better yields and low frequency transmissions.

Furthermore, a remote control receiver 19, ultrasound is used to adjust the characteristics of the prosthesis by 1'audioprothésiste depending on the type of correction to be made, and make it accessible to the user the usual functions power adjustment. It can be adapted more in case of changes of deafness.

The remote control device 19 comprises a transmitter 2 to ultra¬ sound coded with a generator 20 and a controller 22. The signals are picked up by the microphone 5 to broadband through the skin and protection with an attenuation that is believed with frequency.

The frequency ultrasound can be selected in the bands 20-25 kHz. This device is already used in some hearing aids intra-led non-implanted. According to a particular embodiment, the hearing aid consists of a printed circuit carrying integrated circuits for amplification and remote control reception, recovery of the components of the power supply and other electronic components, according to the scheme of the Figure 3.

The microphone 5 can be of type "Electret" Omnidirectional effect whose diameter is approximately 3 mm, is arranged perpendicularly to the prosthesis support but without rigid fixation to allow its positioning according to anatomical variations. The own bandwidth microphone is preferably greater than 25 kHz (- 3 dB). The presence of the skin and the protective film do not cause substantial attenuation up to 8 kHz. For against, to 23 kHz, which can be the frequency of the remote control, the attenuation is 12 dB.

The vibrator 10 which may be piezo-electric type, the dimensions can be for the diameter of about 35 mm and the thickness of about 1.7 mm, may have the following characteristics: bandwidth 600 Hz-20 kHz. Impedance 600 ohms at 1 kHz. It can be fixed to the support 6 of the prosthesis on its periphery by a kind of microfiletage ring system 1/8 or 1/4 turn, or in another embodiment by a system of pegs.

The induction coil 16 may comprise 400 turns of copper wire enameled of 6/100 mm. It is secured preferably by gluing to the periphery of the support of the prosthesis 6 to increase its section. In another variant, it can be printed in the circuit.

The battery 12 may be cadmium-nickel type, with a nominal voltage of about 1.2 volts and a capacity of 30 mA / h.

The electronic assembly described above is coated with an impermeable protective film and a flexible biocompatible material.

The support on which can articulate the vibrator 10 is external to all homogeneous as is the prosthesis 6. This is the only element that is attached to the mastoid 3 by screwing, adhesive or surgical cement.

It is in the form of a biocompatible alloy ring (orthopedic prosthesis material type), of diameter equal to that of the vibrator 10. One side of this ring is intended for fastening on the mastoid by using e.g. surgical glue or cement and the other face being intended to the joint with the vibration of the prosthesis, for example by microfiletage 1/8 or 1/4 turn or in another alternative by lugs.

Claims

1 - Device for hearing aid comprising a hearing prothès (6) to direct bone conduction, operating with a power supply and comprising a generating means (10) of vibrations transmitted directly to the mastoid bone and d receiving means and converting the sounds (5) into analog signals, pui processing thereof to be adapted to the needs of the hearing impaired before being transmitted to said vibration generator (10 characterized in that: - said auditory prosthesis ( 6) is independent, capable andR implanted and placed in subcutaneous position, and comprises a storage batteri (12) rechargeable associated with a coil (16 for receiving said refill induction through u generator (13) field, magnetic alternative episodically placed close to said prosthesis (6).
2 - An hearing aid according to claim characterized in that said prosthesis comprises means (5) for receiving signals from a transmitter REMOTE (19), and a processing circuit (11) of said signals enabling to modify the characteristics of the prosthesis (6) according to the needs of the hearing handicap wearer.
3 - A device for assisting the hearing according to any one of claims 1 and 2 characterized in that the receiving means (5 sound is a microphone which is placed under the skin of the anterior fac of the concha (4 ) of the ear, to the location of a previously removed cartilage morcea to allow slot.
4 - An hearing aid according to any one of claims 2 and 3 characterized in that the means of Receptio sounds (5) is the same as that of reception of remote control signals.
5 - An hearing aid according to any one of claims 1 to 4 characterized in that said generating means (10 sound vibrations transmitted to the mastoid bone (3) is a piezoelectric type vibrateu. 6 - an hearing aid according to any one of claims 1 to 4 characterized in that said generator means (10) of sound vibrations transmitted to the mastoid bone (3) is a vibrateu of electromagnetic type.
7 - A device for assisting the hearing according to any one of claims 1 to 6 characterized in that said generator means (10) of sound vibrations is fixed detachably to an intermediate piece which itself is fixed in a manner said permanent mastoid bone (3).
PCT/FR1991/000165 1990-03-02 1991-03-01 Heraing assistance device comprising a self-contained direct bone conduction hearing aid implant WO1991012783A1 (en)

Priority Applications (2)

Application Number Priority Date Filing Date Title
FR90/02985 1990-03-02
FR9002985A FR2659009A1 (en) 1990-03-02 1990-03-02 An assistive listening device comprising a hearing aid implanted, self-contained direct bone conduction.

Publications (1)

Publication Number Publication Date
WO1991012783A1 true WO1991012783A1 (en) 1991-09-05

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PCT/FR1991/000165 WO1991012783A1 (en) 1990-03-02 1991-03-01 Heraing assistance device comprising a self-contained direct bone conduction hearing aid implant

Country Status (3)

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AU (1) AU7487891A (en)
FR (1) FR2659009A1 (en)
WO (1) WO1991012783A1 (en)

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2003001846A1 (en) * 2001-06-21 2003-01-03 P & B Research Ab Hearing aid apparatus
US8144909B2 (en) 2008-08-12 2012-03-27 Cochlear Limited Customization of bone conduction hearing devices
US8532322B2 (en) 2008-03-31 2013-09-10 Cochlear Limited Bone conduction device for a single sided deaf recipient
US9479879B2 (en) 2011-03-23 2016-10-25 Cochlear Limited Fitting of hearing devices

Families Citing this family (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1997044987A1 (en) * 1996-05-24 1997-11-27 Lesinski S George Improved microphones for an implantable hearing aid
EP1596629A3 (en) * 1996-05-24 2011-09-21 S. George Lesinski Electronic module for implantable hearing aid
ES2493666B1 (en) * 2013-03-12 2015-06-25 Álvaro SAINZ AGUIRRE System for temporary air sound transmission with means to secure it to the ear

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3557775A (en) * 1963-12-27 1971-01-26 Jack Lawrence Mahoney Method of implanting a hearing aid
EP0175909A1 (en) * 1984-08-28 1986-04-02 Siemens Audiologische Technik GmbH Hearing aid device
EP0176116A2 (en) * 1984-09-27 1986-04-02 Philips Electronics N.V. Remote control system for hearing aids
US4904233A (en) * 1985-05-10 1990-02-27 Haakansson Bo Arrangement in a hearing aid device

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3557775A (en) * 1963-12-27 1971-01-26 Jack Lawrence Mahoney Method of implanting a hearing aid
EP0175909A1 (en) * 1984-08-28 1986-04-02 Siemens Audiologische Technik GmbH Hearing aid device
EP0176116A2 (en) * 1984-09-27 1986-04-02 Philips Electronics N.V. Remote control system for hearing aids
US4904233A (en) * 1985-05-10 1990-02-27 Haakansson Bo Arrangement in a hearing aid device

Cited By (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2003001846A1 (en) * 2001-06-21 2003-01-03 P & B Research Ab Hearing aid apparatus
US7043040B2 (en) 2001-06-21 2006-05-09 P&B Research Ab Hearing aid apparatus
US8532322B2 (en) 2008-03-31 2013-09-10 Cochlear Limited Bone conduction device for a single sided deaf recipient
US8731205B2 (en) 2008-03-31 2014-05-20 Cochlear Limited Bone conduction device fitting
US9955270B2 (en) 2008-03-31 2018-04-24 Cochlear Limited Bone conduction device fitting
US8144909B2 (en) 2008-08-12 2012-03-27 Cochlear Limited Customization of bone conduction hearing devices
US9479879B2 (en) 2011-03-23 2016-10-25 Cochlear Limited Fitting of hearing devices
US10412515B2 (en) 2011-03-23 2019-09-10 Cochlear Limited Fitting of hearing devices

Also Published As

Publication number Publication date
FR2659009A1 (en) 1991-09-06
AU7487891A (en) 1991-09-18

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