EP1191815A2 - Système auditif au moins partiellement implantable avec stimulation mécanique d'un espace lymphatique de l'oreille interne - Google Patents

Système auditif au moins partiellement implantable avec stimulation mécanique d'un espace lymphatique de l'oreille interne Download PDF

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Publication number
EP1191815A2
EP1191815A2 EP01118050A EP01118050A EP1191815A2 EP 1191815 A2 EP1191815 A2 EP 1191815A2 EP 01118050 A EP01118050 A EP 01118050A EP 01118050 A EP01118050 A EP 01118050A EP 1191815 A2 EP1191815 A2 EP 1191815A2
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EP
European Patent Office
Prior art keywords
transducer
intracochlear
hearing system
hearing
arrangement
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
EP01118050A
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German (de)
English (en)
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EP1191815B1 (fr
EP1191815A3 (fr
Inventor
Hans Dr.-Ing. Leysieffer
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Sonova Holding AG
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Phonak AG
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Publication of EP1191815A3 publication Critical patent/EP1191815A3/fr
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    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Electric hearing aids
    • H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
    • H04R25/604—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers
    • H04R25/606—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers acting directly on the eardrum, the ossicles or the skull, e.g. mastoid, tooth, maxillary or mandibular bone, or mechanically stimulating the cochlea, e.g. at the oval window
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R2217/00—Details of magnetostrictive, piezoelectric, or electrostrictive transducers covered by H04R15/00 or H04R17/00 but not provided for in any of their subgroups
    • H04R2217/01—Non-planar magnetostrictive, piezoelectric or electrostrictive benders

Definitions

  • the present invention relates to an at least partially implantable system for rehabilitation a hearing disorder with at least one sound-absorbing sensor (microphone), an electronic arrangement for audio signal processing and amplification, an electrical Power supply unit, which individual components of the system with electricity supplied, and an output-side actuator arrangement for direct mechanical Stimulation of a lymphatic space in the inner ear.
  • a sound-absorbing sensor microphone
  • an electrical Power supply unit which individual components of the system with electricity supplied
  • an output-side actuator arrangement for direct mechanical Stimulation of a lymphatic space in the inner ear.
  • hearing impairment is intended to combine all types of inner ear damage Inner and middle ear damage as well as occasional or permanent ear noises (Tinnitus) can be understood.
  • Cochlear implants are inserted into the cochlea by a stimulus electrode array, designed by is controlled by an electronic system, this being hermetically sealed and biocompatible encapsulated electronics module surgically in the bony area behind the ear (mastoid) is embedded.
  • the electronic system essentially only contains decoding and Driver circuits for the stimulation electrodes; the acoustic sound recording, the change of this Sound signal into electrical signals and their further processing is basically done externally in a so-called speech processor, which is worn on the outside of the body.
  • the speech processor encodes the preprocessed signals accordingly to a high frequency Carrier signal which is transmitted via an inductive coupling through the closed skin (transcutaneously) is transferred to the implant.
  • the sound-picking microphone is without exception outside the body and in most applications in a one worn on the auricle Case of a behind-the-ear hearing aid (BTE) and it is connected to a cable connected to the speech processor.
  • BTE behind-the-ear hearing aid
  • Electromechanical systems are implemented using various physical transducer principles such as through electromagnetic and piezoelectric systems.
  • Tinnitus maskers available; these are small, battery powered devices that are similar a hearing aid behind or in the ear and by artificial sound that over a hearing aid speaker, for example, is emitted into the ear canal, the tinnitus mask ("mask”) in a psycho-acoustic way and the annoying ear noise lower it below the perception threshold as far as possible.
  • the artificial sounds are often narrowband noises (for example third-octave noise), which in their spectral position and Volume levels can be adjusted via a programming device in order to achieve the best possible adjustment to enable the individual ear noise situation.
  • narrowband noises for example third-octave noise
  • retraining method whereby by the combination of a mental Training program and the performance of a broadband sound (noise) near the Hearing threshold, the perceptibility of tinnitus can also be largely suppressed should (H. Knör, "Tinnitus Retraining Therapy and Hearing Acoustics” magazine “Hearing Acoustics” 2/97, Pages 26 and 27).
  • These devices are also referred to as “noisers”.
  • This adaptability can be realized in that the necessary setting data of the signal generation and Feed electronics in the same physical and logical data storage area of the implant system stored and programmed in terms of hardware and software, and via appropriate electronic actuators, the supply of the masker or Control the noise signal in the audio path of the hearing implant.
  • the at least partially implantable hearing systems for rehabilitation described above an inner ear damage that is based on an output-side electromechanical transducer differ essentially from conventional, conventional hearing aids only in that the acoustic stimulus on the output side (an amplified sound signal before the eardrum) through an increased mechanical stimulus of the middle or Inner ear is replaced.
  • the acoustic stimulus of a conventional hearing aid leads finally about the mechanical excitation of the eardrum and the subsequent one Middle ear also to a vibratory, i.e. mechanical stimulus of the inner ear.
  • a vibratory stimulus to the damaged inner ear guided for example, increased mechanical vibration of the stirrup in the oval window of the inner ear.
  • stapedectomy uses a passive prosthesis that on the one hand is mostly fixed to the long anvil process by a bracket and on the other hand with its mostly circular shaft in an artificially made opening in the stirrup footplate is used.
  • the stirrup can also be removed completely.
  • the Vibrations of the eardrum are transferred to the anvil using the hammer and cause corresponding vibrations of the passive prosthesis, which lead to dynamic volume shifts in the perilymph of the inner ear, thus triggering traveling waves on the basilar membrane and ultimately lead to an auditory impression.
  • This method has been very safe and successful worldwide for decades as a reconstructive middle ear surgery applied.
  • the insertion of the opening in the stirrup footplate is done by fine surgical Instruments or achieved in particular by laser techniques.
  • the older EP patent application 00 119 195.6 describes a hearing system with a plurality of electromechanical transducers arranged along the cochlea for excitation the fluid-filled inner ear spaces by forming a traveling wave configuration on the basilar membrane.
  • the older EP patent application 01 109 191.5 discloses a hearing system with a dual intracochlear arrangement, which in combination a stimulator arrangement with at least one stimulator element for at least indirect mechanical Stimulation of the inner ear and an electrically acting stimulating electrode arrangement with at least one cochlear implant electrode for electrical stimulation of the Has inner ear.
  • US-A-5 977 689 discloses a hearing system microactuator with an implantable device in the middle ear Hollow body described, which is filled with an incompressible liquid and in which at least one piezoelectric connected to a relatively large-area membrane Converter is housed.
  • the interior of the hollow body is connected to a nozzle, which is used in an artificial fenestration of the promontory and which its end remote from the hollow body of one in comparison to the transducer membrane small membrane is complete.
  • the converter will practice when using appropriate electrical signals is applied, force on the liquid in the hollow body , causing the small nozzle end membrane in contact with fluid in the inner ear of the micro actuator is deflected.
  • a system of the type mentioned is known in which a microactuator with a flat flexible membrane is provided.
  • the micro actuator membrane forms the end face a screw that is screwed into an artificial window in the promontory, or the microactuator is inserted directly into such a window in such a way that its flat membrane in the inner ear fluid contacted.
  • the microactuator sits in the shaft of a passive stapedectomy prosthesis of the type discussed above, for combined passive and active stimulation to care.
  • the invention has for its object an at least partially implantable system for the rehabilitation of a hearing impairment that is capable of improving To provide rehabilitation for sensory hearing disorders.
  • Another advantage of the present invention is that a direct, electromechanical stimulation of the cochlea the occurrence of feedback (coupling of the output signal into the sensor / microphone) as expected largely reduced is because the ossicle chain and thus the eardrum is not or clearly is reduced to vibrations. This is particularly advantageous if a sound sensor (microphone function) is applied in the immediate vicinity of the eardrum (DE-C-196 38 158 and US-A-5 999 632).
  • the electromechanical transducer used here preferably works according to the Principle of dynamic volume change due to dynamic surface enlargement or reduction according to the electrical, controlling Converter AC signal.
  • An optimal effect of the transducer of the present invention can be achieved as expected, if by constructive measures It is ensured that the entire surface of the intracochlear transducer is as possible vibrates (ideally ball oscillator) because this results in a maximum volume shift and therefore the highest possible stimulation level for a given electrical drive power of the Converter is achieved by the preprocessing electronics system.
  • the operative access for the intracochlear transducer is preferably through the oval or an artificial cochlear window, for example a promontorial window.
  • the intracochlear transducer is advantageous at the end of a flexible support structure, in particular a polymer support structure.
  • all physical transducer principles can be considered, such as electromagnetic, electrodynamic, piezoelectric, dielectric (capacitive) and magnetostrictive.
  • piezoelectric principle is preferred here, since with a simple transducer design Ideally, the surface vibrator can be most easily met.
  • the intracochlear transducer preferably with the use of geometric Shape transformations, in particular the bimorph principle, the unimorph principle or of the heteromorph principle with passive material partners, so that it is given Transducer voltage a maximum volume change with minimal electrical Power consumption generated.
  • the intracochlear transducer is particularly easy to manufacture and can be easily implanted, if it has a piezoelectric tube section with a cylindrical cross section, whose inner and outer peripheral surface with a surface metallization Formation of electrical transducer electrodes is provided.
  • the intracochlear piezoelectric transducer can be based on lead zirconate titanate (PZT). Single-layer or multi-layer windings thinner are also particularly suitable Polyvinylidene fluoride film (PVDF).
  • the transducer element is expedient with a biocompatible one Sheathing preferably made of an elastic polymer, for example silicone. The entire transducer element can be surrounded by the biocompatible casing his.
  • the casing has at least one opening - and preferably at least two openings at the lower end of the pipe as well as in the upper area of the casing - for the entry and exit of intracochlear Lymph on.
  • the tube surface of the intracochlear transducer and the cross-sectional area of the inlet and outlet openings can be designed so that a hydraulic Transformation is achieved, which leads to higher rapids of the lymph and thus to higher ones Stimulation levels of the cochlea result from direct surface change through the Converter itself.
  • the converter is preferably designed to be highly tuned, that is, the first mechanical resonance frequency lies at the upper spectral end of the Transmission range. This means that the frequency response when voltage is applied to one Example of a piezoelectric transducer and thus largely free of linear distortions.
  • the intracochlear transducer can expediently have a transmission range of approximately 100 Hz to about 10 kHz.
  • a mechanical damping element can be provided be the vibrations of the intracochlear transducer from a transducer lead decoupled, so as to cause at least partial resonance of the middle ear crossbones to prevent or mechanical contact with this transducer lead largely reduce. Such a resonance could otherwise occur Using sensors close to the eardrum (microphones) can lead to disturbing feedback.
  • the material of the damping element has a similar cross-sectional geometry to that of the Carrier preferably chosen so that a large one to achieve high damping values there is a mechanical impedance difference to the carrier material.
  • the intracochlear transducer can expediently be designed for volume changes of approximately 2 ⁇ 10 -4 microliters.
  • the overall diameter of the intracochlear transducer arrangement can advantageously be in the range from 0.2 mm to 2.0 mm, and the immersion depth of the intracochlear transducer and the length of its active transducer element can preferably be between 0.3 and 2 mm.
  • a digital signal processor provided that performs the audio signal processing and processing and / or generated digital signals for tinnitus masking.
  • the signal processor can be designed statically in such a way that corresponding software modules based on scientific knowledge, once in a program memory of the signal processor are stored and remain unchanged. But then lie later for example, improved algorithms based on recent scientific knowledge for speech signal processing and processing and if these are to be used, must the entire implant or the implant module through an invasive, operative patient intervention, that contains the corresponding signal processing unit against a new one with the changed operating software. This intervention harbors new medical Risks for the patient and involves a lot of effort.
  • one, preferably PC-based, telemetry device for transmitting data between an implanted Part of the system and an external unit, especially an external programming system, is provided, and that the signal processor for recording and playback an operating program, a repeatable, implantable memory arrangement is assigned, with at least parts of the operating program by the external Unit changed or exchanged data transmitted via the telemetry device can be.
  • the operating software including software for controlling the intracochlear Converter, as such change or even completely replace this makes it possible further scientific knowledge, for example regarding speech signal processing strategies to implement in the implant without the implant having to be operated Intervention must be replaced.
  • the design is preferably such that, in addition, fully implantable Systems also in a manner known per se, that is to say patient-specific Data, such as audiological adaptation data, or changeable implant system parameters (For example as a variable in a software program to control the intracochlear transducer or to regulate battery recharge) after the implantation transcutaneously, i.e. wirelessly through the closed skin, transferred into the implant and can be changed with it.
  • patient-specific Data such as audiological adaptation data, or changeable implant system parameters (For example as a variable in a software program to control the intracochlear transducer or to regulate battery recharge) after the implantation transcutaneously, i.e. wirelessly through the closed skin, transferred into the implant and can be changed with it.
  • the software modules are preferably dynamic, or in other words capable of learning, designed to achieve the best possible rehabilitation of the particular hearing disorder.
  • the software modules be designed adaptively, and a parameter adjustment can be made by "training" by the Implant carriers and other aids are made.
  • the signal processing electronics can contain a software module that a optimal stimulation achieved based on an adaptive neural network.
  • This neural network can be trained by the implant carrier and / or with the help of other external aids.
  • the memory arrangement for storing operating parameters and the memory arrangement for recording and playback of the operating program can be independent of each other Memory implemented; however, it can also be a single memory act in which both operating parameters and operating programs are stored can.
  • the present solution allows the system to be adapted to conditions that are not yet are detectable after implantation of the implantable system.
  • the sensory (sound sensor or microphone) and actuator (intracochlear transducer) biological interfaces always dependent on the anatomical, biological and neurophysiological conditions, for example of the interindividual healing process.
  • These interface parameters can be customized in particular also be time variant.
  • the transmission behavior of a implanted microphones due to tissue layers and the transmission behavior of the intracochlear electromechanical transducer coupled to the inner ear vary the coupling quality individually and individually.
  • Such Differences in the interface parameters that are known from those known from the prior art Do not diminish devices even by replacing the implant or can be eliminated in the present case by change or Improvement of the signal processing of the implant can be optimized.
  • an intermediate storage arrangement in which of the data transmitted to the external unit via the telemetry device before being forwarded to the signal processor can be cached.
  • the Complete the transfer process from the external device to the implanted system, before the data transmitted via the telemetry device is forwarded to the signal processor become.
  • a check logic can be provided in the buffer arrangement stored data before being passed to the signal processor of a review subjects.
  • a microprocessor module in particular a microcontroller, be provided for controlling the signal processor within the implant via a data bus, expediently the checking logic and the buffer arrangement in the Microprocessor module are implemented and with the data bus and the telemetry device also program parts or entire software modules between the outside world, the microprocessor module and the signal processor can be transmitted.
  • the microprocessor module is preferably an implantable memory arrangement for Save a work program for the microprocessor module assigned, and at least Parts of the work program for the microprocessor module can be carried out by the External unit changed or exchanged data transmitted via the telemetry device become.
  • At least two memory areas can be used Recording and playback of at least the operating program of the signal processor is provided his. This contributes to the reliability of the system by the multiple Presence of the memory area which contains the operating program or programs contains, for example after a transfer from external or when switching on the The software can be checked for errors.
  • the buffer arrangement can also have at least two memory areas for recording and playback from the external unit via the telemetry device have transmitted data, so that after data transmission from the external Unit still in the area of the buffer a check of correctness of the transmitted data can be made.
  • the memory areas can, for example complementary storage of the data transmitted by the external unit his.
  • At least one of the storage areas of the intermediate storage arrangement can but also for recording only part of the data transmitted by the external unit be designed, in which case the verification of the correctness of the transmitted Data in sections.
  • the signal processor can also be a preprogrammed, not rewritable permanent storage area can be assigned in which the for a "minimal operation" instructions and parameters required by the system are stored, for example Instructions that are at least error-free after a "system crash" Operation of the telemetry device for receiving an operating program and instructions to store the same in the control logic.
  • the telemetry device is advantageously except for reception of operating programs from the external unit also for the transmission of operating parameters between the implantable part of the system and the external unit designed so that on the one hand such parameters from a doctor, a hearing care professional or can be adjusted to the wearer of the system itself (for example volume), on the other hand, the system can also transmit parameters to the external unit, for example to check the status of the system.
  • a fully implantable hearing system of the type explained here can be on the implant side in addition to the intracochlear converter and the signal processing unit at least have an implantable sound sensor and a rechargeable electrical storage element, in such a case, preferably a wireless, transcutaneous charging device is provided for loading the memory element.
  • a primary cell or another energy supply unit is also available can be that does not require transcutaneous reloading. This is especially true if you take into account that in the near future mainly through further development of processor technology with a substantial reduction in the energy requirement for electronic signal processing is to be expected, so that new forms of energy supply for implantable hearing systems become practically applicable, for example an energy supply using the Seebeck effect, as described in DE-C 198 27 898.
  • a wireless is also preferred Remote control for controlling the implant functions by the implant carrier is available.
  • At least one sound sensor is the electronic signal processing unit, the power supply unit and a modulator / transmitter unit in an external on the body, preferably on the head above the implant, external module to be carried.
  • the implant has the electromechanical, intracochlear converter, but is energetically passive and receives its operating energy and control data for the intracochlear converter via the modulator / transmitter unit in the external module.
  • a binaural system for Rehabilitation of a hearing disorder of both ears has two system units, each are assigned to one of the two ears.
  • the two system units can each other be essentially the same. But it can also be a system unit as a master unit and the other system unit is designed as a slave unit controlled by the master unit his.
  • the signal processing modules of the two system units can be set to any Way, in particular via a wired implantable line connection or via a wireless connection, preferably a bidirectional radio frequency link, a structure-borne ultrasound system or electrical conductivity of the tissue of the implant carrier utilizing data transmission path, so with each other communicate that optimized binaural signal processing in both system units and converter array control is achieved.
  • FIG. 1 schematically shows a section through part of the human middle ear the long anvil process 10, the stirrup with the footplate shown perforated here 11, the stirrup superstructure (leg 12 and small head 13) and the ligament 14, with which the stirrup is hung in the oval window of the bony cochlear wall 15 is.
  • the line 20 can be made with a deformable and preferably metallic one known from stapes prosthetics Hook or a loop 25 are fixed to the long anvil extension 10. in principle are the implant feed line 20 and the attachment of the transducer 18, 18 'to the distal one End of this line constructed as in the case of an intracochlear cochlear implant electrode. That is, at the distal end of the implant lead 20 there is a mechanical support 26 attached to the converter 18, 18 '.
  • This carrier preferably consists essentially of a flexible polymer (preferably silicone) molded part of preferably circular Cross-section.
  • a mechanical damping element 28 can be provided, which the vibrations of the converter 18, 18 'decoupled from the feed line 20 and thus a transmission of the Avoid or at least reduce transducer vibrations on the middle ear Use a local sound sensor (microphone) of the implantable hearing system could lead to unwanted feedback.
  • the electromechanical converter 18, 18 preferably works on the principle of dynamic volume change due to a dynamic surface enlargement or reduction in accordance with the electrical, driving converter alternating voltage signal.
  • the overall diameter of the transducer arrangement is in the range from 0.2 mm to 2.0 mm.
  • the immersion depth of the transducer is in the range of 0.3 to 2 mm, the length of the active transducer element in the same range.
  • FIG. 2 schematically shows the basic structure of the converter 18 when using a Piezoelectric tube section 30 with a cylindrical cross section, preferably made of Lead zirconate titanate (PZT). It is on the inner and outer peripheral surface of the Pipe section 30 applied a surface metallization, which electrical transducer electrodes 31 and 32 forms.
  • the converter can preferably also be a single or multilayer wrap of thin polyvinylidene fluoride film (PVDF).
  • the material the surface metallization consists of biocompatible metal, preferably pure Gold, platinum, platinum-iridium, titanium, tantalum, stainless steels and their biocompatible alloys.
  • the electrical connections of the converter electrodes 31 and 32 are made via the two transformer leads 21. The same selection applies to the material of the leads as for the metallization of the transducer.
  • the entire Transducer element 30, 31, 32 in this embodiment is preferably biocompatible thin sheath 33 surrounded.
  • the casing 33 preferably consists of an elastic polymer such as silicone, which can be used as a carrier material for cochlear implant electrodes has proven to be excellent.
  • FIGN. 3 and 4 schematically show a modified embodiment of the converter according to FIG. 2.
  • transducer 18 ' is not completely clear of the polymer jacket 33 surrounded. Rather, at the open lower end 35 of the pipe section 30 and one connected to the interior 36 of the pipe section 30 Transverse opening 37 in the upper region of the casing 33 for the entry and exit of intracochlear Lymph in or out of the tube interior 36 possible, as in FIG. 3 is indicated by arrows 39 and 40. Due to the dynamic change in radius of the Transducers 18 'therefore become a lymphatic shift and thus an intracochlear one Volume shift reached.
  • FIG. 5 shows the possible structure of a signal-processing electronic module 41 of the at least partially implantable hearing system according to the present invention.
  • One or more microphones 42 record the sound signal and convert it into corresponding electrical signals.
  • These sensor signals are each selected in a unit 43, preprocessed and converted from analog to digital (A / D).
  • the preprocessing can consist, for example, of an analog linear or non-linear pre-amplification and filtering (for example antialiasing filtering).
  • the digitized sensor signal or signals are fed to a digital signal processor (DSP) 44, which performs the intended function of the hearing implant, such as audio signal processing in a system for inner ear deafness and / or signal generation in the case of a tinnitus masker or noiser.
  • DSP digital signal processor
  • the signal processor 44 contains a non-rewritable permanent memory area S 0 , in which the instructions and parameters required for "minimal operation" of the system are stored, and a memory area S 1 , in which the operating software for the intended function or functions of the implant system are stored.
  • This memory area is preferably duplicated (S 1 and S 2 ).
  • the program memory which can be written repeatedly, for accommodating the operating software can be based on EEPROM or RAM cells, in which case it should be ensured that this RAM area is always “buffered” by the energy supply system.
  • the digital output signals of the signal processor 44 are in a digital-to-analog converter (D / A) - and driver unit 45 converted into analog signals and to the for control of the converter 18, 18 'brought the desired level.
  • This unit 45 can under Circumstances are completely eliminated, for example when using an electromagnetic intracochlear output transducer, for example a pulse width modulated, serial digital Output signal of the signal processor 44 transmitted directly to the output converter becomes.
  • the signal processing components 43, 44 and 45 are controlled by a microcontroller 47 (.mu.C) with one or two associated memories S 4 and S 5 via a bidirectional data bus 48.
  • the operating software components of the implant management system for example administrative monitoring and telemetry functions, can be stored in the memory areas S 4 and S 5 .
  • the memory S 1 and / or S 2 can also be used to store externally changeable, patient-specific, for example audiological, adaptation parameters.
  • the microcontroller 47 has a memory S 3 that can be written to repeatedly, in which a work program for the microcontroller 47 is stored.
  • the microcontroller 47 communicates with a telemetry system (TS) 50 via a data bus 49.
  • This telemetry system 50 in turn communicates wirelessly bidirectionally with an external programming system (PS) 52 through the closed skin indicated at 51, for example via an inductive coil coupling (not shown)
  • PS external programming system
  • the programming system 52 can advantageously be a PC-based system with corresponding programming, processing, presentation and management software.
  • the operating software of the implant system that is to be changed or completely exchanged is transmitted via this telemetry interface and initially stored temporarily in the memory area S 4 and / or S 5 of the microcontroller 47.
  • the memory area S 5 can be used for a complementary storage of the data transmitted by the external system, and a simple verification of the software transmission by a read operation via the telemetry interface can be carried out to determine the coincidence of the contents of the memory areas S 4 and S 5 to check before the content of the rewritable memory S 3 is changed or exchanged.
  • the operating software of the at least partially implantable hearing system should include both the operating software of the microcontroller 47 (for example housekeeping functions, such as energy management or telemetry functions) and the operating software of the digital signal processor 44.
  • the operating software of the microcontroller 47 for example housekeeping functions, such as energy management or telemetry functions
  • the operating software of the digital signal processor 44 For example, a simple verification of the software transmission can be carried out by means of a reading process via the telemetry interface before the operating software or the corresponding signal processing components of this software are transmitted to the program memory area S 1 of the digital signal processor 44 via the data bus 48.
  • the work program for the microcontroller 47 which is stored, for example, in the repeatedly writable memory S 3 , can be changed or exchanged in whole or in part using the external unit 52 via the telemetry interface 50.
  • All electronic components of the implant system are made by a primary or secondary battery 30 supplied with electrical operating energy.
  • FIG. 6 schematically shows the structure of a fully implantable hearing system an intracochlear transducer 18 or 18 'according to FIGN. 1 to 4 and an implantable Microphone 42.
  • a wireless remote control 54 is used to control the implant functions through the implant carrier.
  • the microphone 42 can advantageously be constructed in the manner known from US Pat. No. 5,814,095 and with a microphone capsule, which is hermetically sealed on all sides in a housing is, as well as with an electrical bushing arrangement for bushing at least an electrical connection from the interior of the housing to the outside be provided, the housing having at least two legs, which in one Angles are aligned with respect to each other, one leg of the microphone capsule picks up and is provided with a sound entry membrane, the other leg contains the electrical bushing arrangement and opposite the plane of the sound entry membrane is set back, and the geometry of the microphone housing is chosen in this way is that when the microphone is implanted in the mastoid cavity of the sound entry membrane containing legs from the mastoid into an artificial hole in the back, protrudes into the bony ear canal wall and the sound entry membrane covers the skin of the ear canal wall touched.
  • a fixation element can expediently be used to fix the microphone 40 of the type known from US-A-5 999 632, which has a cuff, the one with a cylindrical housing part containing the sound inlet membrane Thighs encloses and with against the side of the ear canal wall facing the ear canal skin projectable, projecting, elastic flange parts is provided.
  • the fixation element is preferably a holder, which said flange parts before the implantation against an elastic restoring force of the flange parts in a Push through the bend in the bent position of the ear canal wall holds.
  • the charging system also includes one connected to the output of the charger 55 Charging coil 56, which is preferably part of a transmission series resonant circuit, as is known from US-A-5 279 292 forms that with an unillustrated receive series resonant circuit can be coupled inductively.
  • the reception series resonance circuit can with the Embodiment according to FIG. 6 be part of the electronics module 41 and accordingly US-A-5 279 292 form a constant current source for battery 53 (FIG. 5).
  • the receiving series resonance circuit in a battery charging circuit, which is dependent from the respective phase of the charging current flowing in the charging circuit via one or the other branch of a full-wave rectifier bridge is closed.
  • the electronics module 41 is in the arrangement according to FIG. 6 via a microphone line 58 the microphone 42 and via the implant lead 20 to the intracochlear transducer 18 or 18 'connected.
  • FIG. 7 schematically shows the structure of a partially implantable hearing system with an intracochlear Transducers 18 and 18 'according to FIGN. 1 to 4.
  • this semi-implantable System are a microphone 42, an electronic module 62 for an electronic Signal processing largely according to FIG. 5 (but without the telemetry system 50), the energy supply 53 and a modulator / transmitter unit 63 in an external device on the body, external module 64 to be worn, preferably on the head above the implant.
  • the implant is energetically passive.
  • His electronics module 65 (without battery 53) receives its operating energy and converter control data the modulator / transmitter unit 63 in the external part 64.
  • Both the fully implantable and the partially implantable hearing system can be monoaural or be designed binaural.
  • a binaural hearing aid rehabilitation system Both ears have two system units, each assigned to one of the two ears are.
  • the two system units can be essentially the same. It can also be a system unit as a master unit and the other system unit as slave unit controlled by the master unit.
  • the signal processing modules of the two system units can in any way, in particular via one wired implantable line connection or via a wireless connection, preferably a bidirectional radio-frequency link, a structure-borne ultrasound link or one that takes advantage of the electrical conductivity of the tissue of the implant carrier Data transmission link, so communicate with each other in both system units optimized binaural signal processing is achieved.

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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)
  • Electrotherapy Devices (AREA)
  • Rehabilitation Tools (AREA)
EP01118050A 2000-09-21 2001-07-25 Système auditif au moins partiellement implantable avec stimulation mécanique d'un espace lymphatique de l'oreille interne Expired - Lifetime EP1191815B1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE10046938A DE10046938A1 (de) 2000-09-21 2000-09-21 Mindestens teilimplantierbares Hörsystem mit direkter mechanischer Stimulation eines lymphatischen Raums des Innenohres
DE10046938 2000-09-21

Publications (3)

Publication Number Publication Date
EP1191815A2 true EP1191815A2 (fr) 2002-03-27
EP1191815A3 EP1191815A3 (fr) 2009-10-21
EP1191815B1 EP1191815B1 (fr) 2011-04-20

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Country Status (5)

Country Link
US (1) US6629923B2 (fr)
EP (1) EP1191815B1 (fr)
AT (1) ATE506814T1 (fr)
DE (2) DE10046938A1 (fr)
DK (1) DK1191815T3 (fr)

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Also Published As

Publication number Publication date
DK1191815T3 (da) 2011-07-18
EP1191815B1 (fr) 2011-04-20
DE50115855D1 (de) 2011-06-01
EP1191815A3 (fr) 2009-10-21
DE10046938A1 (de) 2002-04-25
US20020035309A1 (en) 2002-03-21
US6629923B2 (en) 2003-10-07
ATE506814T1 (de) 2011-05-15

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