EP0400630B1 - Implantable hearing aid - Google Patents

Implantable hearing aid Download PDF

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Publication number
EP0400630B1
EP0400630B1 EP90110307A EP90110307A EP0400630B1 EP 0400630 B1 EP0400630 B1 EP 0400630B1 EP 90110307 A EP90110307 A EP 90110307A EP 90110307 A EP90110307 A EP 90110307A EP 0400630 B1 EP0400630 B1 EP 0400630B1
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EP
European Patent Office
Prior art keywords
hearing aid
aid according
transducer
housing
filled
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.)
Expired - Lifetime
Application number
EP90110307A
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German (de)
French (fr)
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EP0400630A2 (en
EP0400630A3 (en
Inventor
Günter Hortmann
Hans Dr.-Ing. Leysieffer
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Sonova Holding AG
Original Assignee
Implex GmbH
Implex Spezialhorgerate GmbH
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Publication of EP0400630A2 publication Critical patent/EP0400630A2/en
Publication of EP0400630A3 publication Critical patent/EP0400630A3/en
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    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
    • H04R25/604—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers
    • H04R25/606—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers acting directly on the eardrum, the ossicles or the skull, e.g. mastoid, tooth, maxillary or mandibular bone, or mechanically stimulating the cochlea, e.g. at the oval window

Definitions

  • the invention relates to an implantable hearing aid for stimulating the inner ear, the hearing aid having a coupling element connected on the input side to an electromechanical transducer for transmitting the mechanical vibrations generated by the transducer to the inner ear.
  • An implantable hearing aid is also known (US-A-3 764 748) which has a fluid-filled sack which is attached to the oval window via a layer of foam plastic.
  • a piezoelectric crystal On the side of the fluid-filled sack facing away from the oval window is a piezoelectric crystal, which forms an electromechanical transducer.
  • 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 output side via an electrical line Auditory nerve 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 this bone 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 there is direct electrical stimulation of the inner ear via an implantable electrode arrangement with the aid of signals which are generated by appropriate signal processing electronics to be provided.
  • the signal processing electronics are housed in a relatively large-volume housing that is carried externally in a separate pocket.
  • the signal processing electronics are connected via a connection cable to a transmission 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 coupling element is designed as a hydromechanical coupling element with an interior filled with liquid, which at its transducer end opens into a likewise filled chamber of the transducer, in which pressure vibrations occur due to transducer vibrations are generated, and that the hydromechanical coupling element is designed such that its end remote from the transducer in the implanted state extends into the fluid-filled inner ear spaces.
  • pressure vibrations are generated by the electromechanical transducer in the fluid-filled transducer chamber and transmitted to the fluid-filled inner ear spaces via the hydromechanical coupling element, bypassing the sound transmission of the auditory ossicles in the inner ear.
  • the hydromechanical coupling element can simply be designed as a liquid-filled hose.
  • 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 for the purpose of optimal mechanical impedance matching and is 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 flexural 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 output 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 pickup 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, and in which, as indicated schematically, 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 reach the tympanic cavity 17 via the outer ear 26, the auditory canal 27 and the eardrum 22. They are picked up there by the sound conductor tube 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 via the hydromechanical coupling element 23 to the fluid-filled inner ear spaces.
  • Fig. 1 shows that the hearing aid is fully 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 generator 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. In such a case, a reception coil 32 is accommodated in the housing 12. In this way, if necessary, 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.
  • 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. Instead, 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 flexural 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 converter 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 the converter disk diameter to the hose inside diameter, which enables high output pressures on the hose membrane 44 in the case of small electrical converter outputs.
  • 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 formed in the housing 12 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 supplied to the microphone 13 from the tympanic cavity 17 via the sound line hose 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, however, also be accommodated in the chamber 40 .
  • 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 which is sealed off with a thin membrane for sealing.

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  • 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)

Description

Die Erfindung betrifft ein implantierbares Hörgerät zur Anregung des Innenohres, wobei das Hörgerät ein eingangsseitig an einen elektromechanischen Wandler angeschlossenes Koppelelement zum Übertragen der von dem Wandler erzeugten mechanischen Schwingungen zum Innenohr aufweist.The invention relates to an implantable hearing aid for stimulating the inner ear, the hearing aid having a coupling element connected on the input side to an electromechanical transducer for transmitting the mechanical vibrations generated by the transducer to the inner ear.

Bei einem bekannten Hörgerät dieser Art (EP-A-0 263 254) ist ein mechanisches Koppelelement vorgesehen.In a known hearing device of this type (EP-A-0 263 254) a mechanical coupling element is provided.

Es ist ferner ein implantierbares Hörgerät bekannt (US-A-3 764 748), das einen fluidgefüllten Sack aufweist, der an dem ovalen Fenster über eine Schicht aus Schaumkunststoff befestigt ist. Auf der von dem ovalen Fenster abgewendeten Seite des fluidgefüllten Sackes liegt ein piezoelektrischer Kristall auf, der einen elektromechanischen Wandler bildet. Bei einer solchen Ausbildung sind die Weiterleitung der Schwingungen an das Innenohr beeinträchtigende Impedanzsprünge an der Treffstelle von Kristallschwinger und flüssigkeitsgefülltem Sack, an der Grenzfläche von Sack und Schaumkunststoffschicht sowie an der Grenzfläche zwischen der Schaumkunststoffschicht und dem ovalen Fenster unvermeidbar.An implantable hearing aid is also known (US-A-3 764 748) which has a fluid-filled sack which is attached to the oval window via a layer of foam plastic. On the side of the fluid-filled sack facing away from the oval window is a piezoelectric crystal, which forms an electromechanical transducer. With such a design, the forwarding of the vibrations to the inner ear impairing jumps in impedance at the meeting point of the crystal oscillator and the liquid-filled sack, at the interface between the sack and the foam plastic layer and at the interface between the foam plastic layer and the oval window are unavoidable.

Bei einem weiteren bekannten Hörgerät zur Anregung des Innenohres (DE-OS 28 25 233) werden die das Hörgerät bildenden Baugruppen einschließlich einer Tritiumbatterie hermetisch gekapselt in den äußeren Gehörgang eingesetzt oder im Mastoid implantiert, und das Hörgerät wird ausgangsseitig über eine elektrische Leitung direkt mit dem Hörnerv verbunden. Bei einer abgewandelten Ausführungsform des bekannten Gerätes werden akustische Schwingungen, die von dem im Mastoid implantierten Hörgerät erzeugt werden, über den Prozessus mastoideus-Knochen in das Mittelohr unter Ausnutzung des Umstandes übertragen, daß dieser Knochen Hohlräume aufweist, die über das Vorhoffenster mit dem Mittelohr in Verbindung stehen.In another known hearing aid for stimulating the inner ear (DE-OS 28 25 233), 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 output side via an electrical line Auditory nerve connected. In a modified embodiment of the known device, 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 this bone has cavities that pass through the atrial window with the middle ear Connect.

Bei einem anderen bekannten Hörgerät (EP 0 242 038 A2) sind in einem in den äußeren Gehörgang einzuschiebenden Gehäuse ein Mikrophon, ein Verstärker, eine Batterie, ein Lautstärkeregler und eine Anregungsspule für einen Magneten untergebracht, der an einem der Hörknöchelchen befestigt wird. Es ist ferner ein Hörgerät bekannt (GB-PS 1 440 724), bei dem ein Mikrophon, ein Verstärker und eine Batterie in einem Gehäuse angeordnet sind, das steckerartig in einen Sockel eingesteckt wird, der ins Schläfenbein hinter der Ohrmuschel implantiert ist. Das Ausgangssignal des Verstärkers geht an eine im Mittelohr implantierte Erregerspule eines auf dem Steigbügel befestigten Magneten.In another known hearing device (EP 0 242 038 A2), 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.

Des weiteren ist ein Hörgerät bekannt (US-PS 4 532 930), bei dem über eine implantierbare Elektrodenanordnung eine unmittelbare elektrische Reizung des Innenohres mit Hilfe von Signalen erfolgt, die von einer zweckentsprechenden Signalverarbeitungselektronik bereitgestellt werden. Die Signalverarbeitungselektronik ist dabei in einem relativ großvolumigen Gehäuse untergebracht, das extern in einer separaten Tasche mitgeführt wird. Die Signalverarbeitungselektronik ist über ein Verbindungskabel an eine Sendeantenne angeschlossen, die im Bereich des betreffenden Ohres angeordnet wird.Furthermore, a hearing aid is known (US Pat. No. 4,532,930) in which there is direct electrical stimulation of the inner ear via an implantable electrode arrangement with the aid of signals which are generated by appropriate signal processing electronics to be provided. The signal processing electronics are housed in a relatively large-volume housing that is carried externally in a separate pocket. The signal processing electronics are connected via a connection cable to a transmission antenna which is arranged in the area of the ear concerned.

Bei den bekannten Hörgeräten läßt die erzielbare Klangqualität häufig zu wünschen übrig. Es kann zu Anpassungsproblemen kommen, und die Anregung über einen an einem Hörknöchelchen befestigten Magneten macht einen mit Risiken verbundenen Eingriff in die Kette der Gehörknöchelchen erforderlich.In the known hearing aids, the achievable sound quality often leaves something to be desired. Adjustment problems can arise, and excitation via a magnet attached to an auditory ossicle requires risky intervention in the ossicular chain.

Der Erfindung liegt die Aufgabe zugrunde, ein implantierbares Hörgerät zur Anregung des Innenohres zu schaffen, das eine hohe Klangqualität hat sowie einen relativ einfachen und risikolosen Einsatz erlaubt.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.

Diese Aufgabe wird erfindungsgemäß dadurch gelöst, daß bei einem Hörgerät der eingangs genannten Art das Koppelelement als hydromechanisches Koppelelement mit einem mit Flüssigkeit gefüllten Innenraum ausgebildet ist, der an seinem wandlerseitigen Ende in eine gleichfalls mit Flüssigkeit gefüllte Kammer des Wandlers einmündet, in welcher durch Wandlerschwingungen Druckschwingungen erzeugt werden, und daß das hydromechanische Koppelelement so ausgebildet ist, daß sein von dem Wandler abliegendes Ende im implantierten Zustand in die flüssigkeitsgefüllten Innenohrräume hineinreicht.This object is achieved in that, in a hearing aid of the type mentioned, the coupling element is designed as a hydromechanical coupling element with an interior filled with liquid, which at its transducer end opens into a likewise filled chamber of the transducer, in which pressure vibrations occur due to transducer vibrations are generated, and that the hydromechanical coupling element is designed such that its end remote from the transducer in the implanted state extends into the fluid-filled inner ear spaces.

Bei dem Hörgerät nach der Erfindung werden von dem elektromechanischen Wandler Druckschwingungen in der flüssigkeitsgefüllten Wandlerkammer erzeugt und über das hydromechanische Koppelelement - unter Umgehung der Schallübertragung der Gehörknöchelchen im Innenohr - auf die flüssigkeitsgefüllten Innenohrräume übertragen. Es läßt sich dadurch auf verhältnismäßig einfache Weise eine besonders wirkungsvolle Innenohranregung mit hoher Klangqualität erzielen.In the hearing aid according to the invention, pressure vibrations are generated by the electromechanical transducer in the fluid-filled transducer chamber and transmitted to the fluid-filled inner ear spaces via the hydromechanical coupling element, bypassing the sound transmission of the auditory ossicles in the inner ear. This enables a particularly effective inner ear excitation with high sound quality to be achieved in a relatively simple manner.

Das hydromechanische Koppelelement kann in weiterer Ausgestaltung der Erfindung einfach als flüssigkeitsgefüllter Schlauch ausgebildet sein.In a further embodiment of the invention, the hydromechanical coupling element can simply be designed as a liquid-filled hose.

Vorteilhaft ist der elektromechanische Wandler hermetisch gekapselt zur Implantation in der Paukenhöhle oder im Mastoid ausgebildet. Der Schlauch ist zwecks optimaler mechanischer Impedanzanpassung vorteilhaft mit einer lymphähnlichen Flüssigkeit gefüllt und an dem von dem Wandler abliegenden Ende mit einer dünnen Membran verschlossen. Er kann mittels einer aufgeschobenen Drahtwendel oder durch einen oder mehrere in die Schlauchwandung eingelassene Drähte entsprechend den jeweiligen anatomischen Gegebenheiten dauerhaft geformt werden. Der elektromechanische Wandler kann in ein Gehäuse einer implantierbaren Signalverarbeitungselektronik integriert sein und auf dem elektrodynamischen, elektromagnetischen oder, vorzugsweise, piezoelektrischen Prinzip beruhen. Insbesondere kann der Wandler einen piezoelektrischen Biegeschwinger aufweisen, der auf einer Trägermembran sitzt, die in dem den Wandler aufnehmenden Gehäuse eingespannt ist. Der Biegeschwinger kann aus einer einlagigen piezoelektrischen Scheibe bestehen oder eine zur Trägermembran symmetrische Bimorphstruktur aufweisen, und er hat vorteilhaft einen Durchmesser, der mindestens dem 0,8-fachen und vorzugsweise mindestens dem 0,9-fachen des Innendurchmessers des zugehörigen Gehäuses entspricht. Durch ein großes Verhältnis von Wandlerscheibendurchmesser zu Schlauchinnendurchmesser wird dabei eine Schnelletransformation erzielt, die schon bei kleinen elektrischen Wandlerleistungen hohe Ausgangsdrücke an dem vom Wandler abliegenden Schlauchende entstehen läßt.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 for the purpose of optimal mechanical impedance matching and is 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. In particular, 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 flexural 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 output pressures at the end of the tube lying away from the transducer.

In weiterer Ausgestaltung der Erfindung ist ein den elektromechanischen Wandler über eine Signalverarbeitungselektronik mit Eingangssignalen versorgendes Mikrophon mit einem akustischen Koppelelement zur Schallaufnahme aus der Paukenhöhle verbunden, wodurch die natürliche Richtcharakteristik des Außenohres voll ausgenutzt wird. Das akustische Koppelelement kann einfach als an das Mikrophon angeschlossener Schalleitungsschlauch ausgebildet sein, dessen vom Mikrophon abgewendetes Ende im implantierten Zustand in die Paukenhöhle hineinragt und zweckmäßig mit einer Membran verschlossen ist.In a further embodiment of the invention, a microphone supplying the electromechanical transducer via signal processing electronics with input signals is connected to an acoustic coupling element for sound pickup 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.

Bevorzugte Ausführungsbeispiele der Erfindung sind nachstehend unter Bezugnahme auf die Zeichnungen näher erläutert. Es zeigen:

Fig. 1
einen schematischen Schnitt durch ein menschliches Ohr mit implantiertem Hörgerät, sowie gleichfalls schematisch einen externen Steuersignalgeber,
Fig. 2
in größerem Maßstab einen schematischen Schnitt durch einen elektromechanischen Wandler mit zugehörigem hydromechanischem Koppelelement zur Übertragung von Wandlerschwingungen auf das Innenohr, und
Fig. 3
in größerem Maßstab einen Schnitt durch das Gehäuse der Signalverarbeitungselektronik in welchem zugleich der elektromechanische Wandler untergebracht ist.
Preferred exemplary embodiments of the invention are explained in more detail below with reference to the drawings. Show it:
Fig. 1
2 shows a schematic section through a human ear with an implanted hearing aid, and also schematically an external control signal transmitter,
Fig. 2
on a larger scale, a schematic section through an electromechanical transducer with associated hydromechanical coupling element for transmitting transducer vibrations to the inner ear, and
Fig. 3
on a larger scale a section through the housing of the signal processing electronics in which the electromechanical converter is housed.

Das in Fig. 1 dargestellte Hörgerät weist ein in der näheren Umgebung des betreffenden Ohres 10, insbesondere im Mastoid 11 implantierbares, hermetisch dichtes Gehäuse 12 auf, in welchem, wie schematisch angedeutet, ein Mikrophon 13, eine Signalverarbeitungselektronik 14 und eine Energieversorgung, beispielsweise eine Sekundärzellenanordnung 15 (d.h. ein oder mehrere wiederaufladbare Akkumulatoren) untergebracht sind. Das Mikrophon 13 steht über ein akustisches Koppelelement in Form eines Schalleitungsschlauchs 16 mit der Paukenhöhle 17 in Verbindung. Das von dem Mikrophon 13 abgewendete Ende des Schalleitungsschlauchs 16 reicht dabei im implantierten Zustand in die Paukenhöhle 17, und es ist dort mittels einer dünnen Membran 18 verschlossen.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, and in which, as indicated schematically, 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 den Ausgang der Signalverarbeitungselektronik 14 ist über eine Wandlerzuleitung 20 ein elektromechanischer Wandler 21 angeschlossen, der hermetisch gekapselt in der Paukenhöhle hinter dem Trommelfell 22 mechanisch fest fixiert ist. Der Wandler 21 ist seinerseits mit einem hydromechanischen Koppelelement 23 verbunden. Über das Koppelelement 23 werden von dem Wandler 21 mechanische Schwingungen zum Innenohr 24 übertragen. Bei dem in Fig. 1 veranschaulichten Ausführungsbeispiel erstreckt sich dazu das Koppelelement 23 durch eine Bohrung in der Steigbügelfußplatte 25 hindurch.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. In the exemplary embodiment illustrated in FIG. 1, the coupling element 23 extends through a bore in the stirrup foot plate 25.

Bei der Ausführungsform gemäß Fig. 1 gelangen Schallsignale über das Außenohr 26, den Gehörgang 27 und das Trommelfell 22 zur Paukenhöhle 17. Sie werden dort von dem Schalleitungsschlauch 16 hinter dem Trommelfell 22 aufgenommen und an das in dem Gehäuse 12 sitzende Mikrophon 13 weitergeleitet. Das Mikrophon 13 wandelt den Schall in elektrische Mikrophonsignale um. Diese Signale werden in der Signalverarbeitungselektronik 14 in geeignete Ausgangssignale umgesetzt und verstärkt über die Wandlerzuleitung 20 an den elektromechanischen Wandler 21 geführt. Der Wandler 21 setzt die elektrischen Ausgangssignale in mechanische Schwingungen um. Die mechanischen Schwingungen werden über das hydromechanische Koppelelement 23 auf die flüssigkeitsgefüllten Innenohrräume übertragen.In the embodiment according to FIG. 1, sound signals reach the tympanic cavity 17 via the outer ear 26, the auditory canal 27 and the eardrum 22. They are picked up there by the sound conductor tube 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 via the hydromechanical coupling element 23 to the fluid-filled inner ear spaces.

Die Fig. 1 läßt erkennen, daß das Hörgerät vollständig implantiert ist. Der Träger wird durch das Gerät unter normalen Alltagsbedingungen nicht beeinträchtigt. Zum Beispiel ist Schwimmen ohne weiteres möglich. Die natürliche Richtcharakteristik des Außenohrs 26 wird voll ausgenutzt und nicht durch mechanische Elemente im äußeren Gehörgang 27 beeinträchtigt. Nach der Signalverstärkung in der Signalverarbeitungselektronik 14 erfolgt keine Wandlung im Luftschall, wodurch eine hohe Klangqualität möglich wird. Etwaige Rückkopplungsprobleme lassen sich relativ einfach beherrschen. Die natürliche Übertragung über die Gehörknöchelchenkette 28 bleibt unbeeinflußt. Damit ist das Risiko für den Patienten minimiert.Fig. 1 shows that the hearing aid is fully 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. After the signal amplification in the signal processing electronics 14, there is no conversion in airborne sound, as a result of which a high sound quality is possible. Any feedback problems can be mastered relatively easily. The natural transmission via the ossicular chain 28 remains unaffected. This minimizes the risk for the patient.

Zum wahlweisen Einstellen eines oder mehrerer Kennwerte der Signalverarbeitungselektronik 14 kann ein externer Steuersignalgeber 30 vorgesehen sein, an dessen Ausgang eine Sendespule 31 angeschlossen ist. In dem Gehäuse 12 ist in einem solchen Fall eine Empfangsspule 32 untergebracht. Auf diese Weise kann im Bedarfsfall über die Spulen 31 und 32 eine hochfrequente induktive Datenübertragung zwischen dem externen Steuersignalgeber 30 und der implantierten Signalverarbeitungselektronik 14 erfolgen. Zweckmäßig kann die für die induktive Datenübertragung vorgesehene Hochfrequenzstrecke auch genutzt werden, um Energie zum Aufladen der implantierten Sekundärzellenanordnung 15 zu übertragen. Stattdessen kann für eine transkutane Datenübertragung zwischen dem Steuersignalgeber 30 und der Signalverarbeitungselektronik 14 auch eine lichtgebundene Infrarotstrecke vorgesehen sein.An external control signal generator 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. In such a case, a reception coil 32 is accommodated in the housing 12. In this way, if necessary, 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. 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. Instead, 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.

Ein Ausführungsbeispiel des elektromechanischen Wandlers 21 und des hydromechanischen Koppelelements 23 ist in größerem Maßstab in Fig. 2 dargestellt. Der Wandler 21 weist ein zweiteiliges, hermetisch dichtes Gehäuse 34 auf. In dem Gehäuse 34 ist ein vorzugsweise kreisförmiger piezoelektrischer Biegeschwinger 35 untergebracht, der auf einer Trägermembran 36 sitzt. Die vorzugsweise aus Messing oder Aluminium bestehende Trägermembran 36 ist an ihrem Rand in dem Gehäuse 34 etwa mittig eingespannt. Der veranschaulichte Biegeschwinger 35 hat eine zu der Trägermembran 36 symmetrische Bimorphstruktur, deren beide Lagen mit 37 und 38 bezeichnet sind. Die Lagen 37, 38 können elektrisch parallel oder hintereinander geschaltet sein. Dabei werden die zwei oder bei elektrischer Parallelschaltung drei Elektrodenflächen der Lagen 37,38 kontaktiert und durch Gehäusedurchführungen an die Wandlerzuleitung 20 angeschlossen.An embodiment of the electromechanical transducer 21 and the hydromechanical coupling element 23 is shown on a larger scale in FIG. 2. The converter 21 has a two-part, hermetically sealed housing 34. A preferably circular piezoelectric flexural 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 converter feed line 20 through housing bushings.

Es versteht sich, daß gegebenenfalls auch die eine der beiden Lagen 37,38 weggelassen werden kann, so daß der Biegeschwinger 35 aus einer einlagigen piezoelektrischen Scheibe besteht. Der Biegeschwinger 35 hat zweckmäßig einen Durchmesser, der mindestens dem 0,8-fachen und vorzugsweise mindestens dem 0,9-fachen des Innendurchmessers des Gehäuses 34 entspricht. Die Trägermembran 36 unterteilt den Innenraum des Gehäuses 34 in zwei Kammern 39 und 40. Die eine Kammer 39 ist mit einer Flüssigkeit 41 gefüllt, deren Dichte und Zusammensetzung mindestens näherungsweise der Perilymphe (der Flüssigkeit im Innenohr) entsprechen. Durch eine Wandung des Gehäuses 34 ist ein Anschlußstutzen 42 geführt, über den durch die Wandlerschwingung erzeugte Druckschwankungen auf einen das hydromechanische Koppelelement 23 bildenden Schlauch 43 geleitet werden. Der Schlauch 43 ist mit der gleichen Flüssigkeit wie die Kammer 39 gefüllt, und sein von dem Wandler 21 abliegendes Ende ist mittels einer dünnen Membran 44 verschlossen. Der Schlauch 43 kann zweckmäßig aus biokompatiblem Silikon bestehen, und er hat vorteilhaft einen Außendurchmesser von 0,3 bis 1,0 mm, vorzugsweise etwa 0,6 mm, sowie eine Wandstärke von 0,05 bis 0,3 mm, vorzugsweise etwa 0,1 mm. Das Wandlergehäuse 34 ist kreisförmig oder annähernd kreisförmig ausgebildet, und es hat zweckmäßig einen Durchmesser von 5 bis 10 mm, vorzugsweise etwa 8 mm. Das Gehäuse 34 kann ebenso wie das Gehäuse 12 vorteilhaft aus einer biokompatiblen Keramik, z.B. Al₂O₃, oder aus Titan bestehen. Die andere Kammer 40 des Gehäuses 34 ist mit einem Edelgas, vorzugsweise Argon, gefüllt. Um den Schlauch 43 ist ein dünner Draht 45 aus biokompatiblem Werkstoff, vorzugsweise Platin, gewendelt. Die Drahtwendel erlaubt es, eine beständige Formung von Biegeradien zur Anpassung an die jeweiligen anatomischen Gegebenheiten zu erreichen. An Stelle der Drahtwendel können auch ein oder mehrere Drähte, vorzugsweise Platindrähte, in die Wandung des Schlauchs 43 eingelassen sein.It goes without saying that one of the two layers 37, 38 can optionally also be omitted, so that 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. Like the housing 12, 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. A thin wire 45 made of biocompatible material, preferably platinum, is wound around the hose 43. The wire helix makes it possible to achieve a constant formation of bending radii to adapt to the respective anatomical conditions. Instead of the wire helix, one or more wires, preferably platinum wires, can also be embedded in the wall of the hose 43.

Die wesentliche Wirkung der in Fig. 2 veranschaulichten Anordnung beruht einerseits auf dem Prinzip einer Druckkammer, durch das erreicht wird, daß bei großem Verhältnis von Wandlerscheibendurchmesser zu Schlauchinnendurchmesser eine Schnelletransformation entsteht, die bei Kleinen elektrischen Wandlerleistungen hohe Ausgangsdrücke an der Schlauchmembran 44 ermöglicht. Andererseits erlaubt die Füllung des Schlauchs 43 mit einer lymphähnlichen Flüssigkeit eine optimale mechanische Impedanzanpassung an das Innenohr. Dadurch werden störende Reflexionen vermieden.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 the converter disk diameter to the hose inside diameter, which enables high output pressures on the hose membrane 44 in the case of small electrical converter outputs. On the other hand, 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.

Bei der abgewandelten Ausführungsform gemäß Fig. 3 ist der elektromechanische Wandler 21 mit in das Gehäuse 12 der Signalverarbeitungselektronik 14 integriert. Die von der Trägermembran 36 des Biegeschwingers 35 begrenzte, in diesem Fall gleichfalls in dem Gehäuse 12 ausgebildete, flüssigkeitsgefüllte Kammer 39 ist analog der Fig. 2 mit dem hydromechanischen Koppelelement 23 in Form des flüssigkeitsgefüllten Schlauches 43 verbunden. Entsprechend der Ausführungsform der Fig. 1 sind in dem Gehäuse 12 ferner das Mikrophon 13 und die Energieversorgung, beispielsweise eine Sekundärzellenanordnung 15, untergebracht. Der Schall wird dem Mikrophon 13 aus der Paukenhöhle 17 über den Schalleitungsschlauch 16 zugeführt. Letzterer ist mit dem Gehäuse 12 über einen Anschlußstutzen 46 verbunden und an seinem freien Ende mittels der dünnen Membran 18 abgeschlossen. Um Rückkopplungen zu vermeiden, ist das Mikrophon 13 in dem Gehäuse 12 schwingungstechnisch isoliert aufgehängt. Wie in Fig. 3 angedeutet ist, sitzen das Mikrophon 13, die Signalverarbeitungselektronik 14 und die Energieversorgung 15 in einer von der gasgefüllten Kammer 40 mittels einer Trennwand 47 abgeteilten dritten Kammer 48. Gegebenenfalls können mindestens einzelne dieser Baugruppen aber auch in der Kammer 40 untergebracht sein.In the modified embodiment according to FIG. 3, the electromechanical converter 21 is also integrated in the housing 12 of the signal processing electronics 14. The bounded by the support membrane 36 of the bending vibrator 35, in this case also The liquid-filled chamber 39 formed in the housing 12 is connected to the hydromechanical coupling element 23 in the form of the liquid-filled hose 43 analogously to FIG. 2. According to the embodiment of FIG. 1, the microphone 13 and the power supply, for example a secondary cell arrangement 15, are also accommodated in the housing 12. The sound is supplied to the microphone 13 from the tympanic cavity 17 via the sound line hose 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. In order to avoid feedback, 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, however, also be accommodated in the chamber 40 .

Zur Energieversorgung kann auch eine Primärzellenanordnung vorgesehen sein, die in einem von dem Gehäuse 12 der Signalverarbeitungselektronik 14 getrennten Gehäuse untergebracht und über eine trennbare Verbindung an die Signalverarbeitungselektronik 14 angeschlossen ist. Dadurch kann im Bedarfsfall die Primärzellenanordnung (eine oder mehrere Batterien) ausgetauscht werden, ohne daß ein gleichzeitiger Austausch des Gehäuses 12 bzw. ein Eingriff in dieses Gehäuse notwendig wird.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. As a result, the primary cell arrangement (one or more batteries) can be replaced if necessary, without a simultaneous exchange of the housing 12 or an intervention in this housing being necessary.

Es ist ferner möglich, das Schall aus der Paukenhöhle 17 aufnehmende Mikrophon 13 in einem gesonderten Gehäuse unterzubringen, das bei der Implantation unmittelbar in der Paukenhöhle 17 fixiert wird. Das Mikrophon 13 nimmt dabei den Schall aus der Paukenhöhle über einen durch das Gehäuse geführten Stutzen auf, der zur Abdichtung mit einer dünnen Membran abgeschlossen ist.It is also possible to accommodate 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 which is sealed off with a thin membrane for sealing.

Claims (24)

  1. Implantable hearing aid for stimulating the inner ear, wherein the hearing aid has a coupling element (23), connected on the input side to an electromechanical transducer (21), for transmitting mechanical vibrations generated by the transducer to the inner ear, characterised in that the coupling element takes the form of a hydromechanical coupling element (23) having a cavity filled with fluid (41) and opening at its end associated with the transducer into a chamber (39) of the transducer also filled with fluid (41), in which chamber pressure vibrations are generated by transducer vibrations, and in that the hydromechanical coupling element (23) is so formed that its end remote from the transducer (21) extends, in the implanted state, into the fluid-filled chambers of the inner ear.
  2. Hearing aid according to claim 1, characterised in that the hydromechanical coupling element (23) is formed as a fluid-filled flexible tube (43).
  3. Hearing aid according to claim 1 or 2, characterised in that the electromechanical transducer (21) is hermetically encapsulated for implantation in the tympanic cavity or mastoid.
  4. Hearing aid according to claim 2, characterised in that the fluid-filled flexible tube (43) is sealed at the end remote from the electromechanical transducer (21).
  5. Hearing aid according to claim 4, characterised in that the end of the flexible tube is sealed with a thin membrane (44).
  6. Hearing aid according to claim 4 or 5, characterised in that the flexible tube (43) is filled with a lymph-like fluid.
  7. Hearing aid according to one of claims 2 to 6, characterised in that the fluid-filled flexible tube (43) 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.
  8. Hearing aid according to one of claims 2 to 7, characterised in that the flexible tube (43) is wrapped in a biocompatible wire (45), preferably platinum wire.
  9. Hearing aid according to one of claims 2 to 8, characterised in that one or more wires, preferably platinum wires, penetrate the wall of the flexible tube (43).
  10. Hearing aid according to one of claims 3 to 9, characterised in that the electromechanical transducer (21) is housed in a circular or approximately circular transducer housing (34) having a diameter of 5 to 10 mm, preferably approximately 8 mm.
  11. Hearing aid according to one of the aforesaid claims, characterised in that the electromechanical transducer (21) is incorporated in a housing (12) of an implantable electronic signal processor (14).
  12. Hearing aid according to one of the aforesaid claims, characterised in that the transducer (21) operates according to the electrodynamic, electromagnetic or preferably piezoelectric principle.
  13. Hearing aid according to one of the aforesaid claims, characterised in that the electromechanical transducer (21) has a preferably circular, piezoelectric flexural resonator (35) resting on a support membrane (36), which is mounted in the housing (12, 34) receiving the transducer.
  14. Hearing aid according to claim 13, characterised in that the flexural resonator (35) consists of a single-ply piezoelectric disc.
  15. Hearing aid according to claim 13, characterised in that the flexural resonator (35) has a bimorphic structure symmetrical to the support membrane (36), its two layers (37, 38) being connected electrically in parallel or in series.
  16. Hearing aid according to one of claims 13 to 15, characterised in that the flexural resonator (35) has a diameter corresponding to at least 0.8 times, and preferably at least 0.9 times the inner diameter of the associated housing (12, 34).
  17. Hearing aid according to one of claims 13 to 16, characterised in that the support membrane (36) divides the interior of the housing (12, 34) into the chamber (39) filled with fluid (41) and a further chamber (40).
  18. Hearing aid according to one of the aforesaid claims, characterised in that the fluid in the transducer chamber (39) has a density and composition approximately corresponding to the density and composition of perilymph.
  19. Hearing aid according to claim 17 or 18, characterised in that the further chamber (40) of the housing (23, 34) is filled with a noble gas, preferably argon.
  20. Hearing aid according to one of claims 17 to 19, characterised in that in the further or in a third chamber (48) of the housing, an electronic signal processor (14) and/or a microphone (13) and/or a power supply (15, 15′) are housed.
  21. Hearing aid according to one of the aforesaid claims, characterised in that the hydromechanical coupling element (23) in the implanted state extends through a bore in the stapes plate or a bore in the vicinity of the fenestra into the inner ear.
  22. Hearing aid according to one of the aforesaid claims, characterised in that a microphone (13) supplying the electromechanical transducer (21) with input signals via an electronic signal processor (14) is connected to an acoustic coupling element (16) for receiving sound from the tympanic cavity.
  23. Hearing aid according to claim 22, characterised in that as an acoustic coupling element a sound conducting hose (16) connected to the microphone (13) is provided, its end remote from the microphone projecting in the implanted state into the tympanic cavity.
  24. Hearing aid according to claim 23, characterised in that the sound conducting hose (16) is sealed with a membrane (18) at the end remote from the microphone (13).
EP90110307A 1989-06-02 1990-05-30 Implantable hearing aid Expired - Lifetime EP0400630B1 (en)

Applications Claiming Priority (2)

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

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EP0400630A2 EP0400630A2 (en) 1990-12-05
EP0400630A3 EP0400630A3 (en) 1992-08-05
EP0400630B1 true EP0400630B1 (en) 1995-08-02

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EP (1) EP0400630B1 (en)
DE (3) DE3940632C1 (en)
DK (1) DK0400630T3 (en)

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE19827898C1 (en) * 1998-06-23 1999-11-11 Hans Leysieffer Electrical energy supply for an implant, eg. a hearing aid
DE102016107517A1 (en) * 2016-04-22 2017-10-26 Medizinische Hochschule Hannover Middle ear implant

Families Citing this family (151)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE4104358A1 (en) * 1991-02-13 1992-08-20 Implex Gmbh IMPLANTABLE HOER DEVICE FOR EXCITING THE INNER EAR
US5282858A (en) * 1991-06-17 1994-02-01 American Cyanamid Company Hermetically sealed implantable transducer
US5531787A (en) * 1993-01-25 1996-07-02 Lesinski; S. George Implantable auditory system with micromachined microsensor and microactuator
US5430801A (en) * 1993-12-14 1995-07-04 Hill; Frank C. Hearing aid
US5772575A (en) * 1995-09-22 1998-06-30 S. George Lesinski Implantable hearing aid
EP0861570B1 (en) * 1995-11-13 2005-08-10 Cochlear Limited Implantable microphone for cochlear implants
EP0891684B1 (en) * 1996-03-25 2008-11-12 S. George Lesinski Attaching of an implantable hearing aid microactuator
DE19618961B4 (en) * 1996-05-10 2004-09-16 Phonak Ag Device for electromechanical stimulation and testing of the hearing
EP1596629A3 (en) * 1996-05-24 2011-09-21 S. George Lesinski Electronic module for implantable hearing aid
EP0963683B1 (en) * 1996-05-24 2005-07-27 S. George Lesinski Improved microphones for an implantable hearing aid
US5977689A (en) * 1996-07-19 1999-11-02 Neukermans; Armand P. Biocompatible, implantable hearing aid microactuator
US5707338A (en) * 1996-08-07 1998-01-13 St. Croix Medical, Inc. Stapes vibrator
US5879283A (en) * 1996-08-07 1999-03-09 St. Croix Medical, Inc. Implantable hearing system having multiple transducers
US5899847A (en) 1996-08-07 1999-05-04 St. Croix Medical, Inc. Implantable middle-ear hearing assist system using piezoelectric transducer film
US5997466A (en) * 1996-08-07 1999-12-07 St. Croix Medical, Inc. Implantable hearing system having multiple transducers
US6171229B1 (en) 1996-08-07 2001-01-09 St. Croix Medical, Inc. Ossicular transducer attachment for an implantable hearing device
US6001129A (en) * 1996-08-07 1999-12-14 St. Croix Medical, Inc. Hearing aid transducer support
US5842967A (en) * 1996-08-07 1998-12-01 St. Croix Medical, Inc. Contactless transducer stimulation and sensing of ossicular chain
US5762583A (en) * 1996-08-07 1998-06-09 St. Croix Medical, Inc. Piezoelectric film transducer
US5836863A (en) 1996-08-07 1998-11-17 St. Croix Medical, Inc. Hearing aid transducer support
US6005955A (en) * 1996-08-07 1999-12-21 St. Croix Medical, Inc. Middle ear transducer
US5814095A (en) * 1996-09-18 1998-09-29 Implex Gmbh Spezialhorgerate Implantable microphone and implantable hearing aids utilizing same
DE19638158C2 (en) * 1996-09-18 2000-08-31 Implex Hear Tech Ag Implantable microphone
DE19638159C2 (en) * 1996-09-18 2000-09-07 Implex Hear Tech Ag Fully implantable hearing aid for electrical hearing stimulation
US6010532A (en) * 1996-11-25 2000-01-04 St. Croix Medical, Inc. Dual path implantable hearing assistance device
SE509135C2 (en) * 1997-04-11 1998-12-07 Nobel Biocare Ab Hearing aid
US6315710B1 (en) 1997-07-21 2001-11-13 St. Croix Medical, Inc. Hearing system with middle ear transducer mount
US6264603B1 (en) 1997-08-07 2001-07-24 St. Croix Medical, Inc. Middle ear vibration sensor using multiple transducers
US5954628A (en) * 1997-08-07 1999-09-21 St. Croix Medical, Inc. Capacitive input transducers for middle ear sensing
DE19745331A1 (en) * 1997-10-14 1999-04-15 Schumann Klaus Electronic hearing aid
EP0936840A1 (en) * 1998-02-16 1999-08-18 Daniel F. àWengen Implantable hearing aid
WO1999063785A2 (en) 1998-06-05 1999-12-09 St. Croix Medical, Inc. Reduced feedback in implantable hearing assistance systems
DE19829637C2 (en) 1998-07-02 2000-10-19 Implex Hear Tech Ag Medical implant
DE19837913C2 (en) * 1998-08-20 2000-09-28 Implex Hear Tech Ag Implantable device with a charging current feed arrangement having a receiving coil
DE19838137A1 (en) 1998-08-21 2000-03-02 Implex Hear Tech Ag Charger arrangement for rechargeable Ni Cd, Ni-metal hydride, or Lithium batteries in implant, has current source which provides high initial current
DE19840211C1 (en) * 1998-09-03 1999-12-30 Implex Hear Tech Ag Transducer for partially or fully implantable hearing aid
US6364825B1 (en) 1998-09-24 2002-04-02 St. Croix Medical, Inc. Method and apparatus for improving signal quality in implantable hearing systems
DE19858399C2 (en) * 1998-12-17 2003-02-20 Phonak Ag Staefa Electroacoustic transducer for hearing aids for airborne sound radiation in the external auditory canal
DE19859171C2 (en) 1998-12-21 2000-11-09 Implex Hear Tech Ag Implantable hearing aid with tinnitus masker or noiser
DE19914992A1 (en) * 1999-04-01 2000-12-07 Implex Hear Tech Ag Implantable hearing system with audiometer
DE19915846C1 (en) 1999-04-08 2000-08-31 Implex Hear Tech Ag Partially implantable system for rehabilitating hearing trouble includes a cordless telemetry device to transfer data between an implantable part, an external unit and an energy supply.
US6259951B1 (en) 1999-05-14 2001-07-10 Advanced Bionics Corporation Implantable cochlear stimulator system incorporating combination electrode/transducer
DE19931788C1 (en) * 1999-07-08 2000-11-30 Implex Hear Tech Ag Implanted mechanical coupling device for auditory ossicle chain in hearing aid system has associated settling device for movement of coupling device between open and closed positions
US6629922B1 (en) 1999-10-29 2003-10-07 Soundport Corporation Flextensional output actuators for surgically implantable hearing aids
US6516228B1 (en) 2000-02-07 2003-02-04 Epic Biosonics Inc. Implantable microphone for use with a hearing aid or cochlear prosthesis
DE10015421C2 (en) 2000-03-28 2002-07-04 Implex Ag Hearing Technology I Partially or fully implantable hearing system
DE10018361C2 (en) 2000-04-13 2002-10-10 Cochlear Ltd At least partially implantable cochlear implant system for the rehabilitation of a hearing disorder
DE10018334C1 (en) * 2000-04-13 2002-02-28 Implex Hear Tech Ag At least partially implantable system for the rehabilitation of a hearing impairment
DE10018360C2 (en) 2000-04-13 2002-10-10 Cochlear Ltd At least partially implantable system for the rehabilitation of a hearing impairment
SE523123C2 (en) * 2000-06-02 2004-03-30 P & B Res Ab Hearing aid that works with the principle of bone conduction
SE0002073L (en) 2000-06-02 2001-05-21 P & B Res Ab Vibrator for leg anchored and leg conduit hearing aids
SE514930C2 (en) * 2000-06-02 2001-05-21 P & B Res Ab Vibrator for leg anchored and leg conduit hearing aids
DE10030372C2 (en) * 2000-06-16 2002-04-25 Univ Dresden Tech Implantable hydroacoustic transducer
US6572531B2 (en) * 2000-06-17 2003-06-03 Alfred E. Mann Foundation For Scientific Reseach Implantable middle ear implant
US6648813B2 (en) 2000-06-17 2003-11-18 Alfred E. Mann Foundation For Scientific Research Hearing aid system including speaker implanted in middle ear
WO2002005590A1 (en) 2000-06-30 2002-01-17 Cochlear Limited Cochlear implant
DE10031832C2 (en) * 2000-06-30 2003-04-30 Cochlear Ltd Hearing aid for the rehabilitation of a hearing disorder
DE10041727C2 (en) * 2000-08-25 2003-04-10 Cochlear Ltd Implantable hermetically sealed housing for an implantable medical device
DE10041728A1 (en) 2000-08-25 2002-03-21 Implex Hear Tech Ag Implantable medicinal device with hermetically sealed housing has storage device accommodated directly within hermetically sealed housing without housing of its own
DE10047388C1 (en) * 2000-09-25 2002-01-10 Implex Hear Tech Ag Implantable hearing system, includes a detachable coupling for securing and locating a transducer and a micro-manipulator
DE10046938A1 (en) 2000-09-21 2002-04-25 Implex Ag Hearing Technology I At least partially implantable hearing system with direct mechanical stimulation of a lymphatic space in the inner ear
US6707920B2 (en) 2000-12-12 2004-03-16 Otologics Llc Implantable hearing aid microphone
AU2002252676A1 (en) 2001-04-12 2002-10-28 Otologics Llc Hearing aid with internal acoustic middle ear transducer
US6730015B2 (en) 2001-06-01 2004-05-04 Mike Schugt Flexible transducer supports
DE10136737A1 (en) * 2001-07-27 2003-02-13 Univ Ilmenau Tech Micro-tool or instrument for keyhole surgery or fine machining technology uses ultrasonic energy to drive a tool at the end of a long connection tube which is filled with liquid metal to transmit the ultrasonic energy
US6786860B2 (en) 2001-10-03 2004-09-07 Advanced Bionics Corporation Hearing aid design
US7127078B2 (en) * 2001-10-03 2006-10-24 Advanced Bionics Corporation Implanted outer ear canal hearing aid
US6879695B2 (en) * 2001-10-03 2005-04-12 Advanced Bionics Corporation Personal sound link module
US8147544B2 (en) 2001-10-30 2012-04-03 Otokinetics Inc. Therapeutic appliance for cochlea
AU2003294595A1 (en) 2002-12-09 2004-06-30 Medtronic, Inc. Modular implantable medical device
US7596408B2 (en) 2002-12-09 2009-09-29 Medtronic, Inc. Implantable medical device with anti-infection agent
DE10301723B3 (en) 2003-01-15 2004-09-16 Med-El Elektromedizinische Geräte GmbH Implantable electromechanical transducer
US7794431B2 (en) * 2003-04-12 2010-09-14 Incumed Llc Apparatus and method for facilitating the replacement of an implanted catheter
US7731697B2 (en) * 2003-04-12 2010-06-08 Incumed Llc, A Nevada Limited Liability Co. Apparatus and method for percutaneous catheter implantation and replacement
EP1613252B1 (en) * 2003-04-12 2016-03-09 IncuMed LLC Percutaneously implantable medical device configured to promote tissue ingrowth
US7263401B2 (en) 2003-05-16 2007-08-28 Medtronic, Inc. Implantable medical device with a nonhermetic battery
AU2003903839A0 (en) * 2003-07-24 2003-08-07 Cochlear Limited Battery characterisation
AU2003904086A0 (en) * 2003-08-04 2003-08-21 Cochlear Limited Implant battery short circuit protection
US7204799B2 (en) * 2003-11-07 2007-04-17 Otologics, Llc Microphone optimized for implant use
US7556597B2 (en) * 2003-11-07 2009-07-07 Otologics, Llc Active vibration attenuation for implantable microphone
JP3958739B2 (en) * 2003-12-12 2007-08-15 Ｎｅｃトーキン株式会社 Acoustic vibration generator
US7651460B2 (en) * 2004-03-22 2010-01-26 The Board Of Regents Of The University Of Oklahoma Totally implantable hearing system
US7214179B2 (en) * 2004-04-01 2007-05-08 Otologics, Llc Low acceleration sensitivity microphone
US7840020B1 (en) 2004-04-01 2010-11-23 Otologics, Llc Low acceleration sensitivity microphone
US7596399B2 (en) 2004-04-29 2009-09-29 Medtronic, Inc Implantation of implantable medical device
US20050245984A1 (en) 2004-04-30 2005-11-03 Medtronic, Inc. Implantable medical device with lubricious material
US7668325B2 (en) * 2005-05-03 2010-02-23 Earlens Corporation Hearing system having an open chamber for housing components and reducing the occlusion effect
US8295523B2 (en) * 2007-10-04 2012-10-23 SoundBeam LLC Energy delivery and microphone placement methods for improved comfort in an open canal hearing aid
US7867160B2 (en) * 2004-10-12 2011-01-11 Earlens Corporation Systems and methods for photo-mechanical hearing transduction
DE102004038078B4 (en) * 2004-07-30 2010-11-25 Technische Universität Dresden Implantable hearing aid part
AU2005312331B2 (en) * 2004-11-30 2010-04-22 Cochlear Acoustics Ltd Implantable actuator for hearing aid applications
EP1851994B1 (en) * 2005-01-11 2015-07-01 Cochlear Limited Active vibration attenuation for implantable microphone
US8096937B2 (en) * 2005-01-11 2012-01-17 Otologics, Llc Adaptive cancellation system for implantable hearing instruments
JP4330541B2 (en) * 2005-01-31 2009-09-16 ヤマハ株式会社 Body temperature utilization power generator and cochlear implant system using the same
WO2006091808A2 (en) * 2005-02-25 2006-08-31 Medical Research Products-B, Inc. Fully implantable hearing aid system
US7489793B2 (en) 2005-07-08 2009-02-10 Otologics, Llc Implantable microphone with shaped chamber
US20080205679A1 (en) * 2005-07-18 2008-08-28 Darbut Alexander L In-Ear Auditory Device and Methods of Using Same
US20070127757A2 (en) * 2005-07-18 2007-06-07 Soundquest, Inc. Behind-The-Ear-Auditory Device
US7522738B2 (en) * 2005-11-30 2009-04-21 Otologics, Llc Dual feedback control system for implantable hearing instrument
US9084901B2 (en) 2006-04-28 2015-07-21 Medtronic, Inc. Cranial implant
US8021340B2 (en) * 2006-07-05 2011-09-20 Incumed, Llc Enhanced apparatus for percutaneous catheter implantation and replacement
US7720542B2 (en) * 2006-07-17 2010-05-18 Med-El Elektromedizinische Geraete Gmbh Remote sensing and actuation of fluid in cranial implants
JP5160543B2 (en) * 2006-07-17 2013-03-13 メド−エル エレクトロメディジニシェ ゲラテ ゲーエムベーハー Remote sensing and activation of inner ear fluid
WO2008077943A2 (en) * 2006-12-26 2008-07-03 3Win N.V. Device and method for improving hearing
WO2008128300A1 (en) 2007-04-23 2008-10-30 Cochlear Limited Implant assembly
DK2208367T3 (en) 2007-10-12 2017-11-13 Earlens Corp Multifunction system and method for integrated listening and communication with noise cancellation and feedback management
US8472654B2 (en) 2007-10-30 2013-06-25 Cochlear Limited Observer-based cancellation system for implantable hearing instruments
US8144910B2 (en) * 2007-11-14 2012-03-27 Siemens Hearing Instruments, Inc. Composite receiver tube for a hearing instrument
US8406888B2 (en) * 2008-03-31 2013-03-26 Cochlear Limited Implantable cochlear access device
US8526641B2 (en) * 2008-03-31 2013-09-03 Cochlear Limited Customizable mass arrangements for bone conduction devices
US20090306457A1 (en) * 2008-03-31 2009-12-10 Cochlear Limited Implantable hearing system
US20090259090A1 (en) * 2008-03-31 2009-10-15 Cochlear Limited Bone conduction hearing device having acoustic feedback reduction system
EP2301262B1 (en) 2008-06-17 2017-09-27 Earlens Corporation Optical electro-mechanical hearing devices with combined power and signal architectures
CN102124757B (en) 2008-06-17 2014-08-27 依耳乐恩斯公司 Transmission sound signal and system, device and method for simulating object by utilizing transmission sound signal
US8396239B2 (en) 2008-06-17 2013-03-12 Earlens Corporation Optical electro-mechanical hearing devices with combined power and signal architectures
US8301260B2 (en) 2008-08-13 2012-10-30 Daglow Terry D Method of implanting a medical implant to treat hearing loss in a patient, devices for faciliting implantation of such devices, and medical implants for treating hearing loss
WO2010022314A1 (en) * 2008-08-21 2010-02-25 Med-El Elektromedizinische Geraete Gmbh Multipath stimulation hearing systems
BRPI0918994A2 (en) 2008-09-22 2017-06-13 SoundBeam LLC device, and method for transmitting an audio signal to a user.
US9393432B2 (en) 2008-10-31 2016-07-19 Medtronic, Inc. Non-hermetic direct current interconnect
US8771166B2 (en) 2009-05-29 2014-07-08 Cochlear Limited Implantable auditory stimulation system and method with offset implanted microphones
EP2438768B1 (en) * 2009-06-05 2016-03-16 Earlens Corporation Optically coupled acoustic middle ear implant device
US9544700B2 (en) * 2009-06-15 2017-01-10 Earlens Corporation Optically coupled active ossicular replacement prosthesis
EP2443843A4 (en) * 2009-06-18 2013-12-04 SoundBeam LLC Eardrum implantable devices for hearing systems and methods
DK2443773T3 (en) 2009-06-18 2017-02-27 Earlens Corp OPTICALLY CONNECTED COCHLEAR IMPLANT SYSTEMS
WO2011005479A2 (en) 2009-06-22 2011-01-13 SoundBeam LLC Optically coupled bone conduction systems and methods
WO2011005500A2 (en) 2009-06-22 2011-01-13 SoundBeam LLC Round window coupled hearing systems and methods
US8845705B2 (en) 2009-06-24 2014-09-30 Earlens Corporation Optical cochlear stimulation devices and methods
US8715154B2 (en) 2009-06-24 2014-05-06 Earlens Corporation Optically coupled cochlear actuator systems and methods
PL2505003T3 (en) 2009-11-24 2020-08-10 Med-El Elektromedizinische Geräte GmbH Implantable microphone for hearing systems
US20110271965A1 (en) * 2010-05-10 2011-11-10 Red Tail Hawk Corporation Multi-Material Hearing Protection Custom Earplug
US20120136197A1 (en) * 2010-11-30 2012-05-31 Van Gerwen Peter B J Hearing prosthesis having a flexible elongate energy transfer mechanism
WO2012088187A2 (en) 2010-12-20 2012-06-28 SoundBeam LLC Anatomically customized ear canal hearing apparatus
US20130303835A1 (en) * 2012-05-10 2013-11-14 Otokinetics Inc. Microactuator
US9167362B2 (en) 2012-09-13 2015-10-20 Otokinetics Inc. Implantable receptacle for a hearing aid component
US10034103B2 (en) 2014-03-18 2018-07-24 Earlens Corporation High fidelity and reduced feedback contact hearing apparatus and methods
EP3169396B1 (en) 2014-07-14 2021-04-21 Earlens Corporation Sliding bias and peak limiting for optical hearing devices
US9924276B2 (en) 2014-11-26 2018-03-20 Earlens Corporation Adjustable venting for hearing instruments
US10284968B2 (en) 2015-05-21 2019-05-07 Cochlear Limited Advanced management of an implantable sound management system
US20170095202A1 (en) 2015-10-02 2017-04-06 Earlens Corporation Drug delivery customized ear canal apparatus
US10321247B2 (en) 2015-11-27 2019-06-11 Cochlear Limited External component with inductance and mechanical vibratory functionality
WO2017116791A1 (en) 2015-12-30 2017-07-06 Earlens Corporation Light based hearing systems, apparatus and methods
US11350226B2 (en) 2015-12-30 2022-05-31 Earlens Corporation Charging protocol for rechargeable hearing systems
US10492010B2 (en) 2015-12-30 2019-11-26 Earlens Corporations Damping in contact hearing systems
US11071869B2 (en) 2016-02-24 2021-07-27 Cochlear Limited Implantable device having removable portion
CN109952771A (en) 2016-09-09 2019-06-28 伊尔兰斯公司 Contact hearing system, device and method
WO2018093733A1 (en) 2016-11-15 2018-05-24 Earlens Corporation Improved impression procedure
WO2019173470A1 (en) 2018-03-07 2019-09-12 Earlens Corporation Contact hearing device and retention structure materials
WO2019199680A1 (en) 2018-04-09 2019-10-17 Earlens Corporation Dynamic filter
JP2023537781A (en) * 2020-08-20 2023-09-05 ザ リージェンツ オブ ザ ユニバーシティ オブ カリフォルニア Stimulation methods for direct-drive hearing aids
CA3189183A1 (en) * 2020-08-20 2022-02-24 Hamid Djalilian Semi-implantable hearing aid
CN114449417B (en) * 2020-10-30 2022-11-25 华为技术有限公司 Speaker and electronic equipment

Family Cites Families (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3594514A (en) * 1970-01-02 1971-07-20 Medtronic Inc Hearing aid with piezoelectric ceramic element
US3764748A (en) * 1972-05-19 1973-10-09 J Branch Implanted hearing aids
GB1440724A (en) * 1972-07-18 1976-06-23 Fredrickson J M Implantable electromagnetic hearing aid
FR2395016A1 (en) * 1977-06-21 1979-01-19 Ducommun Georges Hearing aid using tritium battery as power supply - is implanted in or near damaged ear and has microphone in auditory passage
US4357497A (en) * 1979-09-24 1982-11-02 Hochmair Ingeborg System for enhancing auditory stimulation and the like
US4756312A (en) * 1984-03-22 1988-07-12 Advanced Hearing Technology, Inc. Magnetic attachment device for insertion and removal of hearing aid
US4729366A (en) * 1984-12-04 1988-03-08 Medical Devices Group, Inc. Implantable hearing aid and method of improving hearing
US4850962A (en) * 1984-12-04 1989-07-25 Medical Devices Group, Inc. Implantable hearing aid and method of improving hearing
US4800884A (en) * 1986-03-07 1989-01-31 Richards Medical Company Magnetic induction hearing aid
US4988333A (en) * 1988-09-09 1991-01-29 Storz Instrument Company Implantable middle ear hearing aid system and acoustic coupler therefor

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE19827898C1 (en) * 1998-06-23 1999-11-11 Hans Leysieffer Electrical energy supply for an implant, eg. a hearing aid
DE102016107517A1 (en) * 2016-04-22 2017-10-26 Medizinische Hochschule Hannover Middle ear implant

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EP0400630A2 (en) 1990-12-05
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DK0400630T3 (en) 1995-09-18
DE3918086C1 (en) 1990-09-27
EP0400630A3 (en) 1992-08-05
US5411467A (en) 1995-05-02

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