EP1041857B1 - Système auditif implantable avec audiomètre - Google Patents

Système auditif implantable avec audiomètre Download PDF

Info

Publication number
EP1041857B1
EP1041857B1 EP99122698A EP99122698A EP1041857B1 EP 1041857 B1 EP1041857 B1 EP 1041857B1 EP 99122698 A EP99122698 A EP 99122698A EP 99122698 A EP99122698 A EP 99122698A EP 1041857 B1 EP1041857 B1 EP 1041857B1
Authority
EP
European Patent Office
Prior art keywords
hearing system
signal
hearing
signal processing
unit
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
EP99122698A
Other languages
German (de)
English (en)
Other versions
EP1041857A2 (fr
EP1041857A3 (fr
Inventor
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.)
Cochlear Ltd
Original Assignee
Cochlear Ltd
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 Cochlear Ltd filed Critical Cochlear Ltd
Publication of EP1041857A2 publication Critical patent/EP1041857A2/fr
Publication of EP1041857A3 publication Critical patent/EP1041857A3/fr
Application granted granted Critical
Publication of EP1041857B1 publication Critical patent/EP1041857B1/fr
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

Links

Images

Classifications

    • 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
    • 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
    • H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
    • H04R25/505—Customised settings for obtaining desired overall acoustical characteristics using digital signal processing

Definitions

  • Patent 5,814,095 US-A-5 554 096 and U.S. Patent 5,624,376 .
  • these implantable hearing aids use a mechanical, vibratory stimulus as an output signal that directly excites the middle ear or inner ear.
  • the coupling of the mechanical stimulus is done by direct mechanical connection of the vibrating transducer element to the ossicular chain or an ossicle of the middle ear or to the inner ear ( US-A-5,941,814 ) or by a force coupling via an air gap in eg electromagnetic transducers.
  • the coupling quality of the mechanical stimulus is influenced by many parameters and contributes significantly to the rehabilitation of the hearing damage and to the perceived hearing quality. Intraoperatively, this quality of coupling is difficult or even unpredictable, since the motion amplitudes of the vibrating parts, even at the highest stimulation levels, are within a range of or well below 1 ⁇ m and therefore can not be assessed by direct visual inspection. Even if this is possible by other technical measurement methods, for example by intraoperative laser measurements (eg laser Doppler vibrometry), the uncertainty of a long-term stable, safe coupling remains, as they are negatively influenced, among other things by necrosis, tissue neoplasmosis, changes in air pressure and other external and internal influences can.
  • laser Doppler vibrometry eg laser Doppler vibrometry
  • the need to assess the coupling quality of the transducer remains because a full implant does not have the ability to measure individual system components separately at their technical interfaces, if, for example, the implant wearer complains a declined transmission quality by reprogramming individual audiological Matching parameters can not be improved and therefore an operative intervention to improve the situation can not be ruled out. Even if such a case does not exist, there is a fundamental scientific interest in having a meaningful monitor function of the long-term development of the quality of the converter coupling.
  • the object of the present invention is to provide a partially or fully implantable hearing system which, by circumventing the aforementioned disadvantages by psychoacoustic measurements, that is to say by subjective patient responses, determines the coupling quality of the electromechanical transducer to the middle or inner ear. without any further biological-technical interfaces being included in the evaluation, which impair the informative value of the determination of the converter coupling quality.
  • this object is achieved in that the hearing aid is supplemented by an electronic audiometer module that generates audiometric signals for an audiological, subjective examination and evaluation of the coupling quality of the electromechanical output transducer and fed into the audio signal processing path of the hearing implant.
  • the audiometer module preferably consists of one or more externally adjustable or programmable electronic signal generators which feed an electrical auditory test signal into the signal processing path of the implant.
  • the electromechanical output transducer of the implanted hearing system is controlled by the audiometer module technically reproducible and quantitatively determined electrically directly; In this way, distortions of the stimulation level are avoided, as they can occur, for example, by Köpf Anlagener- or in particular acoustic free-field performances of the audiometric test sound, because in this case also the sensor or microphone function with all the associated variability in the psychoacoustic measurement is included.
  • the system according to the invention has, inter alia, the advantage that, for example, frequency-specific hearing threshold measurements with pure sine tones or narrow-band signals (for example, third-party noise) can be reproduced very well even at relatively long time intervals. Furthermore, it is also possible to obtain reproducible psychoacoustic data in the suprathreshold area, such as loudness scaling. Moreover, by offering pure signals such as sinusoidal signals, non-linearities can also be subjected to subjective interrogation, which can arise, for example, as a result of decreasing coupling quality and can be heard as "clinking". Such investigations are limited or even impossible by the initially described objective measurement methods based on evoked potentials.
  • the inventive solution has the advantage that the parameters of the signaling such as the electrical control level of the electromechanical implant converter by the implant-internal generators are quantitatively accurately determined and reproducible and not subject to fluctuations, such as in a full implant by acoustic headphone presentation the test signals are given.
  • the transfer function of the implanted sound sensor is also involved in the transfer; The sensor function can also be subject to temporal fluctuations and thus makes an exact interface definition to the transducer transfer function impossible.
  • an implantable electromechanical output transducer is in particular a converter according to US-A-5,277,694 that is, a transducer in which a wall of the transducer housing is designed as a vibratable membrane, which represents an electromechanically active heteromorph composite element together with a piezoelectric ceramic disc mounted on the membrane inside.
  • transducer assembly for partially or fully implantable hearing for direct mechanical excitation of the middle or inner ear, which is provided with a fixable at the implantation site with respect to the skull housing and with respect to the housing movable, mechanically rigid coupling element, wherein in the housing, an electromechanical transducer is housed, with which the coupling element can oscillate, which are transmitted after implantation of the transducer assembly to a middle ear ossicle or directly to the inner ear.
  • the electromechanical transducer is designed as an electromagnet arrangement which has a component fixed relative to the converter housing, in particular a toroidal coil, and a vibratable component, preferably in the form of a permanent magnet pin immersed in a central opening of the toroidal coil, which communicates with the coupling element in such a manner. that vibrations of the oscillatory component are transmitted to the coupling element.
  • a converter in the older one EP patent application 98 121 613.8 It is a converter for partially or fully implantable hearing for direct mechanical excitation of the middle or inner ear, which is provided with a fixable at the implantation housing and a movable with respect to the housing, mechanically rigid coupling element, wherein in the housing a piezoelectric element is housed, with which the coupling element can oscillate, which are transmitted to a middle ear ossicle or directly to the inner ear after implantation of the transducer, and wherein in the housing further comprises an electromagnet assembly is provided which Having fixed with respect to the housing member and a vibratable component which is in communication with the coupling element such that vibrations of the oscillatory component are transmitted to the coupling element.
  • Such a transducer has the advantage that the frequency response of the transducer can be improved both with respect to purely piezoelectric as well as against purely electromagnetic systems, so that an adequate hearing impression at a sufficient volume level is possible.
  • a substantially flat frequency response of the deflection of the coupling element in a wide frequency band at sufficiently high stimulation levels and low power consumption can be realized.
  • patient-specific signal parameters for the audiometry function can be individually adapted to the requirements and pathological needs of the patient by means of an electronic unit.
  • the electronic signal processing and amplification unit expediently has an amplifier connected downstream of the microphone, an audiological signal processing stage acted upon by the output signal of the amplifier and a driver amplifier connected upstream of the electromechanical output converter.
  • the electronic module can be provided with a signal generator arrangement for generating the signals necessary for the audiometry function and a summing element connected between the signal processing stage and the driver amplifier, via which the driver amplifier receives both the output signal of the audiological signal processing stage and the output signal of the signal generator arrangement.
  • a modified embodiment of the invention may also be provided as audiological signal processing stage, a digital signal processor, which is designed both for the preparation of the audio signal and for generating the necessary for the audiometry function signals and for the combination of the latter signals with the audio signal.
  • the signal processor expediently an analog-to-digital converter upstream and downstream of a digital-to-analog converter.
  • the digital-to-analog converter and the driver amplifier can be combined in one module.
  • the signal processor is preferably equipped with a data memory for storing patient-specific, audiological adaptation parameters and / or parameters for generating the signals for the audiometry function.
  • a microcontroller For controlling at least a part of and preferably all signal-processing and / or -producing stages, a microcontroller may advantageously be provided which expediently has a data memory for storing patient-specific, audiological adaptation parameters and / or operating parameters of the signal generator arrangement.
  • the signal processor can also be designed for controlling at least a part of and preferably all signal processing and / or generating stages.
  • a telemetry unit For data entry into the data memory is a telemetry unit that communicates wirelessly or by wire with an external programming system.
  • the signal processing and amplification unit located in the electronic hearing system path the electronic module for generating and supplying the signals required for the audiometry function and the telemetry unit as electronic module, preferably together with the energy supply unit, are preferably in a hermetically sealed and housed biocompatible implant housing.
  • the electronic module is advantageously connected via an implant lead to a subcutaneously implantable microphone in the posterior auditory canal wall and to the electromechanical output transducer via an implantable lead.
  • This compound can be fixed or detachable.
  • a connector as in US-A-5,755,743 is explained in detail.
  • Such a connection arrangement has at least one first contact, at least one second contact mounted on an elastic body and a closure mechanism for engaging the end face of the first contact with the end face of the second contact, wherein the first contact is surrounded by at least one sealing web, which at a Engagement of the contacts is pressed into the elastic body and seals the contacts to the outside.
  • the output transducer is preferably via a coupling element with an ossicle of the middle ear chain for transmitting the output side mechanical transducer oscillations coupled.
  • a coupling element with an ossicle of the middle ear chain for transmitting the output side mechanical transducer oscillations coupled.
  • the coupling element is preferably sleeve-shaped at least in the fixing and plastically cold formed by means of a crimping tool, while the coupling rod at least in the fixing rod-shaped, provided with a rough surface and under the Influence of the crimping force exerted by means of the crimping tool is not plastically cold deformable, wherein in the fixed state of the sleeve-shaped part of the coupling element coldf gutd deformed by the crimping force on the rod-shaped part of the coupling rod and permanently attached.
  • the remote from the output transducer end of the coupling rod can also be inserted into a bore of a portion of the ossicular chain and fixed there.
  • the output transducer can also be designed so that it can be coupled via an air gap to the ossicular chain or the inner ear, as described in detail in the US-A-5 015 225 is described.
  • a fully implantable hearing device includes an external system for the transcutaneous transmission of patient-specific hearing aid and audiometry programming data to the implant-side telemetry unit.
  • the telemetry unit is additionally designed as a power receiving circuit for the implant-side provision of recharging energy for the power supply unit, while the external system is also constructed as a charger.
  • a charging system are suitable for this US-A-5,279,292 known type or arrangements, as in the older EP patent applications 98 121 496.8 and 98 121 498.4 are described.
  • an implant part has, in addition to the output transducer, an energy and signal reception interface and an electronic system connected between the reception interface and the output transducer with components required for power supply and data regeneration, and an external system part comprises the microphone, an electronic module with the in the hearing aid path signal processing unit and the electronic module for generating and feeding the necessary for the audiometry function signals, a driver unit and connected to the output of the driver unit energy and signal transmission interface.
  • To the partially implantable hearing system preferably further includes an external system for transmitting patient-specific hearing aid and audiometry programming data to the electronic module of the external system part.
  • the implant system according to Fig. 1 has a microphone 10, by means of which the sound signal is recorded and converted into an electrical signal, which in an amplifier 40 is pre-amplified.
  • This pre-amplified signal is further processed in an audiological signal processing stage 50 (AP: "Audio Processor”).
  • This stage may include all known components common in modern hearing aids, such as filter stages, automatic gain controls, noise suppression devices, and so forth.
  • This processed signal is supplied to a summation element 70.
  • Further inputs of the signal combining element 70 are the one or more outputs of one or more signal generators 90 (SG1 to SGn) which generate the audiometer signals. These can be individual sinusoidal signals, narrowband signals, broadband signals and the like whose spectral position, level and phase relationships can be set to one another.
  • the audio signal processed by stage 50, together with the audio signal (s) of generator (s) 90, is supplied to a driver amplifier 80 which drives an electro-mechanical converter 20.
  • the transducer 20 stimulates the damaged inner ear by direct mechanical coupling via a coupling element 21 to a central ossicle or via an air gap coupling in, for example, electromagnetic implantable transducers.
  • the signal processing components 40, 50, 80 and the generators 90 are controlled by a microcontroller 100 ( ⁇ C) with associated data memory (S).
  • ⁇ C microcontroller 100
  • S data memory
  • patient-specific, audiological adaptation parameters as well as the audiometry parameters of the signal generators 90 can be stored in the memory area S.
  • These individual programmable data are supplied to the controller 100 via a telemetry unit 110 (T).
  • This telemetry unit 110 communicates wirelessly or by wire bidirectionally with an external programming system 120 (PS).
  • PS external programming system
  • All electronic components of the system are powered by a primary or a rechargeable secondary battery 60 with electrical operating energy except for the programming system 120.
  • Fig. 2 a further embodiment of the electronic signal module 30 is shown.
  • the signal from the microphone 10 is pre-amplified in the amplifier 40 and converted by means of an analog-to-digital converter 130 (A / D) into a digital signal, which is supplied to a digital signal processor 140 (DSP) with a data storage area S.
  • DSP digital signal processor 140
  • the signal processor 140 performs two tasks: on the one hand, as is customary in fully digital hearing aids, the audio signal is processed in accordance with the described signal processing methods for the rehabilitation of an inner ear damage.
  • the signal generators are digitally or software implemented which generate the described audiometer signals. The sum of these digital audio signals and the processed and amplified audio signal also occurs in the signal processor 140.
  • the digital output signal of the signal processor 140 is converted back to an analog signal in a digital to analogue converter 150 (D / A) and electromechanical via the driver amplifier 80 Transducer 20 is supplied.
  • the D / A converter 150 and the driver amplifier 80 can, as in Fig. 2 is indicated by a block 81, be summarized in a module. This is particularly preferable in the case where an electromagnetic system is used as the transducer 20, and in the output signal of the signal processor 140, the signal information by pulse width modulation is included, so that the required for the conversion back to an analog signal temporal integration directly from the converter 20 becomes.
  • All signal processing components are controlled by a microcontroller 100 ( ⁇ C) with associated data memory (S).
  • ⁇ C microcontroller 100
  • S data memory
  • patient-specific, audiological adaptation parameters as well as the individual operating parameters of the audiometer signal generators integrated in the signal processor 140 may be present in the memory area S of the microcontroller 100 be filed.
  • These individual programmable data are supplied to the controller 100 via a telemetry unit 110 (T).
  • This telemetry unit 110 communicates wirelessly or by wire bidirectionally with an external programming system 120 (PS). All electronic components of the system except the programming system 120 are powered by the primary or secondary battery 60 with electrical operating power.
  • PS external programming system 120
  • the Aus colbrungsform according to Fig. 3 is different from the one of Fig. 2 essentially only in that a signal processor 141 is provided which also performs the functions of the microcontroller 100 according to FIG Fig. 2 takes over. In this case, the patient-specific data of the audio signal processing as well as the audiometer functions are then likewise stored in the data memory area S of the signal processor 141.
  • Fig. 4 is a possible fully implantable embodiment according to Fig. 1 .
  • an electronic module 31 (shown without battery) is housed, which except for the absence of the battery, the module 30 of FIGS. 1 . 2 and 3 equivalent.
  • the housing 56 contains the battery 60 for the electrical supply of the implant and the telemetry device 110.
  • the microphone 10 is preferably in the off U.S. Patent 5,814,095 known manner, optionally using the in the EP-A-0 920 239 described fixation element, subcutaneously implanted in the posterior wall of the auditory canal.
  • the microphone 10 receives the sound and converts it into an electrical signal, which is supplied via the implant line 61 to the electronic module 31 in the housing 56.
  • This transducer 20 is shown in the present example as a directly coupled system, that is, the output side mechanical vibrations of the Transducer 20 are coupled via a suitable coupling element 21 directly to an ossicle of the middle ear chain, in the illustrated case to the anvil 62. Preferably, this is done in the itself US-A-5,277,694 and US-A-5 788 711 known way.
  • the transducer oscillations coupled there arrive via the ossicular chain to the inner ear and call there the corresponding one Auditory impression.
  • the external programming system 120 is shown, with which the patient-specific hearing device data and the audiometer parameters are transmitted transcutaneously through the closed skin 57 to the implant-side telemetry unit 110 as described.
  • a transmitting head 121 which is brought to the (bidirectional) data transmission via the implant and, for example, transfers the data by inductive means.
  • the battery 60 in the implant housing 56 is a secondary, rechargeable element
  • the unit 110 may also be a power receiving circuit for implant-side provision of recharging energy.
  • the external system 120 with the transmitting head 121 is, for example, a portable, wireless charger.
  • a partially implantable system is illustrated schematically.
  • the implantable part is shown as subsystem 220 and the external part to be worn on the outside as block 210.
  • the external unit 210 contains the microphone 10, a signal processing unit 30 and a driver unit 160 which generates the generated signals and operating energy for the implant part Example transmitted via a transmitting coil 170 inductively and transcutaneously through the closed skin 180 to the implanted system part 220.
  • This mode of transmission corresponds to the transmission in known, partially implantable cochlear implants or partially implantable hearing aids (see inter alia US-A-4,741,339 . EP-B-0 572 382 . US-A-5 795 287 ).
  • the electronic unit 30 of the external system part 210 contains all the necessary electronic components for hearing aid signal processing and generation of the audiometer signals, as described, for example, with reference to FIGS FIGS. 1 to 3 are explained.
  • the individual programming of the external system with patient-specific hearing aid data and with audiometer parameters takes place via the programming system 120, which is conventionally coupled to the electronic unit 30 in this case, as in conventional hearing aids.
  • the system 220 comprises a power and signal receiving interface, In the illustrated case, an inductive receiver coil 190.
  • the electronic system 200 contains all components required for power supply and data regeneration, such as demodulators and driver circuits for the electromechanical converter 20.

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)
  • Circuit For Audible Band Transducer (AREA)

Claims (23)

  1. Système auditif partiellement ou totalement implantable pour compenser une déficience auditive de l'oreille interne seule ou une déficience combinée de la transmission et de l'oreille interne, avec un micro (10) qui émet un signal audio, une unité électronique de traitement des signaux et d'amplification (40, 50, 80, 140, 141) qui est située dans une liaison électronique de système auditif traitant des signaux audio, un convertisseur électromécanique de sortie implantable (20), et une unité (60) pour alimenter l'implant en énergie, caractérisé en ce que le système auditif est complété par un module électronique (90, 140, 141) qui produit des signaux audiométriques pour un examen audiologique subjectif et une évaluation de la qualité de couplage du convertisseur électromécanique de sortie (20), et qui amène ces signaux dans la trajectoire de traitement de signaux audio de l'implant auditif.
  2. Système auditif selon la revendication 1, caractérisé en ce que des paramètres de signaux propres au patient pour la fonction d'audiométrie sont adaptables aux besoins individuels du patient à l'aide d'une unité électronique (100).
  3. Système auditif selon la revendication 1 ou 2, caractérisé en ce que l'unité électronique de traitement de signaux et d'amplification comporte un amplificateur (40) monté en aval du micro (10), un étage audiologique de traitement de signaux (50, 140) sollicité par le signal de sortie de l'amplificateur (40), et un étage excitateur (80) monté en amont du convertisseur électromécanique de sortie (20).
  4. Système auditif selon la revendication 3, caractérisé en ce que le module électronique comporte un dispositif générateur de signaux (90) pour générer les signaux nécessaires pour la fonction d'audiométrie, et un additionneur (70) qui est monté entre l'étage de traitement de signaux (50) et l'étage excitateur (80) et par l'intermédiaire duquel l'étage excitateur (80) reçoit à la fois le signal de sortie de l'étage audiologique de traitement de signaux (50) et le signal de sortie du dispositif générateur de signaux (90).
  5. Système auditif selon la revendication 3, caractérisé en ce qu'il est prévu comme étage audiologique de traitement de signaux un processeur numérique de signaux (140, 141) qui est conçu à la fois pour préparer le signal audio et produire les signaux nécessaires pour la fonction d'audiométrie, et pour réunir ces signaux et le signal audio.
  6. Système auditif selon la revendication 5, caractérisé en ce qu'il est prévu en amont du processeur de signaux (140, 141) un convertisseur analogique-numérique (130), et en aval un convertisseur numérique-analogique (150).
  7. Système auditif selon les revendications 3 et 6, caractérisé en ce que le convertisseur numérique-analogique (150) et l'étage excitateur (80) sont réunis dans un module.
  8. Système auditif selon l'une des revendications 5 à 7, caractérisé en ce que le processeur de signaux (140, 141) comporte une mémoire de données (S) pour la mise en mémoire de paramètres d'adaptation audiologiques propres au patient et/ou de paramètres pour la production des signaux pour la fonction d'audiométrie.
  9. Système auditif selon l'une des revendications précédentes, caractérisé en ce qu'une partie au moins des étages de traitement et/ou de production de signaux (40, 50, 80, 90, 130, 140, 150) sont commandés à l'aide d'un microcontrôleur (100).
  10. Système auditif selon la revendication 9, caractérisé en ce que le microcontrôleur (100) comporte une mémoire de données (S) pour la mise en mémoire de paramètres d'adaptation audiologiques propres au patient et/ou de paramètres de fonctionnement du dispositif générateur de signaux (90).
  11. Système auditif selon l'une des revendications 5 à 8, caractérisé en ce que le processeur de signaux (141) lui-même est conçu pour commander une partie au moins des étages de traitement et/ou de production de signaux (40, 80, 130, 150).
  12. Système auditif selon la revendication 10 ou les revendications 8 et 11, caractérisé en ce qu'il est prévu, pour l'entrée de données dans la mémoire de données (S), une unité de télémétrie (110).
  13. Système auditif selon la revendication 12, caractérisé par un système de programmation externe (120) qui communique, sans fil ou par fil, avec l'unité de télémétrie (110).
  14. Système auditif selon la revendication 12 ou 13, caractérisé en ce que l'appareil est conçu pour pouvoir être complètement implanté, et l'unité de traitement de signaux et d'amplification (40, 50, 80, 140, 141) située dans la liaison électronique de système auditif, le module électronique (90, 140, 141) pour produire et transmettre les signaux nécessaires pour la fonction d'audiométrie, et l'unité de télémétrie (110) sont logés sous la forme d'un module électronique (31), de préférence avec l'unité d'alimentation en énergie (60), dans un boîtier d'implant (56) hermétique et biocompatible.
  15. Système auditif selon la revendication 14, caractérisé en ce que le module électronique (31) est relié par une ligne d'implant (61) à un micro (20) apte à être implanté sous la peau dans la paroi arrière du conduit auditif.
  16. Système auditif selon la revendication 14 ou 15, caractérisé en ce que le module électronique (31) est relié par une ligne implantable (59) au convertisseur électromécanique de sortie (20).
  17. Système auditif selon l'une des revendications précédentes, caractérisé en ce que le convertisseur de sortie (20) est apte à être couplé par un élément de couplage (21) à un osselet de la chaîne de l'oreille
    moyenne pour transmettre les vibrations mécaniques du convertisseur côté sortie.
  18. Système auditif selon l'une des revendications 1 à 16, caractérisé en ce que le convertisseur de sortie (20) est conçu pour pouvoir être couplé par l'intermédiaire d'un entrefer à la chaîne d'osselets ou à l'oreille interne.
  19. Système auditif selon l'une des revendications 14 à 18, caractérisé par un système externe (120) pour la transmission transcutanée de données de programmation de système auditif et d'audiométrie individuelles pour le patient à l'unité de télémétrie (110) prévue côté implant.
  20. Système auditif selon la revendication 19, caractérisé en ce qu'il est prévu comme unité d'alimentation en énergie (60) un élément secondaire rechargeable, l'unité de télémétrie (110) est conçue en supplément comme un circuit récepteur d'énergie pour fournir côté implant une énergie de rechargement pour l'unité d'alimentation en énergie, et le système externe (120) est construit en même temps comme un appareil de chargement.
  21. Système auditif selon l'une des revendications 14 à 20, caractérisé par une unité de télécommande portable (65) pour régler ou modifier des fonctions du système auditif et d'audiométrie.
  22. Système auditif selon l'une des revendications 1 à 11, 17 ou 18, caractérisé en ce que le système est conçu pour pouvoir être en partie implanté, étant précisé qu'un élément d'implant (220) comporte en plus du convertisseur de sortie (20) une interface d'énergie et de réception de signaux (190) ainsi qu'un système électronique (200) qui est monté entre l'interface de réception et le convertisseur de sortie (20) et qui est pourvu de composants nécessaires pour l'alimentation en énergie et la régénération de données, et qu'un élément de système externe (210) comprend le micro (10), un module électronique (30) avec l'unité de traitement de signaux (40, 50, 140, 141) située dans la liaison de système auditif et avec le module électronique (90, 140, 141) pour produire et fournir les signaux nécessaires pour la fonction d'audiométrie, une unité d'excitation (160) et une interface d'énergie et d'émission de signaux (170) reliée à la sortie de l'unité d'excitation.
  23. Système auditif selon la revendication 22, caractérisé par un système externe (120) pour transmettre au module électronique (30) de l'élément de système externe (210) des données de programmation de système auditif et d'audiométrie individuelles pour le patient.
EP99122698A 1999-04-01 1999-11-15 Système auditif implantable avec audiomètre Expired - Lifetime EP1041857B1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE19914992 1999-04-01
DE19914992A DE19914992A1 (de) 1999-04-01 1999-04-01 Implantierbares Hörsystem mit Audiometer

Publications (3)

Publication Number Publication Date
EP1041857A2 EP1041857A2 (fr) 2000-10-04
EP1041857A3 EP1041857A3 (fr) 2006-05-31
EP1041857B1 true EP1041857B1 (fr) 2012-03-07

Family

ID=7903338

Family Applications (1)

Application Number Title Priority Date Filing Date
EP99122698A Expired - Lifetime EP1041857B1 (fr) 1999-04-01 1999-11-15 Système auditif implantable avec audiomètre

Country Status (6)

Country Link
US (1) US6788790B1 (fr)
EP (1) EP1041857B1 (fr)
AT (1) ATE548861T1 (fr)
AU (1) AU766943B2 (fr)
CA (1) CA2300636A1 (fr)
DE (1) DE19914992A1 (fr)

Families Citing this family (26)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7787647B2 (en) 1997-01-13 2010-08-31 Micro Ear Technology, Inc. Portable system for programming hearing aids
EP1252799B2 (fr) 2000-01-20 2022-11-02 Starkey Laboratories, Inc. Procédé et appareil pour l'adaptation des prothèses auditives
DE10041726C1 (de) 2000-08-25 2002-05-23 Implex Ag Hearing Technology I Implantierbares Hörsystem mit Mitteln zur Messung der Ankopplungsqualität
US20030163021A1 (en) * 2002-02-26 2003-08-28 Miller Douglas Alan Method and system for external assessment of hearing aids that include implanted actuators
US7248926B2 (en) 2002-08-30 2007-07-24 Advanced Bionics Corporation Status indicator for implantable systems
TWI233815B (en) * 2004-02-06 2005-06-11 Shr Ji Tau Injector of injection system for nuclear radioactive medicament and automatic feeding device for physiological saline cartridge
US7651460B2 (en) * 2004-03-22 2010-01-26 The Board Of Regents Of The University Of Oklahoma Totally implantable hearing system
WO2007012700A1 (fr) * 2005-07-26 2007-02-01 Mbdsys (Sarl) Dispositif de correction acoustique a moyens propres de parametrage
US20080285780A1 (en) * 2005-11-01 2008-11-20 Koninklijke Philips Electronics, N.V. Method to Adjust a Hearing Aid Device, Hearing Aid System and Hearing Aid Device
EP2278827A1 (fr) 2006-03-23 2011-01-26 Phonak Ag Procedé pour l'adaptation individuelle d'un appareil auditif
US7715571B2 (en) * 2006-03-23 2010-05-11 Phonak Ag Method for individually fitting a hearing instrument
CA2601662A1 (fr) 2006-09-18 2008-03-18 Matthias Mullenborn Interface sans fil pour programmer des dispositifs d'aide auditive
EP2066140B1 (fr) * 2007-11-28 2016-01-27 Oticon Medical A/S Procédé pour adapter une prothèse auditive ancrée dans l'os sur un utilisateur et système de prothèse auditive à conduction osseuse ancrée dans l'os
KR100977525B1 (ko) * 2008-04-11 2010-08-23 주식회사 뉴로바이오시스 적외선 통신 방식의 귓속형 인공 와우 장치
EP2303204A4 (fr) * 2008-06-25 2014-06-25 Cochlear Ltd Système de microphone implantable à performances améliorées
US8144909B2 (en) * 2008-08-12 2012-03-27 Cochlear Limited Customization of bone conduction hearing devices
AU2010225449A1 (en) 2009-03-16 2011-10-13 Cochlear Limited Transcutaneous modulated power link for a medical implant
US8675900B2 (en) * 2010-06-04 2014-03-18 Exsilent Research B.V. Hearing system and method as well as ear-level device and control device applied therein
CN103328041B (zh) 2010-10-19 2016-03-16 耳蜗有限公司 用于将植入式医疗设备连接至外部电子设备的中继接口
CN103503484B (zh) 2011-03-23 2017-07-21 耳蜗有限公司 听力设备的调配
US9313589B2 (en) * 2011-07-01 2016-04-12 Cochlear Limited Method and system for configuration of a medical device that stimulates a human physiological system
US10455336B2 (en) 2013-10-11 2019-10-22 Cochlear Limited Devices for enhancing transmissions of stimuli in auditory prostheses
WO2016209682A1 (fr) * 2015-06-23 2016-12-29 Duke University Systèmes et procédés utilisant une optimisation basée sur un modèle de paramètres de stimulation de la moelle épinière
US10348891B2 (en) 2015-09-06 2019-07-09 Deborah M. Manchester System for real time, remote access to and adjustment of patient hearing aid with patient in normal life environment
CN109893139A (zh) * 2019-04-02 2019-06-18 佛山博智医疗科技有限公司 听力测试状态反馈***
CN114305402B (zh) * 2021-12-29 2024-03-01 中山大学附属第三医院（中山大学肝脏病医院） 基于云平台的纯音测听质量评价***

Family Cites Families (22)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE3205685A1 (de) * 1982-02-17 1983-08-25 Robert Bosch Gmbh, 7000 Stuttgart Hoergeraet
CA1246680A (fr) 1984-10-22 1988-12-13 James M. Harrison Transfert d'energie pour prothese implantee
US5015225A (en) 1985-05-22 1991-05-14 Xomed, Inc. Implantable electromagnetic middle-ear bone-conduction hearing aid device
DE3918086C1 (fr) * 1989-06-02 1990-09-27 Hortmann Gmbh, 7449 Neckartenzlingen, De
US5042084A (en) 1989-09-07 1991-08-20 Cochlear Pty. Limited Three wire system for Cochlear implant processor
DE4104359A1 (de) * 1991-02-13 1992-08-20 Implex Gmbh Ladesystem fuer implantierbare hoerhilfen und tinnitus-maskierer
DE4104358A1 (de) * 1991-02-13 1992-08-20 Implex Gmbh Implantierbares hoergeraet zur anregung des innenohres
US5624376A (en) 1993-07-01 1997-04-29 Symphonix Devices, Inc. Implantable and external hearing systems having a floating mass transducer
US5554096A (en) 1993-07-01 1996-09-10 Symphonix Implantable electromagnetic hearing transducer
EP0681411B1 (fr) * 1994-05-06 2003-01-29 Siemens Audiologische Technik GmbH Prothèse auditive programmable
US6118877A (en) * 1995-10-12 2000-09-12 Audiologic, Inc. Hearing aid with in situ testing capability
US5795287A (en) 1996-01-03 1998-08-18 Symphonix Devices, Inc. Tinnitus masker for direct drive hearing devices
DE19618961B4 (de) * 1996-05-10 2004-09-16 Phonak Ag Gerät zur elektromechanischen Stimulation und Prüfung des Gehörs
DE19618964C2 (de) 1996-05-10 1999-12-16 Implex Hear Tech Ag Implantierbares Positionier- und Fixiersystem für aktorische und sensorische Implantate
DE19622669A1 (de) 1996-06-05 1997-12-11 Implex Gmbh Implantierbare Einheit
US5814095A (en) * 1996-09-18 1998-09-29 Implex Gmbh Spezialhorgerate Implantable microphone and implantable hearing aids utilizing same
DE19638159C2 (de) * 1996-09-18 2000-09-07 Implex Hear Tech Ag Vollständig implantierbare Hörhilfe zur elektrischen Anregung des Gehörs
DE19638158C2 (de) * 1996-09-18 2000-08-31 Implex Hear Tech Ag Implantierbares Mikrofon
US5999856A (en) 1997-02-21 1999-12-07 St. Croix Medical, Inc. Implantable hearing assistance system with calibration and auditory response testing
DK0917398T3 (da) * 1997-11-12 2007-09-03 Siemens Audiologische Technik Höreapparat og fremgangsmåde til indstilling af audiologiske/akustiske parametre
DE19859171C2 (de) * 1998-12-21 2000-11-09 Implex Hear Tech Ag Implantierbares Hörgerät mit Tinnitusmaskierer oder Noiser
DE19914993C1 (de) * 1999-04-01 2000-07-20 Implex Hear Tech Ag Vollimplantierbares Hörsystem mit telemetrischer Sensorprüfung

Also Published As

Publication number Publication date
AU766943B2 (en) 2003-10-23
ATE548861T1 (de) 2012-03-15
EP1041857A2 (fr) 2000-10-04
US6788790B1 (en) 2004-09-07
EP1041857A3 (fr) 2006-05-31
CA2300636A1 (fr) 2000-10-01
AU2226700A (en) 2000-10-05
DE19914992A1 (de) 2000-12-07

Similar Documents

Publication Publication Date Title
EP1041857B1 (fr) Système auditif implantable avec audiomètre
DE19859171C2 (de) Implantierbares Hörgerät mit Tinnitusmaskierer oder Noiser
EP1181950B1 (fr) Système auditif implantable comportant des moyens de mesure de la qualité d'accouplement
EP1145734B1 (fr) Système au moins partiellement implantable de réhabilitation d'un trouble auditif
DE19914993C1 (de) Vollimplantierbares Hörsystem mit telemetrischer Sensorprüfung
DE19915846C1 (de) Mindestens teilweise implantierbares System zur Rehabilitation einer Hörstörung
EP1246503B1 (fr) Système auditif entièrement implantable
DE10031832C2 (de) Hörgerät zur Rehabilitation einer Hörstörung
DE19618961B4 (de) Gerät zur elektromechanischen Stimulation und Prüfung des Gehörs
US5999856A (en) Implantable hearing assistance system with calibration and auditory response testing
DE10018360C2 (de) Mindestens teilimplantierbares System zur Rehabilitation einer Hörstörung
DE10018361C2 (de) Mindestens teilimplantierbares Cochlea-Implantat-System zur Rehabilitation einer Hörstörung
EP1179969B1 (fr) Système auditif au moins partiellement implantable
DE19638159C2 (de) Vollständig implantierbare Hörhilfe zur elektrischen Anregung des Gehörs
DE10046938A1 (de) Mindestens teilimplantierbares Hörsystem mit direkter mechanischer Stimulation eines lymphatischen Raums des Innenohres
EP0831673A2 (fr) Microphone implantable
DE10057584A1 (de) Gerät zür präoperativen Demonstration implantierbarer Hörsysteme

Legal Events

Date Code Title Description
PUAI Public reference made under article 153(3) epc to a published international application that has entered the european phase

Free format text: ORIGINAL CODE: 0009012

AK Designated contracting states

Kind code of ref document: A2

Designated state(s): AT BE CH CY DE DK ES FI FR GB GR IE IT LI LU MC NL PT SE

AX Request for extension of the european patent

Free format text: AL;LT;LV;MK;RO;SI

RAP1 Party data changed (applicant data changed or rights of an application transferred)

Owner name: COCHLEAR LIMITED

PUAL Search report despatched

Free format text: ORIGINAL CODE: 0009013

AK Designated contracting states

Kind code of ref document: A3

Designated state(s): AT BE CH CY DE DK ES FI FR GB GR IE IT LI LU MC NL PT SE

AX Request for extension of the european patent

Extension state: AL LT LV MK RO SI

17P Request for examination filed

Effective date: 20061128

AKX Designation fees paid

Designated state(s): AT DE

17Q First examination report despatched

Effective date: 20080409

GRAP Despatch of communication of intention to grant a patent

Free format text: ORIGINAL CODE: EPIDOSNIGR1

GRAS Grant fee paid

Free format text: ORIGINAL CODE: EPIDOSNIGR3

GRAA (expected) grant

Free format text: ORIGINAL CODE: 0009210

AK Designated contracting states

Kind code of ref document: B1

Designated state(s): AT DE

REG Reference to a national code

Ref country code: AT

Ref legal event code: REF

Ref document number: 548861

Country of ref document: AT

Kind code of ref document: T

Effective date: 20120315

REG Reference to a national code

Ref country code: DE

Ref legal event code: R096

Ref document number: 59915325

Country of ref document: DE

Effective date: 20120503

PLBE No opposition filed within time limit

Free format text: ORIGINAL CODE: 0009261

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: NO OPPOSITION FILED WITHIN TIME LIMIT

26N No opposition filed

Effective date: 20121210

REG Reference to a national code

Ref country code: DE

Ref legal event code: R097

Ref document number: 59915325

Country of ref document: DE

Effective date: 20121210

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: DE

Payment date: 20171108

Year of fee payment: 19

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: AT

Payment date: 20171026

Year of fee payment: 19

REG Reference to a national code

Ref country code: DE

Ref legal event code: R119

Ref document number: 59915325

Country of ref document: DE

REG Reference to a national code

Ref country code: AT

Ref legal event code: MM01

Ref document number: 548861

Country of ref document: AT

Kind code of ref document: T

Effective date: 20181115

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: DE

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20190601

Ref country code: AT

Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES

Effective date: 20181115