EP1014755A2 - Prothèse auditive implantable avec masquage de acuphène - Google Patents

Prothèse auditive implantable avec masquage de acuphène Download PDF

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Publication number
EP1014755A2
EP1014755A2 EP99122697A EP99122697A EP1014755A2 EP 1014755 A2 EP1014755 A2 EP 1014755A2 EP 99122697 A EP99122697 A EP 99122697A EP 99122697 A EP99122697 A EP 99122697A EP 1014755 A2 EP1014755 A2 EP 1014755A2
Authority
EP
European Patent Office
Prior art keywords
hearing aid
aid according
signal
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.)
Withdrawn
Application number
EP99122697A
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German (de)
English (en)
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
Implex AG Hearing Technology
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Filing date
Publication date
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Application filed by Implex AG Hearing Technology filed Critical Implex AG Hearing Technology
Publication of EP1014755A2 publication Critical patent/EP1014755A2/fr
Withdrawn legal-status Critical Current

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Classifications

    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; 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
    • 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
    • H04R25/75—Electric tinnitus maskers providing an auditory perception
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2460/00—Details of hearing devices, i.e. of ear- or headphones covered by H04R1/10 or H04R5/033 but not provided for in any of their subgroups, or of hearing aids covered by H04R25/00 but not provided for in any of its subgroups
    • H04R2460/13—Hearing devices using bone conduction transducers

Definitions

  • tinnitus maskers are therefore known (WO-A-90/07251); These are small, battery-operated devices that are worn behind or in the ear, similar to a hearing aid, and cover up the tinnitus in a psycho-acoustic way ("masking") with artificial sounds, which are emitted into the ear canal, for example, via a hearing aid speaker lower disturbing ear noises as far as possible below the threshold of perception.
  • the artificial sounds are often narrowband noises (e.g.
  • third-octave noise which can be adjusted in their spectral position and their volume level via a programming device in order to enable the best possible adaptation to the individual ear noise situation.
  • retraining method has recently existed, whereby the perception of tinnitus is also to be largely suppressed by the combination of a mental training program and the presentation of a broadband sound (noise) near the resting hearing threshold.
  • noisesers magazines are also referred to as “noisers” (magazine Hearing Acoustics "2/97, pages 26 and 27).
  • the present invention has as its object the one mentioned Inner ear damage and tinnitus in the event of simultaneous occurrence while avoiding the Deficiencies outlined above can be treated more easily and effectively.
  • a hearing aid for the rehabilitation of a Inner hearing loss with a microphone that emits an audio signal, one in one audio signal processing, electronic hearing aid path lying electronic Signal processing and amplification unit, an implantable electromechanical Output converter and a unit for energetic supply of the implant, this is Object achieved according to the invention in that the hearing aid for the rehabilitation of tinnitus is provided with an electronic module which can be used to mask tinnitus or signals necessary for a noise function are generated and into the audio signal processing path of the hearing implant.
  • the hearing aid according to the invention allows, with a single active, at least partially implantable system not only inner ear damage, but also and additionally to treat tinnitus.
  • a stigmatization of the patient by visible external Device parts are kept small in the case of a partially implantable simultaneous therapy system, and it is completely avoided with a fully implantable device.
  • the one for the at least partially Implantation of the combination device required surgical intervention and thus associated residual risks do not go beyond what is at least partially the case implantable hearing aid only or with an at least partially implantable tinnitus masker only is to be accepted anyway.
  • An implantable electromechanical output converter is particularly suitable Converter according to US-A-5 277 694, that is a converter in which a wall of the Converter housing is designed as a vibratable membrane, which together with one on the Piezoelectric ceramic disc applied to the inside of the membrane an electromechanical represents active heteromorph composite element.
  • the electromechanical transducer is an electromagnet arrangement formed, which is a component fixed with respect to the converter housing, in particular a toroidal coil, and a vibratable component, preferably in the form of a has a central opening of the ring coil immersing permanent magnet pin, soft with the coupling element is connected in such a way that vibrations of the vibratable Component are transferred to the coupling element.
  • a converter of the type disclosed in the older EP patent application 98 121 613.8 is also advantageous described type. It is a converter for partially or fully implantable Hearing aids for the direct mechanical excitation of the middle or inner ear, with a housing that can be fixed at the implantation site and a movable with respect to the housing mechanically rigid coupling element is provided, with a piezoelectric in the housing Is housed element with which the coupling element can be set in vibration, after implantation of the transducer on a middle ear ossicle or directly on the Inner ear are transmitted, and wherein also in the housing Electromagnet arrangement is provided which is a component fixed with respect to the housing and has an oscillatable component, which is so soft with the coupling element in Connection is that vibrations of the vibratable component on the coupling element be transmitted.
  • Such a converter has the advantage that the frequency response of the converter both purely piezoelectric and purely electromagnetic Systems can be improved so that an adequate auditory impression with sufficient Volume level is enabled.
  • a largely flat frequency response the deflection of the coupling element in a wide frequency band at sufficiently high Stimulation levels and low power consumption can be realized.
  • the hearing aid according to the invention there are preferably patient-specific ones Signal parameters for tinnitus masking or noise function using an electronic Unity to the needs and pathological needs of the patient individually customizable.
  • the electronic signal processing and amplification unit expediently has one Microphone downstream amplifier, one with the output signal of the amplifier applied audiological signal processing level and one the electromechanical Output converter upstream driver amplifier.
  • This can be advantageous electronic module with a signal generator arrangement for generating the for Tinnitus masking or the noiser function necessary signals and one between the Signal processing stage and the driver amplifier-connected summing element, via the driver amplifier both the output signal of the audiological signal processing stage as well as the output signal of the signal generator arrangement.
  • a digital signal processor can be provided both for processing the audio signal and for generating tinnitus masking or Noiserfunktion necessary signals and for the summary of the the latter signals is designed with the audio signal.
  • a digital signal processor can be provided both for processing the audio signal and for generating tinnitus masking or Noiserfunktion necessary signals and for the summary of the the latter signals is designed with the audio signal.
  • the digital-to-analog converter and the driver amplifier can be combined in one module his.
  • the signal processor is preferably with a data memory for storing patient-specific, audiological adjustment parameters and / or parameters for the Generation of signals for tinnitus masking or the noiser function.
  • a microcontroller can advantageously be provided expediently a data memory for storing patient-specific, audiological adaptation parameters and / or operating parameters of the signal generator arrangement having.
  • the signal processor can also itself for controlling at least part of the and preferably all signal processing and / or generating stages.
  • a telemetry unit which is equipped with a external programming system communicates wirelessly or wired.
  • the hearing aid is designed to be fully implantable, those in the are preferably electronic hearing aid path signal processing and amplification unit, the electronic module for generating and feeding in for tinnitus masking or Noise function necessary signals and the telemetry unit as an electronic module, expediently together with the energy supply unit, in a hermetically sealed and biocompatible implant housing.
  • the electronics module is advantageous here via an implant line with a subcutaneously in the posterior wall of the auditory canal implantable microphone and via an implantable line with the electromechanical Output converter connected. This connection can be fixed or detachable. For a detachable connection is particularly suitable for a plug connection as described in US-A-5 755 743 is explained in detail.
  • Such a connection arrangement has at least a first contact, at least one second supported on an elastic body Contact and a locking mechanism for engaging the end face of the first Contact with the end face of the second contact, wherein the first contact of is surrounded at least one sealing web, which when the contacts engage in the is pressed in elastic body and seals the contacts to the outside.
  • the output converter is preferably connected to an ossicle via a coupling element Middle ear chain for transmission of the mechanical converter vibrations on the output side connectable.
  • Solutions in US-A-5 277 694 and in are particularly suitable for this US-A-5 941 814 described.
  • an actively vibratable part of the Output converter with a coupling rod to be mechanically firmly connected via a Coupling element is coupled to a part of the ossicular chain.
  • the coupling element is preferably sleeve-shaped at least in the fixing area formed and is plastically cold-deformable by means of a crimping tool, while the Coupling rod is rod-shaped at least in the fixing area, with a rough surface provided and not under the influence of the crimping force exerted by the crimping tool is plastically cold deformable, with the sleeve-shaped part of the Coupling element deformed cold-flowing by the crimping force on the rod-shaped part of the Coupling rod is free of play and permanently attached.
  • the end of the coupling rod can also be in a hole in part of the ossicular chain inserted and fixed there.
  • the output converter can also be designed so that it is connected to the air gap
  • the ossicular chain or the inner ear can be coupled, as is described in detail in US Pat. No. 5,015,225 is described.
  • a fully implantable hearing aid is one external system for transcutaneous transmission of patient-specific hearing aids and Tinnitus masker or noiser programming data to the implant-side telemetry unit.
  • the telemetry unit is preferably also used as an energy receiving circuit for the provision of recharging energy on the implant side for the energy supply unit trained while the external system is also a charger is constructed.
  • a charging system from US Pat. No. 5,279,292 is particularly suitable for this known type or arrangements, as in the older EP patent applications 98 121 496.8 and 98 121 498.4 are described.
  • a portable remote control unit for setting or changing is also useful of hearing aid and tinnitus masking or noiser functions.
  • an implant part preferably has in addition to that Output converter a power and signal receiving interface and one between the Receiving interface and the output converter switched electronic system with for the components required for energy supply and data regeneration, and one External system part includes the microphone, an electronic module with the in the hearing aid path lying signal processing unit and the electronic module for generation and Feeding of the signals necessary for tinnitus masking or the noise function, a driver unit and an energy and connected to the output of the driver unit Signal transmission interface.
  • the partially implantable hearing aid preferably also includes an external system Transfer of patient-specific hearing aid and tinnitus masker or noiser 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 is in an amplifier 40 is preamplified.
  • This pre-amplified signal is in an audiological signal processing stage 50 (AP: "Audio Processor") processed further.
  • Audio Processor audiological signal processing stage 50
  • This level can all known, at components common to modern hearing aids such as filter stages, automatic gain controls, Interference signal suppression devices and so on included.
  • This edited Signal is fed to a summation element 70.
  • Further inputs of the signal-summarizing element 70 are the one or more outputs one or more signal generators 90 (SG1 to SGn) which generate the signals, which are required for tinnitus masking or noiser function.
  • This can in itself known manner single sinusoidal signals, narrowband signals, broadband signals and the like be, the spectral position, level and phase relationships to each other are adjustable.
  • the audio signal processed by stage 50, along with the masker (s), is related Noiser signals of the generator (s) 90 to a driver amplifier 80 supplied, which controls an electromechanical converter 20.
  • the converter 20 stimulates the damaged inner ear by direct mechanical coupling via a coupling element 21 a middle ear crosspiece 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) controlled. In the memory area S in particular patient-specific, audiological Matching parameters and the individual operating parameters of the signal generators 90 for Tinnitus masking or noiser function.
  • These individual, programmable Data is supplied to controller 100 via a telemetry unit 110 (T).
  • This Telemetry unit 110 communicates wirelessly or wired bidirectionally with one external programming system 120 (PS).
  • All electronic components of the system are except for the programming system 120 by a primary or a rechargeable secondary battery 60 with electrical operating energy provided.
  • FIG. 2 A further embodiment of the electronic signal module 30 is shown in FIG. 2.
  • the signal of the microphone 10 is pre-amplified in the amplifier 40 and by means of an analog-to-digital converter 130 (A / D) is converted into a digital signal that corresponds to a digital Signal processor 140 (DSP) with a data storage area S is supplied.
  • DSP digital Signal processor 140
  • the signal processor 140 takes on two tasks: on the one hand, as in fully digital hearing aids usual the audio signal the described signal processing methods for a Rehabilitation of an inner ear damage prepared accordingly. On the other hand, in the Signal processor 140 digitally or software-implemented the signal generators that the for Masking the tinnitus or necessary to achieve a noiser function Generate signals.
  • the summary of these digital masker or Noiser signals and the processed and amplified audio signal also takes place in the signal processor 140.
  • the digital output signal of the signal processor 140 is in a digital-to-analog converter 150 (D / A) converted back into an analog signal and via the driver amplifier 80 fed to the electromechanical converter 20.
  • the D / A converter 150 and the driver amplifier 80 can, as in FIG. 2, by a block 81 is indicated to be combined in one module. This is particularly the case preferable in which 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 time required for the conversion back into an analog signal Integration is taken over directly by the converter 20.
  • All signal processing components are controlled by a microcontroller 100 ( ⁇ C) associated data storage (S) controlled.
  • ⁇ C microcontroller 100
  • S data storage
  • S of the microcontroller 100 can, in particular, patient-specific, audiological adjustment parameters as well as the individual operating parameters of the signal generators integrated in the signal processor 140 for tinnitus masking or noiser function.
  • These individual, Programmable data is sent to controller 100 via a telemetry unit 110 (T) fed.
  • This telemetry unit 110 communicates wirelessly or wired bidirectionally with an external programming system 120 (PS). All electronic components of the system are down to the programming system 120 by the primary or secondary Battery 60 supplied with electrical operating energy.
  • the embodiment according to FIG. 3 differs essentially from that of FIG. 2 only in that a signal processor 141 is provided, which also functions as Microcontroller 100 according to FIG. 2 takes over.
  • the patient-specific Data from audio signal processing as well as tinnitus masking or noise function then also stored in the data storage area S of the signal processor 141.
  • FIG. 4 shows a possible fully implantable embodiment according to FIG. 1, 2 or Fig. 3 is shown schematically.
  • housing 56 is an electronics module 31 (shown without a battery), which except for the Absence of the battery corresponds to the module 30 of Figures 1, 2 and 3. It also contains Housing 56, the battery 60 for the electrical supply of the implant and the telemetry device 110.
  • the microphone 10 is preferably known from US-A-5,814,095 Way, optionally using that described in EP-A-0 920 239 Fixation element, implanted subcutaneously in the posterior wall of the auditory canal. The microphone 10 picks up the sound and converts it into an electrical signal that is transmitted via the Implant line 61 is supplied to the electronics module 31 in the housing 56.
  • the audiologically processed and amplified signal, the corresponding tinnitus mask or relation Noiser signals attached by the electronic unit 31 arrives via the implantable line 59 to the electromechanical transducer 20.
  • 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 determined by a suitable Coupling element 21 directly coupled to an ossicle of the middle ear chain, in the case shown the anvil 62. This is preferably done in US-A-5 277 694 and US-A-5 788 711 known manner.
  • the transducer vibrations injected there pass through the ossicle chain to the inner ear and cause the corresponding auditory impression there.
  • the external programming system 120 is shown in FIG. 4, with which, as described the patient-specific hearing aid and tinnitus masker or noiser data transcutaneously through the closed skin 57 to the implant-side telemetry unit 110 are transmitted.
  • a transmit head 121 is used for this purpose, for (bidirectional) data transmission the data is brought over the implant and, for example, inductively transferred.
  • the battery 60 in the implant housing 56 is a secondary, rechargeable Element, unit 110 may also include an energy receiving circuit for the implant side Provision of recharging energy. Then the external system 120 with the transmitter head 121 a portable, wireless charger, for example.
  • a portable remote control unit 65 is also shown, with which the patient Set essential hearing aid and tinnitus masker or noiser functions or can change.
  • a partially implantable system is illustrated schematically in FIG.
  • 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, for example, inductively and transcutaneously through the transmitter coil 170 closed skin 180 is transmitted to the implanted system part 220.
  • This type of transmission corresponds to the transmission in known, partially implantable cochlear implants or partially implantable hearing aids or partially implantable tinnitus maskers (see among others US-A-4 741 339, EP-B-0 572 382, US-A-5 795 287).
  • the electronic Unit 30 of external system part 210 contains all the necessary electronic components for hearing aid signal processing and tinnitus masking or noise function, as they are explained for example with reference to Figures 1 to 3.
  • the individual programming of the external system with patient-specific hearing aid and tinnitus masker or noiser data takes place via the programming system 120, which is as in In this case, conventional hearing aids are usually wired to the electronic unit 30 is coupled.
  • the system 220 includes an energy and signal reception interface, in the case shown an inductive receiving coil 190.
  • the electronic System 200 contains everything necessary for energy supply and data regeneration Components such as demodulators and driver circuits for the electromechanical Converter 20.
EP99122697A 1998-12-21 1999-11-15 Prothèse auditive implantable avec masquage de acuphène Withdrawn EP1014755A2 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE19859171A DE19859171C2 (de) 1998-12-21 1998-12-21 Implantierbares Hörgerät mit Tinnitusmaskierer oder Noiser
DE19859171 1998-12-21

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EP1014755A2 true EP1014755A2 (fr) 2000-06-28

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EP99122697A Withdrawn EP1014755A2 (fr) 1998-12-21 1999-11-15 Prothèse auditive implantable avec masquage de acuphène

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US (1) US6394947B1 (fr)
EP (1) EP1014755A2 (fr)
DE (1) DE19859171C2 (fr)

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EP1041857A2 (fr) * 1999-04-01 2000-10-04 IMPLEX Aktiengesellschaft Hearing Technology Système auditif implantable avec audiomètre
EP1173044A2 (fr) * 2000-06-30 2002-01-16 Cochlear Limited Système implantable de réhabilitation d'un trouble auditif
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EP1041857A2 (fr) * 1999-04-01 2000-10-04 IMPLEX Aktiengesellschaft Hearing Technology Système auditif implantable avec audiomètre
EP1041857A3 (fr) * 1999-04-01 2006-05-31 Cochlear Limited Système auditif implantable avec audiomètre
EP1173044A2 (fr) * 2000-06-30 2002-01-16 Cochlear Limited Système implantable de réhabilitation d'un trouble auditif
EP1173044A3 (fr) * 2000-06-30 2005-08-17 Cochlear Limited Système implantable de réhabilitation d'un trouble auditif
US7376563B2 (en) 2000-06-30 2008-05-20 Cochlear Limited System for rehabilitation of a hearing disorder
EP1215937A2 (fr) * 2000-12-14 2002-06-19 IMPLEX Aktiengesellschaft Hearing Technology Elément de fixation pour microphone implantable
EP1215937A3 (fr) * 2000-12-14 2010-04-14 Phonak Ag Elément de fixation pour microphone implantable
WO2007091180A2 (fr) * 2006-02-07 2007-08-16 Med-El Elektromedizinische Geraete Gmbh Implant cochléaire de suppression d'acouphène
WO2007091180A3 (fr) * 2006-02-07 2008-01-17 Med El Elektromed Geraete Gmbh Implant cochléaire de suppression d'acouphène

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US6394947B1 (en) 2002-05-28
DE19859171A1 (de) 2000-07-20
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