EP0400630A2 - Prothèse auditive avec implantation - Google Patents

Prothèse auditive avec implantation Download PDF

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Publication number
EP0400630A2
EP0400630A2 EP90110307A EP90110307A EP0400630A2 EP 0400630 A2 EP0400630 A2 EP 0400630A2 EP 90110307 A EP90110307 A EP 90110307A EP 90110307 A EP90110307 A EP 90110307A EP 0400630 A2 EP0400630 A2 EP 0400630A2
Authority
EP
European Patent Office
Prior art keywords
hearing aid
aid according
housing
transducer
tube
Prior art date
Legal status (The legal status 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 status listed.)
Granted
Application number
EP90110307A
Other languages
German (de)
English (en)
Other versions
EP0400630B1 (fr
EP0400630A3 (fr
Inventor
Günter Hortmann
Hans Dr.-Ing. Leysieffer
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Sonova Holding AG
Original Assignee
Hortmann GmbH
Implex Spezialhorgerate GmbH
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
Application filed by Hortmann GmbH, Implex Spezialhorgerate GmbH filed Critical Hortmann GmbH
Publication of EP0400630A2 publication Critical patent/EP0400630A2/fr
Publication of EP0400630A3 publication Critical patent/EP0400630A3/fr
Application granted granted Critical
Publication of EP0400630B1 publication Critical patent/EP0400630B1/fr
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

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Classifications

    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Electric hearing aids
    • H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
    • H04R25/604—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers
    • H04R25/606—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers acting directly on the eardrum, the ossicles or the skull, e.g. mastoid, tooth, maxillary or mandibular bone, or mechanically stimulating the cochlea, e.g. at the oval window

Definitions

  • the invention relates to an implantable hearing aid for stimulating the inner ear.
  • the assemblies forming the hearing aid including a tritium battery, are inserted hermetically encapsulated in the external auditory canal or implanted in the mastoid, and the hearing aid is connected directly to the auditory nerve on the output side via an electrical line connected.
  • acoustic vibrations that are generated by the hearing aid implanted in the mastoid are transmitted via the mastoid bone process into the middle ear, taking advantage of the fact that it has cavities that pass through the atrial window with the middle ear Connect.
  • a microphone, an amplifier, a battery, a volume control and an excitation coil for a magnet are accommodated in a housing to be inserted into the external auditory canal, which is attached to one of the ossicles.
  • a hearing aid is also known (GB-PS 1 440 724), in which a microphone, an amplifier and a battery are arranged in a housing which is plug-like inserted into a base which is implanted in the temporal bone behind the ear cup. The output signal of the amplifier goes to an excitation coil implanted in the middle ear of a magnet attached to the stirrup.
  • a hearing aid is known (US Pat. No. 4,532,930), in which an electrical stimulation of the inner ear takes place directly via an implantable electrode arrangement with the aid of signals provided by appropriate signal processing electronics.
  • the signal processing electronics are housed in a relatively large-volume housing, the external in a separate Bag is carried.
  • the signal processing electronics are connected via a connecting cable to a transmitting antenna which is arranged in the area of the ear concerned.
  • the invention has for its object to provide an implantable hearing aid for stimulating the inner ear, which has a high sound quality and allows a relatively simple and risk-free use.
  • the hearing aid has a hydromechanical coupling element connected on the input side to an electromechanical transducer for transmitting the mechanical vibrations generated by the transducer to the inner ear.
  • the hydromechanical coupling element can simply have a liquid-filled hose connected to the electromechanical transducer, the end of which extends from the transducer in the implanted state and extends into the fluid-filled inner ear spaces.
  • the electromechanical transducer is advantageously hermetically encapsulated for implantation in the tympanic cavity or in the mastoid.
  • the tube is advantageously filled with a lymph-like liquid and closed at the end remote from the transducer with a thin membrane. He can by means of a wire coil pushed on or by one or more wires embedded in the hose wall according to the respective anatomical conditions are permanently shaped.
  • the electromechanical transducer can be integrated in a housing of implantable signal processing electronics and based on the electrodynamic, electromagnetic or, preferably, piezoelectric principle.
  • the transducer can have a piezoelectric flexural oscillator which is seated on a carrier membrane which is clamped in the housing accommodating the transducer.
  • the bending oscillator can consist of a single-layer piezoelectric disk or have a bimorph structure symmetrical to the support membrane, and it advantageously has a diameter which corresponds to at least 0.8 times and preferably at least 0.9 times the inside diameter of the associated housing.
  • a large ratio of the transducer disc diameter to the inner tube diameter results in a rapid transformation which, even with small electrical transducer outputs, can result in high outlet pressures at the end of the tube lying away from the transducer.
  • a microphone supplying the electromechanical transducer via signal processing electronics with input signals is connected to an acoustic coupling element for sound absorption from the tympanic cavity, thereby fully utilizing the natural directional characteristic of the outer ear.
  • the acoustic coupling element can simply be designed as a switching line hose connected to the microphone, the end of which facing away from the microphone projects into the tympanic cavity in the implanted state and is expediently closed with a membrane.
  • the hearing aid shown in FIG. 1 has a hermetically sealed housing 12 which can be implanted in the vicinity of the ear 10 in question, in particular in the mastoid 11, in which, as schematically indicated, a microphone 13, signal processing electronics 14 and a power supply, for example a Secondary cell arrangement 15 (ie one or more rechargeable batteries) are accommodated.
  • the microphone 13 is connected to the tympanic cavity 17 via an acoustic coupling element in the form of a sound line hose 16.
  • the end of the switching line tube 16 facing away from the microphone 13 extends into the tympanic cavity 17 in the implanted state, and it is closed there by means of a thin membrane 18.
  • An electromechanical transducer 21 is connected to the output of the signal processing electronics 14 via a transducer feed line 20 and is mechanically fixed in a hermetically sealed manner in the tympanic cavity behind the eardrum 22.
  • the converter 21 is in turn connected to a hydromechanical coupling element 23. Mechanical vibrations are transmitted from the transducer 21 to the inner ear 24 via the coupling element 23.
  • the coupling element 23 extends through a bore in the stirrup foot plate 25.
  • sound signals pass through the outer ear 26, the auditory canal 27 and the eardrum 22 to the tympanic cavity 17. They are picked up there by the sound conduit hose 16 behind the eardrum 22 and passed on to the microphone 13 seated in the housing 12.
  • the microphone 13 converts the sound into electrical microphone signals. These signals are converted into suitable output signals in the signal processing electronics 14 and are increasingly fed to the electromechanical converter 21 via the converter feed line 20.
  • the converter 21 converts the electrical output signals into mechanical vibrations. The mechanical vibrations are transmitted to the fluid-filled inner ear spaces via the hydromechanical coupling element 23.
  • the hearing aid is completely implanted.
  • the wearer is not affected by the device under normal everyday conditions. For example swimming is easily possible.
  • the natural directional characteristic of the outer ear 26 is fully utilized and is not impaired by mechanical elements in the outer auditory canal 27.
  • the natural transmission via the ossicular chain 28 remains unaffected. This minimizes the risk for the patient.
  • An external control signal transmitter 30 can be provided for selectively setting one or more characteristic values of the signal processing electronics 14, to whose output a transmission coil 31 is connected.
  • a reception coil 32 is accommodated in the housing 12.
  • high-frequency inductive data transmission between the external control signal generator 30 and the implanted signal processing electronics 14 can take place via the coils 31 and 32 if necessary.
  • the high-frequency link provided for the inductive data transmission can also expediently be used to transmit energy for charging the implanted secondary cell arrangement 15.
  • a light-bound infrared path can also be provided for transcutaneous data transmission between the control signal generator 30 and the signal processing electronics 14.
  • the converter 21 has a two-part, hermetically sealed housing 34.
  • a preferably circular piezoelectric bending oscillator 35 is accommodated in the housing 34 and sits on a carrier membrane 36.
  • the support membrane 36 which is preferably made of brass or aluminum, is clamped approximately centrally at its edge in the housing 34.
  • the illustrated flexural vibrator 35 has a bimorph structure symmetrical to the support membrane 36, the two layers of which are designated 37 and 38.
  • the layers 37, 38 can be electrically connected in parallel or in series. The two or, in the case of electrical parallel connection, three electrode surfaces of the layers 37, 38 are contacted and connected to the transducer feed line 20 through housing bushings.
  • the bending oscillator 35 consists of a single-layer piezoelectric Disc exists.
  • the bending vibrator 35 expediently has a diameter which corresponds to at least 0.8 times and preferably at least 0.9 times the inside diameter of the housing 34.
  • the carrier membrane 36 divides the interior of the housing 34 into two chambers 39 and 40.
  • One chamber 39 is filled with a liquid 41, the density and composition of which at least approximately correspond to the perilymph (the liquid in the inner ear).
  • a connection piece 42 is guided through a wall of the housing 34, via which pressure fluctuations generated by the transducer vibration are directed to a hose 43 forming the hydromechanical coupling element 23.
  • the tube 43 is filled with the same liquid as the chamber 39, and its end remote from the transducer 21 is closed by means of a thin membrane 44.
  • the tube 43 can expediently consist of biocompatible silicone, and it advantageously has an outer diameter of 0.3 to 1.0 mm, preferably approximately 0.6 mm, and a wall thickness of 0.05 to 0.3 mm, preferably approximately 0. 1 mm.
  • the converter housing 34 is circular or approximately circular, and it expediently has a diameter of 5 to 10 mm, preferably about 8 mm.
  • the housing 34 can advantageously consist of a biocompatible ceramic, for example Al2O3, or of titanium.
  • the other chamber 40 of the housing 34 is filled with an inert gas, preferably argon.
  • the wire helix makes it possible to achieve a constant formation of bending radii to adapt to the respective anatomical conditions.
  • one or more wires, preferably platinum wires, can also be embedded in the wall of the hose 43.
  • the essential effect of the arrangement illustrated in FIG. 2 is based, on the one hand, on the principle of a pressure chamber, by means of which a rapid transformation occurs with a large ratio of converter disk diameter to hose inside diameter, which enables high output pressures on the hose membrane 44 in the case of small electrical converter powers.
  • the filling of the tube 43 with a lymph-like liquid allows an optimal mechanical impedance adaptation to the inner ear. This prevents annoying reflections.
  • the electromechanical converter 21 is also integrated in the housing 12 of the signal processing electronics 14.
  • the liquid-filled chamber 39 is connected to the hydromechanical coupling element 23 in the form of the liquid-filled hose 43, analogously to FIG. 2.
  • the microphone 13 and the power supply for example a secondary cell arrangement 15, are also accommodated in the housing 12.
  • the sound is fed to the microphone 13 from the tympanic cavity 17 via the formwork tube 16.
  • the latter is connected to the housing 12 via a connecting piece 46 and terminated at its free end by means of the thin membrane 18.
  • the microphone 13 is suspended in the housing 12 so that it is isolated in terms of vibration. As indicated in FIG. 3, the microphone 13, the signal processing electronics 14 and the energy supply 15 are seated in a third chamber 48, which is separated from the gas-filled chamber 40 by means of a partition 47. At least some of these modules can also be accommodated in the chamber 40 if necessary .
  • a primary cell arrangement can also be provided for the energy supply, which is accommodated in a housing which is separate from the housing 12 of the signal processing electronics 14 and is connected to the signal processing electronics 14 via a separable connection.
  • the primary cell arrangement one or more batteries
  • the primary cell arrangement can be replaced if necessary, without a simultaneous exchange of the housing 12 or an intervention in this housing being necessary.
  • the microphone 13 receiving the sound from the tympanic cavity 17 in a separate housing which is fixed directly in the tympanic cavity 17 during the implantation.
  • the microphone 13 picks up the sound from the tympanic cavity via a nozzle which is guided through the housing and is sealed off with a thin membrane for sealing.

Landscapes

  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Otolaryngology (AREA)
  • Neurosurgery (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Prostheses (AREA)
EP90110307A 1989-06-02 1990-05-30 Prothèse auditive avec implantation Expired - Lifetime EP0400630B1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE3918086A DE3918086C1 (fr) 1989-06-02 1989-06-02
DE3918086 1989-06-02

Publications (3)

Publication Number Publication Date
EP0400630A2 true EP0400630A2 (fr) 1990-12-05
EP0400630A3 EP0400630A3 (fr) 1992-08-05
EP0400630B1 EP0400630B1 (fr) 1995-08-02

Family

ID=6381974

Family Applications (1)

Application Number Title Priority Date Filing Date
EP90110307A Expired - Lifetime EP0400630B1 (fr) 1989-06-02 1990-05-30 Prothèse auditive avec implantation

Country Status (4)

Country Link
US (1) US5411467A (fr)
EP (1) EP0400630B1 (fr)
DE (3) DE3940632C1 (fr)
DK (1) DK0400630T3 (fr)

Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5814095A (en) * 1996-09-18 1998-09-29 Implex Gmbh Spezialhorgerate Implantable microphone and implantable hearing aids utilizing same
US6565503B2 (en) 2000-04-13 2003-05-20 Cochlear Limited At least partially implantable system for rehabilitation of hearing disorder
US6629923B2 (en) 2000-09-21 2003-10-07 Phonak Ag At least partially implantable hearing system with direct mechanical stimulation of a lymphatic space of the inner ear
US6697674B2 (en) 2000-04-13 2004-02-24 Cochlear Limited At least partially implantable system for rehabilitation of a hearing disorder
US7376563B2 (en) 2000-06-30 2008-05-20 Cochlear Limited System for rehabilitation of a hearing disorder
DE102016107517B4 (de) 2016-04-22 2019-06-06 Medizinische Hochschule Hannover Mittelohrimplantat

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* Cited by examiner, † Cited by third party
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US5282858A (en) * 1991-06-17 1994-02-01 American Cyanamid Company Hermetically sealed implantable transducer
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US5772575A (en) * 1995-09-22 1998-06-30 S. George Lesinski Implantable hearing aid
CA2236743C (fr) * 1995-11-13 2007-06-05 Cochlear Limited Microphone implantable pour implants cochleaires et autres dispositifs du meme type
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DE19618961B4 (de) * 1996-05-10 2004-09-16 Phonak Ag Gerät zur elektromechanischen Stimulation und Prüfung des Gehörs
DE69733837T2 (de) * 1996-05-24 2006-04-27 Lesinski, S. George, Cincinnati Verbesserte mikrophone für implantierbares hörhilfegerät
EP1596629A3 (fr) * 1996-05-24 2011-09-21 S. George Lesinski Module électronique pour une prothèse auditive implantable
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EP0400630B1 (fr) 1995-08-02
DK0400630T3 (da) 1995-09-18
DE3918086C1 (fr) 1990-09-27
DE59009461D1 (de) 1995-09-07
EP0400630A3 (fr) 1992-08-05
US5411467A (en) 1995-05-02
DE3940632C1 (en) 1990-12-06

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