EP1191815B1 - At least partially implantable hearing system with direct mechanical stimulation of a lymphatic space of the internal ear - Google Patents
At least partially implantable hearing system with direct mechanical stimulation of a lymphatic space of the internal ear Download PDFInfo
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- EP1191815B1 EP1191815B1 EP01118050A EP01118050A EP1191815B1 EP 1191815 B1 EP1191815 B1 EP 1191815B1 EP 01118050 A EP01118050 A EP 01118050A EP 01118050 A EP01118050 A EP 01118050A EP 1191815 B1 EP1191815 B1 EP 1191815B1
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- Prior art keywords
- transducer
- hearing system
- intracochlear
- hearing
- signal processing
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Images
Classifications
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- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
- H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
- H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
- H04R25/604—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers
- H04R25/606—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers acting directly on the eardrum, the ossicles or the skull, e.g. mastoid, tooth, maxillary or mandibular bone, or mechanically stimulating the cochlea, e.g. at the oval window
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- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
- 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 the rehabilitation of a hearing impairment with at least one sound-absorbing sensor (microphone), an electronic arrangement for audio signal processing and amplification, an electrical power supply unit which supplies individual components of the system with power, and an output-side actuator array for direct mechanical stimulation of a lymphatic space of the inner ear.
- a sound-absorbing sensor microphone
- an electrical power supply unit which supplies individual components of the system with power
- an output-side actuator array for direct mechanical stimulation of a lymphatic space of the inner ear.
- hearing impairment should be understood to mean all types of inner ear damage, combined inner and middle ear damage as well as occasional or permanent ear noises (tinnitus).
- the electronic system essentially contains only decoder and driver circuits for the stimulating electrodes;
- the acoustic sound recording, the conversion of this sound signal into electrical signals and their further processing is basically external in a so-called speech processor, which is worn on the outside of the body.
- the speech processor converts the preprocessed signals corresponding encoded to a high-frequency carrier signal, which is transmitted to the implant via an inductive coupling through the closed skin (transcutaneously).
- the sound-absorbing microphone is invariably outside the body and, in most applications, in a back-of-the-ear (BTE) case worn on the pinna and is equipped with a cable connected to the speech processor.
- BTE back-of-the-ear
- Such cochlear implant systems their components and principles of transcutaneous signal transmission are exemplary in US-A-5 070 535 .
- Methods for speech processing and coding in cochlear implants are, for example, in US Pat. No. 5,597,380 .
- the principle in the predominant embodiments is to stimulate an ossicle of the middle ear or the inner ear directly via a mechanical or hydromechanical stimulus and not via the amplified acoustic signal of a conventional hearing aid, in which the amplified sound signal is supplied to the external auditory canal.
- the actuatoric stimulus of these electromechanical systems is realized with various physical transducer principles, such as electromagnetic and piezoelectric systems.
- nonlinear distortions which are particularly pronounced in electromagnetic transducers, can occur are to negatively impact the resulting sound quality.
- pronounced high-frequency losses are difficult to supply with electromagnetic transducers.
- tinnitus maskers are available; These are small, battery-powered devices that are similar to a hearing aid worn behind or in the ear and by artificial sounds that are emitted via a hearing aid speaker, for example, in the ear canal, the tinnitus in a psychoacoustic manner hide (“mask”) and the disturbing noise of the ear as low as possible below the threshold of perception.
- the artificial sounds are often narrow-band noise (for example, third-octaves), which can be adjusted in their spectral position and volume levels via a programmer to allow the best possible adaptation to the individual ear noise situation.
- narrow-band noise for example, third-octaves
- retraining method whereby by the combination of a mental training program and the presentation of a broadband sound (noise) near the rest hearing threshold, the perceptibility of tinnitus should also be largely suppressed ( H. Knör, "Tinnitus Retraining Therapy and Hearing Acoustics” Journal “Hörakustik” 2/97, pages 26 and 27 ).
- These devices are also called “Noiser”.
- an implantable tinnitus masker with "direct drive” of the middle ear is described, for example, via an electromechanical transducer coupled to the ossicular chain.
- This directly coupled converter may preferably be a so-called “Floating Mass Transducer” (FMT).
- FMT floating Mass Transducer
- the above-described, at least partially implantable hearing aid rehabilitation based on an output-side electromechanical transducer differ essentially from conventional conventional hearing aids essentially only in that the output side acoustic stimulus (an amplified sound signal in front of the eardrum) by an enhanced mechanical Stimulus of the middle or inner ear is replaced.
- the acoustic stimulus of a conventional hearing aid finally leads via the mechanical stimulation of the eardrum and the subsequent middle ear to a vibratory, that is mechanical stimulus of the inner ear.
- a locally localized vibratory stimulus is directed to the damaged inner ear on the output side (for example, reinforced mechanical vibration of the stirrup in the oval window of the inner ear).
- otosclerosis in particular, the mobility of the ligament of the stirrup suspension in the oval window is limited or completely prevented by calcification, is used by the surgical method of stapedectomy (English Stapedotomy) a passive prosthesis, on the one hand by a Bracket is usually fixed on the long incus process and on the other hand with its mostly circular shaft in an artificially introduced opening in the stirrup foot plate is used.
- stapedectomy English Stapedotomy
- Bracket is usually fixed on the long incus process and on the other hand with its mostly circular shaft in an artificially introduced opening in the stirrup foot plate is used.
- the stirrup can also be completely removed.
- the vibrations of the eardrum are transmitted via the hammer on the anvil and thus cause corresponding vibrations of the passive prosthesis, which lead to dynamic volume shifts in the perilymph of the inner ear, thereby triggering traveling waves on the basilar membrane and ultimately to a listening experience.
- This method has been used for decades as a reconstructive Mittelohroperation very safe and successful.
- the introduction of the opening in the stirrup footplate is achieved by fine surgical instruments or, in particular, by laser techniques.
- the older one EP patent application 00 119 195.6 describes a hearing system having a plurality of electromechanical transducers distributed along the cochlea to excite the fluid-filled inner ear spaces by forming a traveling wave configuration on the basilar membrane.
- the older one EP patent application 01 109 191.5 discloses a hearing system with a dual intracochlear assembly having in combination a stimulator assembly with at least one stimulator element for at least indirect mechanical stimulation of the inner ear and an electrically acting stimulation electrode assembly with at least one cochlear implant electrode for electrical stimulation of the inner ear.
- a hearing system microactuator is described with a hollow body implantable in the middle ear, which is filled with an incompressible liquid and in the at least one connected to a relatively large-area membrane piezoelectric transducer is housed.
- the interior of the hollow body is in communication with a nozzle which is inserted into an artificial fenestration of Promontoriums and which is closed at its end remote from the hollow body of a small compared to the transducer membrane.
- the transducer when applied with appropriate electrical signals, exerts force on the fluid in the hollow body, thereby deflecting the small nozzle end diaphragm of the microactuator in fluid contact with the inner tube.
- a system of the aforementioned type in which a microactuator with a flat flexible membrane is provided as the output-side actuator arrangement.
- the Mikroaktuatormembran forms the end face of a screw which is screwed into an artificial fenestration in Promontorium, or the microactuator is inserted directly into such a fenestration such that its planar membrane in the inner tube located fluid contacts.
- the microactuator sits in the stem of a passive stapedectomy prosthesis of the type discussed above to provide for combined passive and active stimulation.
- a generic system is from the DE 42 21 866 A1 known, which relates to a fully implantable hearing aid with trained as liquid sonic Ausgantswandler, which dips into the perilymph and stored in a borehole Stapesfussplatte, wherein the liquid sound transmitter as bending transducer from bimorph Piezokeramik or PVDF film or after the electrodynamic principle working with permanent magnet and a magnet surrounding the magnet may be formed.
- the invention has for its object to provide an at least partially implantable system for the rehabilitation of hearing impairment, which is able to provide for improved rehabilitation of sensory hearing disorders.
- the output-side actuator array consists of an intracochlear electromechanical transducer.
- an intracochlear transducer structure according to the invention are, on the one hand, in particular that the mechanical stimulus can be generated over a relatively large area directly in the inner ear and no additional masses, stiffnesses of the suspension and / or lossy joints of the middle ossicles lie in the mechanical transmission path, in particular to linear distortions of the can lead to transmitted frequency response of the converter.
- the interindividual reproducibility of the mechanical stimulation is significantly better by direct inner ear stimulation than in the case of transmission by coupling elements to the middle ear particles, because thereby always anatomical fluctuations and in particular the personal approach of the surgeon play an important role.
- Another advantage of the present invention is that the occurrence of feedback (coupling of the output signal into the sensor / microphone) is expectedly largely reduced by a direct, electromechanical stimulation of the cochlea, because the ossicular chain and thus the eardrum is not or significantly reduced to vibrations is stimulated. This is particularly advantageous when 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 presently used electromechanical transducer operates on the principle of dynamic volume change due to a dynamic surface enlargement or reduction in accordance with the electrical, driving converter AC voltage signal.
- An optimal effect of the transducer of the present invention can be expected to be achieved if it is ensured by constructive measures that as possible the entire surface of the intracochlear transducer oscillates (ideal ball vibrator), because thereby a maximum volume shift and thus the highest possible stimulation level for a given electrical Drive power of the converter is achieved by the preprocessing electronic 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 advantageously arranged at the end of a flexible support structure, in particular a polymer support structure.
- the intracochlear transducer preferably with the use of geometric Shape transformations, in particular the bimorph principle, the unimorph principle or the heteromorphic principle with passive material partners, be designed so that it generates a maximum volume change with a minimum electrical power consumption for a given transducer voltage.
- the intracochlear transducer is particularly easy to manufacture and easy to implant if it has a piezoelectric tube section of cylindrical cross-section, the inner and outer circumferential surfaces of which are provided with a surface metallization to form electrical conversion electrodes.
- the intracochlear piezoelectric transducer can be constructed on the basis of lead zirconate titanate (PZT). But is also particularly suitable single or multilayer winding thin polyvinylidene fluoride film (PVDF).
- the transducer element is provided with a biocompatible sheath, preferably made of an elastic polymer, for example silicone. In this case, the entire transducer element can be surrounded by the biocompatible sheathing.
- the sheath has at least one opening - and preferably at least two openings at the lower end of the tube and in the upper region of the sheath - for the entry and exit of intracochlear lymph.
- the tube surface of the intracochlear transducer and the cross-sectional area of the inlet and outlet openings can be designed to achieve a hydraulic transformation that results in higher lymph velocity and thus higher cochlear stimulation levels than by direct surface modification by the transducer itself.
- the converter is designed to be highly tuned, that is, the first mechanical resonance frequency is at the upper spectral end of the transmission range.
- the frequency response is at voltage impressed on a piezoelectric transducer, for example, and thus largely free of linear distortions.
- the intracochlear transducer may suitably have a transmission range of about 100 Hz to about 10 kHz.
- a mechanical damping element can be provided which decouples the vibrations of the intracochlear transducer from a transducer lead, so as to prevent or substantially reduce at least partial resonant oscillation of the middle ossicles due to mechanical contact with this transducer lead. Such a swinging could otherwise lead to disturbing feedback when using eardrum close sensors (microphones).
- the material of the damping element is preferably selected with a similar cross-sectional geometry as that of the carrier, that in order to achieve high attenuation values there is a large mechanical impedance difference to the carrier material.
- the intracochlear transducer may suitably be designed for volume changes of about 2 x 10 -4 microliters.
- the total diameter of the intracochlear transducer array may advantageously be in the range of 0.2 mm to 2.0 mm, and the depth of immersion of the intracochlear transducer and the length of its active transducer element may preferably be between 0.3 and 2 mm.
- a digital signal processor which performs the audio signal processing and conditioning and / or generates digital signals for tinnitus masking.
- the signal processor can be designed statically in such a way that corresponding software modules are stored once on the basis of scientific findings in a program memory of the signal processor and remain unchanged. But later, for example, based on recent scientific findings improved algorithms for speech signal processing and processing before and should they be used by an invasive, surgical patient intervention, the entire implant or implant module containing the corresponding signal processing unit, against a new with the changed Operating software to be replaced. This procedure brings new medical risks for the patient and is associated with high costs.
- a preferably PC-based, telemetry device for transmitting data between an implanted part of the system and an external unit, in particular an external programming system
- the signal processor for recording and reproducing an operating program associated with a rewritable implantable memory device, wherein at least portions of the operating program may be changed or replaced by data communicated from the external device via the telemetry device.
- the operating software including software for controlling the intracochlear transducer, as such change or completely exchange.
- the design is preferably such that, in addition, in fully implantable systems, operating parameters, that is, patient-specific, are also known per se Data, such as fitting audiological data, or changeable implant system parameters (for example as a variable in a software program for driving the intracochlear transducer or for regulating a battery recharge) after implantation can be transcutaneously, ie wirelessly transmitted through the closed skin, into the implant and thereby changed can.
- the software modules are preferably dynamic, or in other words adaptive, designed to come to the best possible rehabilitation of the respective hearing impairment.
- the software modules may be designed to be adaptive, and parameter adjustment may be done by "training" by the implant carrier and other aids.
- the signal processing electronics may include a software module that achieves the best possible stimulation on the basis of a learning neural network.
- the training of this neural network can be done by the implant wearer and / or with the help of other external aids.
- the memory arrangement for storing operating parameters and the memory arrangement for recording and reproducing the operating program can be implemented as independent memories; However, it can also be a single memory in which both operating parameters and operating programs can be stored.
- the present solution allows an adaptation of the system to conditions that are detectable only after implantation of the implantable system.
- the sensory (sound sensor or microphone) and actoric (intracochlear transducer) biological interfaces are always dependent on the anatomical, biological and neurophysiological conditions, for example, of the interindividual healing process.
- These interface parameters can be individual and also time-variant, in particular.
- the transmission behavior of an implanted microphone due to tissue layers and the transmission behavior of the coupled to the inner ear intracochlear electromechanical transducer due to different coupling quality vary individually and individually.
- Such differences in the interface parameters which can not even be reduced or eliminated in the devices known from the prior art by exchanging the implant, can be optimized here by changing or improving the signal processing of the implant.
- a buffer memory arrangement is further provided, in which data transmitted by the external unit via the telemetry device can be buffered before forwarding to the signal processor.
- data transmitted by the external unit via the telemetry device can be buffered before forwarding to the signal processor.
- the transmission process from the external unit to the implanted system can be completed before the data transmitted via the telemetry device are forwarded to the signal processor.
- a check logic may be provided which subjects the data stored in the latch arrangement to a check prior to routing to the signal processor.
- It may be a microprocessor module, in particular a microcontroller, provided for implant-internal control of the signal processor via a data bus, expediently the verification logic and the buffer arrangement are implemented in the microprocessor module and wherein via the data bus and the telemetry and program parts or entire software modules between the outside world, the Microprocessor module and the signal processor can be transmitted.
- the microprocessor chip is preferably associated with an implantable memory device for storing a work program for the microprocessor chip, and at least parts of the work program for the microprocessor chip may be changed or replaced by data transmitted from the external device via the telemetry device.
- At least two memory areas may be provided for recording and reproducing at least the operating program of the signal processor. This contributes to the error safety of the system, in that by the multiple presence of the memory area which contains the operating program (s), for example after a transmission from external or when the implant is switched on, a check can be carried out for the correctness of the software.
- the buffer memory 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 a data transmission from the external unit or in the area of the cache memory, a check of the accuracy of the transmitted data can be made.
- the memory areas can be designed for, for example, complementary storage of the data transmitted by the external unit.
- at least one of the memory areas of the buffer arrangement can also be designed to accommodate only a part of the data transmitted by the external unit, in which case the checking of freedom from error of the transmitted data takes place in sections.
- the signal processor may also be associated with a preprogrammed non-rewritable memory area in which the instructions and parameters required for a "minimum operation" of the system are stored, for example instructions following a "Crash" at least ensure error-free operation of the telemetry device for receiving an operating program and instructions for storing the same in the control logic.
- the telemetry device is also advantageously designed for the transmission of operating parameters between the implantable part of the system and the external unit, such that on the one hand such parameters are provided by a physician, a hearing healthcare professional or the wearer
- 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 described here can have at least one implantable sound sensor and a rechargeable electrical storage element next to the intracochlear transducer and the signal processing unit, in which case a wireless, transcutaneous charging device for charging the storage element is preferably provided.
- a primary cell or another power supply unit may be present, which does not require transcutaneous recharge.
- a wireless is also Remote control for controlling the implant functions by the implant carrier available.
- the implant has the output side electromechanical intracochlear transducer, but is energetically passive and receives its operating and control data for the intracochlear transducer via the modulator / transmitter unit in the external module.
- a binaural system for rehabilitation of hearing impairment in both ears has two system units, each associated with one of the two ears.
- the two system units can be substantially equal to each other.
- one system unit may also be designed as the master unit and the other system unit as a slave unit controlled by the master unit.
- the signal processing modules of the two system units can communicate with each other in any way, in particular via a wired implantable line connection or via a wireless connection, preferably a bidirectional high-frequency link, a structure-borne sound-coupled ultrasound link or a data transmission path utilizing the electrical conductivity of the tissue of the implant carrier, such that in both system units an optimized binaural signal processing and transducer array drive is achieved.
- FIG. 1 schematically shows a section through a portion of the human middle ear with the long anvil process 10, the stirrup with the here perforated base plate 11, the Stirrup superstructure (leg 12 and head 13) and the ligament 14, with the stirrup in the oval window of the bony cochletic Wall 15 is suspended.
- an intracochlear electromechanical transducer 18, 18 ' is introduced into the inner ear as a whole.
- the transducer 18, 18 ' is connected to an implant lead 20, the inside of the in FIG. 2 shown electrical converter leads 21 leads.
- Surgical sealing of the implant lead 20 in the stapes footplate perforation is expedient, as known from stapes prosthetics, by rearrangement with fascia or other endogenous thin tissue 23.
- the lead 20 may be provided with a deformable and preferably metallic hook or loop known from stapes prosthetics 25 are fixed to the long anvil process 10.
- the implant lead 20 and the mounting of the transducer 18, 18 ' are constructed at the distal end of this lead 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 for the transducer 18, 18 '.
- This support preferably consists essentially of a flexible polymer (preferably silicone) molding of preferably circular cross-section.
- a mechanical damping element 28 can be provided which decouples the vibrations of the transducer 18, 18 'from the feed line 20 and thus avoids or at least reduces transmission of the transducer vibrations to the middle ossicles when using a local sound sensor (microphone) of the implantable hearing system could lead to unwanted feedback.
- the electromechanical transducer 18, 18 operates on the principle of dynamic volume change due to a dynamic surface enlargement or reduction in accordance with the electrical, driving converter AC voltage signal.
- the required volume changes for an adequate, equivalent sound pressure level of about 100 dB SPL result in about 2 ⁇ 10 -4 microliters.
- the overall diameter of the transducer assembly is in the range of 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 area.
- FIG. 2 schematically shows the basic structure of the transducer 18 when using a piezoelectric pipe section 30 with a cylindrical cross section, preferably of lead zirconate titanate (PZT).
- PZT lead zirconate titanate
- a surface metallization is applied on the inner and the outer peripheral surface of the pipe section 30, which forms electrical transformer electrodes 31 and 32.
- the transducer can preferably also be constructed from a single-layer or multi-layer winding of thin polyvinylidene fluoride film (PVDF).
- the surface metallization material consists of biocompatible metal, preferably pure gold, platinum, platinum-iridium, titanium, tantalum, stainless steels and their biocompatible alloys.
- the electrical connections of the transducer electrodes 31 and 32 are made via the two transducer leads 21. The same choice applies to the material of the leads as for the metallization of the transducer.
- the entire transducer element 30, 31, 32 is preferably surrounded in this embodiment with a biocompatible thin sheath 33.
- the sheath 33 is preferably made of an elastic polymer such as silicone, which has proven to be excellent as a carrier material for cochlear implant electrodes.
- FIGS. 3 and 4 schematically show a modified embodiment of the converter according to FIG. 2 ,
- the transducer 18 ' is not completely surrounded by the polymer jacket 33. Rather, at the open lower end 35 of the pipe section 30 and a communicating with the interior 36 of the pipe section 30 transverse opening 37 in the upper region of the sheath 33 of the inlet and outlet of intracochlear lymph in or out of the tube interior 36 is possible, as in FIG. 3 indicated by arrows 39 and 40. Due to the dynamic radius change of the transducer 18 'therefore directly a lymphatic displacement and thus an intracochlear volume shift can be achieved.
- FIG. 5 shows the possible structure of a signal processing electronics module 41 of the at least partially implantable hearing system according to the present invention.
- One or more Microphones 42 pick up the sound signal and convert it into corresponding electrical signals.
- These sensor signals are each selected in a unit 43, preprocessed and converted analog-to-digital (A / D).
- the preprocessing may, for example, consist in an analogue linear or non-linear preamplification and filtering (for example antialiasing filtering).
- the digitized sensor signal (s) are applied 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 hearing loss and / or signal generation in the case of a tinnitus masker or noise.
- DSP digital signal processor
- the signal processor 44 contains a non-rewritable read-only memory area S 0 , in which the instructions and parameters required for a "minimum operation" of the system are stored, and a memory area S 1 , in which the operating software of the intended function or functions of the implant system are stored. Preferably, this memory area is duplicated (S 1 and S 2 ).
- the rewritable program memory for holding the operating software may be based on EEPROM or RAM cells, in which case it should be ensured that this RAM area is always "buffered" by the power supply system.
- the digital output signals of the signal processor 44 are converted into analog signals in a digital-to-analog converter (D / A) and driver unit 45 and brought to the desired level for driving the converter 18, 18 '.
- this unit 45 can be completely dispensed with if, for example, when using an electromagnetic intracochlear output transducer, an example pulse-width-modulated, serial digital output signal of the signal processor 44 is transmitted directly to the output transducer.
- the signal processing components 43, 44 and 45 are controlled by a microcontroller 47 ( ⁇ C) with one or two associated memories S 4 and S 5 via a bidirectional data bus 48.
- the operating software portions of the implant management system may be stored in the memory area S 4 and S 5 , for example, administration monitoring and telemetry functions.
- the memories S 1 and / or S 2 also externally variable, patient-specific, such as audiological fitting parameters can be stored.
- the microcontroller 47 has a repeatedly writable memory S 3 , in which a work program for the microcontroller 47 is stored.
- the microcontroller 47 communicates in the illustrated implantable embodiment via a data bus 49 with a telemetry system (TS) 50.
- 50 communicates wirelessly bidirectionally with an external programming system (PS) 52 via 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 be.
- the operating software of the implant system 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 may be used for complementarily storing the data transmitted from the external system, and a simple verification of the software transmission by a telemetry read operation may be performed to determine the coincidence of the contents of the memory areas S 4 and S 5 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 comprise 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 performed by a read operation via the telemetry interface, before the operating software or the corresponding signal processing components of this software are transferred 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 replaced completely or partially via the telemetry interface 50 with the aid of the external unit 52.
- All electronic components of the implant system are powered by a primary or secondary battery 30 with electrical operating energy.
- FIG. 6 1 schematically shows the structure of a fully implantable hearing system with an intracochlear transducer 18 or 18 'according to FIGS FIGS. 1 to 4 and an implantable microphone 42.
- a wireless remote control 54 serves to control the implant functions through the implant carrier.
- the microphone 42 may be advantageous in the U.S. Patent 5,814,095 constructed known manner and housed with a microphone capsule hermetically sealed on all sides in a housing is, as well as provided with an electrical feedthrough assembly for performing at least one electrical connection from the interior of the housing to the outside thereof, the housing having at least two legs, which are aligned at an angle with respect to each other, wherein the one leg receives the microphone capsule and is provided with a sound inlet membrane, wherein the other leg contains the electrical feedthrough assembly and is set back from the plane of the sound inlet membrane, and wherein the geometry of the microphone housing is selected so that when implanting the microphone in the mastoid of the leg containing the sound inlet membrane from the mastoid in an artificial hole protrudes into the posterior, bony canal wall and the sound inlet membrane touches the skin of the auditory canal wall.
- the microphone 40 may expedient a fixation of the US-A-5,999,632 be known, which has a sleeve which encloses the legs containing the sound inlet membrane with a cylindrical housing part and provided with against the ear canal facing the side of the ear canal wall engageable, projecting, elastic flange parts.
- the fixing element preferably includes a holder, which holds the said flange prior to implantation against an elastic restoring force of the flange in a bent-through the bore of the ear canal wall permitting the bent position.
- To the charging system includes a connected to the output of the charger 55 charging coil 56, preferably in the off US-A-5,279,292 known type forms part of a transmission series resonant circuit which can be inductively coupled to a non-illustrated receive series resonant circuit.
- the reception series resonant circuit in the embodiment according to FIG. 6 Be part of the electronic module 41 and accordingly US-A-5,279,292 a constant current source for the battery 53 ( FIG. 5 ) form.
- the receive series resonant circuit is located in a battery charging circuit, which is closed in dependence on the respective phase of the charging current flowing in the charging circuit via the one or the other branch of a full-wave rectifier bridge.
- the electronic module 41 is in the arrangement according to FIG. 6 connected via a microphone line 58 to the microphone 42 and the implant lead 20 to the intracochlear transducer 18 and 18 '.
- FIG. 7 shows schematically the structure of a partially implantable hearing system with an intracochlear transducer 18 and 18 'according to the FIGS. 1 to 4 ,
- a microphone 42 an electronic module 62 for electronic signal processing are largely as appropriate FIG. 5 (but without the telemetry system 50), the power supply 53 and a modulator / transmitter unit 63 in an externally on the body, preferably on the head above the implant to be worn external module 64 included.
- the implant is energetically passive as in known partial implants. Its electronic module 65 (without battery 53) receives its operating power and converter control data via the modulator / transmitter unit 63 in the external part 64.
- Both the fully implantable and the partially implantable hearing system can be designed to be monaural or binaural.
- a binaural system for rehabilitation of hearing impairment in both ears has two system units, each associated with one of the two ears.
- the two system units can be substantially equal to each other.
- one system unit may also be designed as the master unit and the other system unit as a slave unit controlled by the master unit.
- the signal processing modules of the two system units can communicate with each other in any way, in particular via a wired implantable line connection or via a wireless connection, preferably a bidirectional high-frequency link, a structure-borne sound-coupled ultrasound link or a data transmission path utilizing the electrical conductivity of the tissue of the implant carrier, such that in both system units an optimized binaural signal processing is achieved.
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Abstract
Description
Die vorliegende Erfindung betrifft ein mindestens teilweise implantierbares System zur Rehabilitation einer Hörstörung mit mindestens einem schallaufnehmenden Sensor (Mikrofon), einer elektronischen Anordnung zur Audiosignalverarbeitung und -verstärkung, einer elektrischen Energieversorgungseinheit, welche einzelne Komponenten des Systems mit Strom versorgt, und einer ausgangsseitigen aktorischen Anordnung zur direkten mechanischen Stimulation eines lymphatischen Raums des Innenohres.The present invention relates to an at least partially implantable system for the rehabilitation of a hearing impairment with at least one sound-absorbing sensor (microphone), an electronic arrangement for audio signal processing and amplification, an electrical power supply unit which supplies individual components of the system with power, and an output-side actuator array for direct mechanical stimulation of a lymphatic space of the inner ear.
Unter dem Begriff "Hörstörung" sollen vorliegend alle Arten von Innenohrschäden, kombinierten Innen- und Mittelohrschäden sowie auch zeitweise auftretende oder permanente Ohrgeräusche (Tinnitus) verstanden werden.In the present case, the term "hearing impairment" should be understood to mean all types of inner ear damage, combined inner and middle ear damage as well as occasional or permanent ear noises (tinnitus).
Die Rehabilitation sensorischer Hörstörungen mit teilimplantierbaren, elektronischen Systemen hat in den letzten Jahren einen bedeutenden Stellenwert erhalten. Insbesondere gilt dies für den Patientenkreis, bei dem das Gehör durch Unfall, Krankheit oder sonstige Einflüsse vollständig ausgefallen oder bereits von Geburt an nicht funktionsfähig ist. Ist in diesen Fällen nur das Innenohr (Cochlea) und nicht die nach zentral führende neuronale Hörbahn betroffen, kann mit elektrischen Reizsignalen der verbliebene Hörnerv stimuliert und somit ein Höreindruck erzeugt werden, der bis zu einem offenen Sprachverständnis führen kann. Bei diesen sogenannten Cochlea Implantaten wird ein Reizelektroden-Array in die Cochlea eingeführt, das von einem elektronischen System angesteuert wird, wobei dieses hermetisch dichte und biokompatibel eingekapselte Elektronikmodul operativ im knöchernen Bereich hinter dem Ohr (Mastoid) eingebettet ist. Das elektronische System enthält jedoch im wesentlichen nur Dekodier- und Treiberschaltungen für die Reizelektroden; die akustische Schallaufnahme, die Wandlung dieses Schallsignals in elektrische Signale und deren weitere Verarbeitung erfolgt grundsätzlich extern in einem sogenannten Sprachprozessor, der außen am Körper getragen wird. Der Sprachprozessor setzt die vorverarbeiteten Signale entsprechend kodiert auf ein hochfrequentes Trägersignal um, das über eine induktive Kopplung durch die geschlossene Haut (transkutan) zu dem Implantat übertragen wird. Das schallaufnehmende Mikrofon befindet sich ausnahmslos außerhalb des Körpers und in den meisten Anwendungen in einem an der Ohrmuschel getragenen Gehäuse eines Hinter-dem-Ohr-Hörgerätes (HdO), und es ist mit einem Kabel mit dem Sprachprozessor verbunden. Solche Cochlea-Implantat-Systeme, deren Komponenten und Prinzipien der transkutanen Signalübertragung sind beispielhaft in
Neben der Rehabilitation gehörloser beziehungsweise ertaubter Patienten mit Cochlea Implantaten existieren seit geraumer Zeit Ansätze, Patienten mit einer sensorineuralen Hörstörung, die operativ nicht behebbar ist, mit teil- beziehungsweise vollimplantierbaren Hörgeräten eine bessere Rehabilitation als mit konventionellen Hörgeräten zu bieten. Das Prinzip besteht in den überwiegenden Ausführungsformen darin, ein Ossikel des Mittelohres oder das Innenohr direkt über einen mechanischen beziehungsweise hydromechanischen Reiz zu stimulieren und nicht über das verstärkte akustische Signal eines konventionellen Hörgerätes, bei dem das verstärkte Schallsignal dem äußeren Gehörgang zugeführt wird. Der aktorische Stimulus dieser elektromechanischen Systeme wird mit verschiedenen physikalischen Wandlerprinzipien realisiert wie zum Beispiel durch elektromagnetische und piezoelektrische Systeme. Der Vorteil dieser Verfahren wird hauptsächlich in der gegenüber konventionellen Hörgeräten verbesserten Klangqualität und bei vollimplantierten Systemen in der Unsichtbarkeit der Hörprothese gesehen. Solche teil- und vollimplantierbare elektromechanische Hörgeräte sind beispielhaft von H.
Seit kurzem sind solche teil- und vollimplantierbare Hörsysteme zur Rehabilitation eines Innenohrschadens in der klinischen Anwendung. Dabei zeigt sich je nach verwendetem physikalischem Prinzip des ausgangsseitigen elektromechanischen Wandlers und insbesondere dessen Ankopplungsart an die Ossikel des Mittelohres, dass die erreichten Ergebnisse der Verbesserung des Sprachverständnisses sehr unterschiedlich sein können. Dazu kommt, dass bei manchen Patienten kein ausreichender Lautstärkepegel erreicht werden kann; dieser Aspekt ist spektral sehr unterschiedlich, was bedeuten kann, dass bei zum Beispiel mittleren und hohen Frequenzen die erzeugte Lautheit zwar ausreichend ist, jedoch nicht bei tiefen Frequenzen beziehungsweise umgekehrt. Weiterhin kann die übertragbare spektrale Bandbreite begrenzt sein, so zum Beispiel bei elektromagnetischen Wandlern auf tiefe und mittlere Frequenzen oder bei piezoelektrischen Wandlern auf mittlere und hohe Frequenzen. Darüberhinaus können sich nichtlineare Verzerrungen, die insbesondere bei elektromagnetischen Wandlern ausgeprägt sind, negativ auf die resultierende Klangqualität auswirken. Die mangelnde Lautheit führt insbesondere dazu, dass der audiologische Indikationsbereich für die Implantation eines elektromechanischen Hörsystems sehr eingeschränkt ist, was bedeutet, dass Patienten zum Beispiel mit einem sensorineuralen Hörverlust von größer 50 dB HL (= hearing loss, Hörverlust) im Tieftonbereich mit einem piezoelektrischen System nur unzureichend versorgbar sind. Demgegenüber sind ausgeprägte Hochtonverluste mit elektromagnetischen Wandlern nur schwer versorgbar.Recently, such partially and fully implantable hearing systems for the rehabilitation of an inner ear damage in clinical application. Depending on the used physical principle of the output-side electromechanical transducer and in particular its coupling to the ossicles of the middle ear, it can be seen that the achieved results of the improvement of the speech understanding can be very different. In addition, in some patients, a sufficient volume level can not be achieved; this aspect is spectrally very different, which may mean that for example medium and high frequencies the generated loudness is sufficient, but not at low frequencies or vice versa. Furthermore, the transmittable spectral bandwidth can be limited, such as in electromagnetic transducers to low and medium frequencies or in piezoelectric transducers to medium and high frequencies. In addition, nonlinear distortions, which are particularly pronounced in electromagnetic transducers, can occur are to negatively impact the resulting sound quality. The lack of loudness in particular means that the audiological indication range for the implantation of an electromechanical hearing system is very limited, which means that patients, for example, with a sensorineural hearing loss greater than 50 dB HL (= hearing loss, hearing loss) in the low frequency range with a piezoelectric system can only be supplied insufficiently. In contrast, pronounced high-frequency losses are difficult to supply with electromagnetic transducers.
Viele Patienten mit einem Innenohrschaden leiden zusätzlich unter zeitweise auftretenden oder permanenten Ohrgeräuschen (Tinnitus), die operativ nicht behebbar sind und gegen die bis heute keine zugelassenen medikamentösen Behandlungsformen existieren. Daher sind sogenannte Tinnitus-Maskierer erhältlich; dies sind kleine, batteriebetriebene Geräte, die ähnlich einem Hörgerät hinter oder im Ohr getragen werden und durch artifizielle Schalle, die über einen zum Beispiel Hörgeräte-Lautsprecher in den Gehörgang abgestrahlt werden, den Tinnitus auf psychoakustisch wirkende Weise verdecken ("maskieren") und das störende Ohrgeräusch so möglichst unter die Wahrnehmungsschwelle absenken. Die artifiziellen Schalle sind häufig Schmalbandgeräusche (zum Beispiel Terzrauschen), die in ihrer spektralen Lage und Lautstärkepegel über ein Programmiergerät einstellbar sind, um eine möglichst optimale Anpassung an die individuelle Ohrgeräuschsituation zu ermöglichen. Darüberhinaus existiert seit kurzem die sogenannte "Retraining-Methode", wobei durch die Kombination eines mentalen Trainingsprogramms und die Darbietung eines breitbandigen Schalles (Rauschen) nahe der Ruhehörschwelle die Wahrnehmbarkeit des Tinnitus ebenfalls weitgehend unterdrückt werden soll (
Bei beiden oben genannten Methoden zur apparativen Therapie des Tinnitus sind hörgeräte-ähnliche, technische Geräte außen am Körper im Ohrbereich sichtbar mitzuführen, die den Träger stigmatisieren und daher nicht gerne getragen werden.In both above-mentioned methods for apparative therapy of tinnitus hearing-device-like, technical equipment outside the body in the ear area to carry visible that stigmatize the wearer and therefore are not happy to be worn.
In der
In
Die oben beschriebenen, mindestens teilweise implantierbaren Hörsysteme zur Rehabilitation einer Innenohrschädigung, die auf einem ausgangsseitigen elektromechanischen Wandler basieren, unterscheiden sich von herkömmlichen, konventionellen Hörgeräten im wesentlichen nur dadurch, dass der ausgangsseitige akustische Stimulus (ein verstärktes Schallsignal vor dem Trommelfell) durch einen verstärkten mechanischen Stimulus des Mittel- beziehungsweise Innenohres ersetzt wird. Der akustische Stimulus eines konventionellen Hörgerätes führt schließlich über die mechanische Anregung des Trommelfells und des sich anschließenden Mittelohres auch zu einem vibratorischen, das heißt mechanischen Reiz des Innenohres. Bezüglich der sinnvollen Audiosignalvorverarbeitung bestehen grundlegend ähnliche beziehungsweise gleiche Anforderungen. Weiterhin wird in beiden Ausführungsformen letztendlich ausgangsseitig ein örtlich lokalisierter vibratorischer Stimulus an das geschädigte Innenohr geleitet (zum Beispiel verstärkte mechanische Schwingung des Steigbügels im ovalen Fenster des Innenohres).The above-described, at least partially implantable hearing aid rehabilitation based on an output-side electromechanical transducer, differ essentially from conventional conventional hearing aids essentially only in that the output side acoustic stimulus (an amplified sound signal in front of the eardrum) by an enhanced mechanical Stimulus of the middle or inner ear is replaced. The acoustic stimulus of a conventional hearing aid finally leads via the mechanical stimulation of the eardrum and the subsequent middle ear to a vibratory, that is mechanical stimulus of the inner ear. With regard to the meaningful audio signal preprocessing, fundamentally similar or identical requirements exist. Furthermore, in both embodiments, ultimately, a locally localized vibratory stimulus is directed to the damaged inner ear on the output side (for example, reinforced mechanical vibration of the stirrup in the oval window of the inner ear).
Bei an Taubheit grenzender Schwerhörigkeit sind aus den genannten Gründen unzulänglichen Lautstärkepegels implantierbare, elektromechanische Systeme bislang nicht einsetzbar; hier kommen Cochlea Implantate (CIs) mit rein elektrischer Reizung des Innenohres in Frage, die naturgemäß keine Klangqualität erwarten lassen, die zum Beispiel eine akzeptable Musikübertragung ermöglicht, sondern vorrangig zur Erlangung beziehungsweise Wiederherstellung eines ausreichenden Sprachverständnisses möglichst ohne Lippenablesen konzipiert sind. Auf grund der elektrischen Reizung sind bis zur vollständigen Ertaubung reichende Hörverluste in einem spektral breiten audiologischen Bereich möglich.In deafness-bordering deafness implantable, electromechanical systems are so far not applicable for the reasons mentioned inadequate volume level; Here come cochlear implants (CIs) with purely electrical irritation of the inner ear in question, which naturally can expect no sound quality that allows, for example, an acceptable music transfer, but are designed primarily to obtain or restore a sufficient understanding of speech as possible without lip reading. Due to the electrical stimulation reaching to complete deafening hearing loss in a spectrally broad audiological area are possible.
Bei einer weit verbreiteten Mittelohrschädigung, der sogenannten Otosklerose, bei der insbesondere die Beweglichkeit des Ligaments der Steigbügelaufhängung im ovalen Fenster durch Verkalkungsprozesse eingeschränkt oder vollständig verhindert ist, wird durch die Operationsmethode der Stapedektomie (engl. Stapedotomy) eine passive Prothese verwendet, die einerseits durch einen Bügel zumeist am langen Ambossfortsatz fixiert wird und andererseits mit ihrem zumeist kreisförmigen Schaft in eine artifiziell eingebrachte Öffnung in der Steigbügelfußplatte eingesetzt wird. Der Steigbügel kann auch vollständig entfernt werden. Die Schwingungen des Trommelfells werden über den Hammer auf den Amboss übertragen und bewirken so entsprechende Schwingungen der passiven Prothese, die zu dynamischen Volumenverschiebungen in der Perilymphe des Innenohres, damit zur Auslösung von Wanderwellen auf der Basilarmembran und letztendlich zu einem Höreindruck führen. Diese Methode wird seit Jahrzehnten weltweit als rekonstruktive Mittelohroperation sehr sicher und erfolgreich angewandt. Die Einbringung der Öffnung in der Steigbügelfußplatte wird durch feine chirurgische Instrumente oder insbesondere durch Lasertechniken erreicht.In a widespread middle ear damage, the so-called otosclerosis, in particular, the mobility of the ligament of the stirrup suspension in the oval window is limited or completely prevented by calcification, is used by the surgical method of stapedectomy (English Stapedotomy) a passive prosthesis, on the one hand by a Bracket is usually fixed on the long incus process and on the other hand with its mostly circular shaft in an artificially introduced opening in the stirrup foot plate is used. The stirrup can also be completely removed. The vibrations of the eardrum are transmitted via the hammer on the anvil and thus cause corresponding vibrations of the passive prosthesis, which lead to dynamic volume shifts in the perilymph of the inner ear, thereby triggering traveling waves on the basilar membrane and ultimately to a listening experience. This method has been used for decades as a reconstructive Mittelohroperation very safe and successful. The introduction of the opening in the stirrup footplate is achieved by fine surgical instruments or, in particular, by laser techniques.
Seit kurzer Zeit ist es weiterhin aus CI-Implantationen wissenschaftlich bekannt, dass auch bei nicht vollständiger Taubheit CIs erfolgreich angewendet werden können, wenn mit einem konventionellen Hörgerät keine ausreichende Sprachdiskrimination mehr erreicht werden kann. Interessanterweise konnte nachgewiesen werden, dass die wesentlichen Innenohrstrukturen, die die akustische Resthörigkeit ermöglichen, zum Teil oder weitgehend langzeitstabil erhalten werden können, wenn eine CI-Elektrode in die Cochlea eingeführt wird (
Die ältere
In
Aus
Ein gattungsgemäßes System ist aus der
Der Erfindung liegt die Aufgabe zugrunde, ein mindestens teilweise implantierbares System zur Rehabilitation einer Hörstörung zu schaffen, das in der Lage ist, für eine verbesserte Rehabilitation sensorischer Hörstörungen zu sorgen.The invention has for its object to provide an at least partially implantable system for the rehabilitation of hearing impairment, which is able to provide for improved rehabilitation of sensory hearing disorders.
Diese Aufgabe wird dadurch gelöst, dass bei einem mindestens teilweise implantierbaren System zur Rehabilitation einer Hörstörung mit mindestens einem schallaufnehmenden Sensor (Mikrofon), einer elektronischen Anordnung zur Audiosignalverarbeitung und -verstärkung, einer elektrischen Energieversorgungseinheit, welche einzelne Komponenten des Systems mit Strom versorgt, und einer ausgangsseitigen aktorischen Anordnung zur direkten mechanischen Stimulation eines lymphatischen Raums des Innenohres, erfindungsgemäß die ausgangsseitige aktorische Anordnung aus einem intracochleären elektromechanischen Wandler besteht.This object is achieved in that in an at least partially implantable system for the rehabilitation of a hearing disorder with at least one sound-absorbing sensor (microphone), an electronic device for audio signal processing and amplification, an electrical power unit which supplies power to individual components of the system, and a Output-side actuator array for direct mechanical stimulation of a lymphatic space of the inner ear, according to the invention, the output-side actuator array consists of an intracochlear electromechanical transducer.
Die wesentlichen Vorteile einer erfindungsgemäßen intracochleären Wandlerstruktur bestehen einerseits insbesondere darin, dass der mechanische Stimulus direkt im Innenohr relativ großflächig erzeugt werden kann und keine zusätzlichen Massen, Steifigkeiten der Aufhängung und/oder verlustbehaftete Gelenke der Mittelohrossikel im mechanischen Übertragungsweg liegen, die insbesondere zu linearen Verzerrungen des zu übertragenden Frequenzganges des Wandlers führen können. Andererseits kann davon ausgegangen werden, dass durch die direkte Innenohrstimulation die interindividuelle Reproduzierbarkeit der mechanischen Stimulation deutlich besser ist als bei Übertragung durch Koppelelemente auf die Mittelohrossikel, weil dadurch immer anatomische Schwankungen und insbesondere die persönliche Vorgehensweise des Operateurs eine wichtige Rolle spielen.The main advantages of an intracochlear transducer structure according to the invention are, on the one hand, in particular that the mechanical stimulus can be generated over a relatively large area directly in the inner ear and no additional masses, stiffnesses of the suspension and / or lossy joints of the middle ossicles lie in the mechanical transmission path, in particular to linear distortions of the can lead to transmitted frequency response of the converter. On the other hand, it can be assumed that the interindividual reproducibility of the mechanical stimulation is significantly better by direct inner ear stimulation than in the case of transmission by coupling elements to the middle ear particles, because thereby always anatomical fluctuations and in particular the personal approach of the surgeon play an important role.
Ein weiterer Vorteil der vorliegenden Erfindung besteht darin, dass durch eine direkte, elektromechanische Stimulation der Cochlea das Auftreten von Rückkopplungen (Einkopplung des Ausgangssignals in den Sensor/Mikrofon) erwartungsgemäß weitgehend reduziert wird, weil die Ossikelkette und damit das Trommelfell nicht beziehungsweise deutlich reduziert zu Schwingungen angeregt wird. Dies ist insbesondere dann von Vorteil, wenn ein Schallsensor (Mikrofonfunktion) in unmittelbarer Nähe zum Trommelfell appliziert wird (
Der vorliegend verwendete elektromechanische Wandler arbeitet nach dem Prinzip der dynamischen Volumenänderung aufgrund einer dynamischen Oberflächenvergrößerung beziehungsweise -verkleinerung entsprechend dem elektrischen, ansteuernden Wandlerwechselspannungssignal. Eine optimale Wirkung des Wandlers der vorliegenden Erfindung kann erwartungsgemäß dann erreicht werden, wenn durch konstruktive Maßnahmen dafür gesorgt wird, dass möglichst die ganze Oberfläche des intracochleären Wandlers schwingt (ideal Kugelschwinger), weil dadurch eine maximale Volumenverschiebung und damit ein möglichst hoher Stimulationspegel bei gegebener elektrischer Ansteuerleistung des Wandlers durch das vorverarbeitende Elektroniksystem erreicht wird.The presently used electromechanical transducer operates on the principle of dynamic volume change due to a dynamic surface enlargement or reduction in accordance with the electrical, driving converter AC voltage signal. An optimal effect of the transducer of the present invention can be expected to be achieved if it is ensured by constructive measures that as possible the entire surface of the intracochlear transducer oscillates (ideal ball vibrator), because thereby a maximum volume shift and thus the highest possible stimulation level for a given electrical Drive power of the converter is achieved by the preprocessing electronic system.
Der operative Zugang für den intracochleären Wandler erfolgt vorzugsweise durch das ovale oder ein artifizielles cochleäres Fenster, zum Beispiel ein Promontorialfenster. Nachdem, wie vorstehend geschildert, die Stapedektomie mit Einbringen einer Öffnung in die Steigbügelfußplatte sich seit langem als sichere Mittelohroperation bewährt hat, kann davon ausgegangen werden, dass eine solche Eröffnung und damit ein direkter Zugang zum Innenohr auch dann ohne erhöhtes Schädigungsrisiko möglich ist, wenn keine Otosklerose vorliegt und die Fußplatte noch voll beweglich ist, das heißt bei Vorliegen einer reinen Innenohrschwerhörigkeit. Das bedeutet, dass die bewährten OP-Techniken der Stapedektomie vorliegend für die Wandlerimplantation übertragbar sind.The operative access for the intracochlear transducer is preferably through the oval or an artificial cochlear window, for example a promontorial window. After, as described above, the stapedectomy with the introduction of an opening in the Stirrupfußplatte has long been proven as a safe Mittelohroperation, it can be assumed that such an opening and thus direct access to the inner ear is possible without increased risk of damage, if none Otosclerosis is present and the foot plate is still fully mobile, that is in the presence of a pure inner ear hearing. This means that the proven surgical techniques of stapedectomy are presently applicable to transducer implantation.
Der intracochleäre Wandler ist vorteilhaft am Ende einer flexiblen Trägerstruktur, insbesondere einer Polymer-Trägerstruktur, angeordnet.The intracochlear transducer is advantageously arranged at the end of a flexible support structure, in particular a polymer support structure.
Grundsätzlich kommen alle physikalischen Wandlerprinzipien in Betracht, wie elektromagnetisch, elektrodynamisch, piezoelektrisch, dielektrisch (kapazitiv) und magnetostriktiv. Besonders bevorzugt ist hier das piezoelektrische Prinzip, da mit einfacher Wandlergestaltung dem Ideal des Oberflächenschwingers am einfachsten entsprochen werden kann. Insbesondere kann der intracochleäre Wandler, vorzugsweise mit Ausnützung von geometrischen Gestalttransformationen, insbesondere des Bimorph-Prinzips, des Unimorph-Prinzips oder des Heteromorph-Prinzips mit passiven Materialpartnern, so ausgeführt sein, dass er bei gegebener Wandlerspannung eine maximale Volumenänderung bei minimaler elektrischer Leistungsaufnahme erzeugt.Basically, all physical transducer principles come into consideration, such as electromagnetic, electrodynamic, piezoelectric, dielectric (capacitive) and magnetostrictive. Particularly preferred here is the piezoelectric principle, since with simple transducer design the ideal of the surface vibrator can be most easily met. In particular, the intracochlear transducer, preferably with the use of geometric Shape transformations, in particular the bimorph principle, the unimorph principle or the heteromorphic principle with passive material partners, be designed so that it generates a maximum volume change with a minimum electrical power consumption for a given transducer voltage.
Der intracochleäre Wandler lässt sich besonders einfach herstellen und problemlos implantieren, wenn er einen piezoelektrischen Rohrabschnitt mit zylindrischem Querschnitt aufweist, dessen innere und äußere Umfangsfläche mit einer Oberflächenmetallisierung zur Bildung von elektrische Wandlerelektroden versehen ist.The intracochlear transducer is particularly easy to manufacture and easy to implant if it has a piezoelectric tube section of cylindrical cross-section, the inner and outer circumferential surfaces of which are provided with a surface metallization to form electrical conversion electrodes.
Der intracochleäre piezoelektrische Wandler kann auf der Basis von Blei-Zirkonat-Titanat (PZT) aufgebaut sein. Besonders geeignet ist aber auch ein- oder mehrlagiger Wickel dünner Polyvinylidenfluorid-Folie (PVDF). Zweckmäßig ist das Wandlerelement mit einer biokompatiblen Ummantelung vorzugsweise aus einem elastischen Polymer, zum Beispiel Silikon, versehen. Dabei kann das gesamte Wandlerelement von der biokompatiblen Ummantelung umgeben sein. Entsprechend einer abgewandelten Ausführungsform weist die Ummantelung mindestens eine Öffnung - und vorzugsweise mindestens zwei Öffnungen am unteren Rohrende sowie im oberen Bereich der Ummantelung - für den Ein- und Austritt von intracochleärer Lymphe auf. Die derart ausgebildet ist (sind), dass durch eine dynamische Radiusänderung des Wandlers direkt eine Lymphverschiebung und damit eine intracochleäre Volumenverschiebung erreicht wird. Insbesondere können die Rohroberfläche des intracochleären Wandlers und die Querschnittsfläche der Ein- und Austrittsöffnungen so gestaltet sein, dass eine hydraulische Transformation erreicht wird, die zu höheren Schnellen der Lymphe und damit zu höheren Stimulationspegeln der Cochlea führt als durch direkte Oberflächenveränderung durch den Wandler selbst.The intracochlear piezoelectric transducer can be constructed on the basis of lead zirconate titanate (PZT). But is also particularly suitable single or multilayer winding thin polyvinylidene fluoride film (PVDF). Suitably, the transducer element is provided with a biocompatible sheath, preferably made of an elastic polymer, for example silicone. In this case, the entire transducer element can be surrounded by the biocompatible sheathing. According to a modified embodiment, the sheath has at least one opening - and preferably at least two openings at the lower end of the tube and in the upper region of the sheath - for the entry and exit of intracochlear lymph. Which is designed such that a dynamic change in the radius of the transducer directly a lymphatic displacement and thus an intracochlear volume shift is achieved. In particular, the tube surface of the intracochlear transducer and the cross-sectional area of the inlet and outlet openings can be designed to achieve a hydraulic transformation that results in higher lymph velocity and thus higher cochlear stimulation levels than by direct surface modification by the transducer itself.
Wie an sich aus
In weiterer Ausgestaltung der Erfindung kann ein mechanisches Dämpfungselement vorgesehen sein, das die Schwingungen des intracochleären Wandlers von einer Wandlerzuleitung entkoppelt, um so ein zumindest teilweises Mitschwingen der Mittelohrossikel aufgrund eines mechanischen Kontaktes mit dieser Wandlerzuleitung zu unterbinden beziehungsweise weitgehend zu reduzieren. Ein solches Mitschwingen könnte andernfalls bei Verwendung trommelfellnaher Sensoren (Mikrofone) zu störenden Rückkopplungen führen. Das Material des Dämpfungselementes ist bei ähnlicher Querschnittsgeometrie wie die des Trägers vorzugsweise so gewählt, dass zur Erzielung hoher Dämpfungswerte ein großer mechanischer Impedanzunterschied zu dem Trägermaterial besteht.In a further embodiment of the invention, a mechanical damping element can be provided which decouples the vibrations of the intracochlear transducer from a transducer lead, so as to prevent or substantially reduce at least partial resonant oscillation of the middle ossicles due to mechanical contact with this transducer lead. Such a swinging could otherwise lead to disturbing feedback when using eardrum close sensors (microphones). The material of the damping element is preferably selected with a similar cross-sectional geometry as that of the carrier, that in order to achieve high attenuation values there is a large mechanical impedance difference to the carrier material.
Der intracochleäre Wandler kann zweckmäßig für Volumenveränderungen von etwa 2·10-4 Mikroliter ausgelegt sein. Der Gesamtdurchmesser der intracochleären Wandler-Anordnung kann vorteilhaft im Bereich von 0,2 mm bis 2,0 mm liegen, und die Eintauchtiefe des intracochleären Wandlers sowie die Länge seines aktiven Wandlerelementes können bevorzugt zwischen 0,3 und 2 mm betragen.The intracochlear transducer may suitably be designed for volume changes of about 2 x 10 -4 microliters. The total diameter of the intracochlear transducer array may advantageously be in the range of 0.2 mm to 2.0 mm, and the depth of immersion of the intracochlear transducer and the length of its active transducer element may preferably be between 0.3 and 2 mm.
Entsprechend einer weiteren Ausgestaltung der vorliegenden Erfindung ist ein digitaler Signalprozessor vorgesehen, der die Audiosignalverarbeitung und -aufbereitung vornimmt und/oder digitale Signale für eine Tinnitusmaskierung generiert.According to a further embodiment of the present invention, a digital signal processor is provided which performs the audio signal processing and conditioning and / or generates digital signals for tinnitus masking.
Der Signalprozessor kann statisch in der Weise ausgelegt sein, dass entsprechende Softwaremodule aufgrund wissenschaftlicher Erkenntnisse einmalig in einem Programmspeicher des Signalprozessors abgelegt werden und unverändert bleiben. Liegen dann aber später zum Beispiel aufgrund neuerer wissenschaftlicher Erkenntnisse verbesserte Algorithmen zur Sprachsignalaufbereitung und -verarbeitung vor und sollen diese genutzt werden, muss durch einen invasiven, operativen Patienteneingriff das gesamte Implantat oder das Implantatmodul, das die entsprechende Signalverarbeitungseinheit enthält, gegen ein neues mit der veränderten Betriebssoftware ausgetauscht werden. Dieser Eingriff birgt erneute medizinische Risiken für den Patienten und ist mit hohem Aufwand verbunden. Diesem Problem kann dadurch begegnet werden, dass in weiterer Ausgestaltung der Erfindung eine, vorzugsweise PC-basierte, Telemetrieeinrichtung zur Übertragung von Daten zwischen einem implantierten Teil des Systems und einer externen Einheit, insbesondere einem externen Programmiersystem, vorgesehen ist, und dass dem Signalprozessor zur Aufnahme und Wiedergabe eines Betriebsprogramms eine wiederholt beschreibbare, implantierbare Speicheranordnung zugeordnet ist, wobei mindestens Teile des Betriebsprogramms durch von der externen Einheit über die Telemetrieeinrichtung übermittelte Daten geändert oder ausgetauscht werden können. Auf diese Weise lässt sich nach Implantation des implantierbaren Systems die Betriebssoftware, einschließlich von Software zur Ansteuerung des intracochleären Wandlers, als solche verändern oder auch vollständig austauschen Dies macht es möglich, weitergehende wissenschaftliche Erkenntnisse zum Beispiel bezüglich Sprachsignalverarbeitungsstrategien im Implantat zu implementieren, ohne dass das Implantat durch einen operativen Eingriff ausgetauscht werden muss.The signal processor can be designed statically in such a way that corresponding software modules are stored once on the basis of scientific findings in a program memory of the signal processor and remain unchanged. But later, for example, based on recent scientific findings improved algorithms for speech signal processing and processing before and should they be used by an invasive, surgical patient intervention, the entire implant or implant module containing the corresponding signal processing unit, against a new with the changed Operating software to be replaced. This procedure brings new medical risks for the patient and is associated with high costs. This problem can be addressed by the fact that in a further embodiment of the invention, a preferably PC-based, telemetry device for transmitting data between an implanted part of the system and an external unit, in particular an external programming system is provided, and that the signal processor for recording and reproducing an operating program associated with a rewritable implantable memory device, wherein at least portions of the operating program may be changed or replaced by data communicated from the external device via the telemetry device. In this way, after implantation of the implantable system, the operating software, including software for controlling the intracochlear transducer, as such change or completely exchange. This makes it possible to implement more advanced scientific knowledge, for example, with respect to speech signal processing strategies in the implant, without the implant must be replaced by surgery.
Bevorzugt ist die Auslegung so beschaffen, dass darüber hinaus bei vollimplantierbaren Systemen auch in an sich bekannter Weise Betriebsparameter, das heißt patientenspezifische Daten, wie beispielsweise audiologische Anpassdaten, oder veränderbare Implantatsystemparameter (zum Beispiel als Variable in einem Softwareprogramm zur Ansteuerung des intracochleären Wandlers oder zur Regelung einer Batterienachladung) nach der Implantation transkutan, das heißt drahtlos durch die geschlossene Haut, in das Implantat übertragen und damit verändert werden können. Dabei sind die Softwaremodule bevorzugt dynamisch, oder mit anderen Worten lernfähig, ausgelegt, um zu einer möglichst optimalen Rehabilitation der jeweiligen Hörstörung zu kommen. Insbesondere können die Softwaremodule adaptiv ausgelegt sein, und eine Parameteranpassung kann durch "Training" durch den Implantatträger und weitere Hilfsmittel vorgenommen werden.The design is preferably such that, in addition, in fully implantable systems, operating parameters, that is, patient-specific, are also known per se Data, such as fitting audiological data, or changeable implant system parameters (for example as a variable in a software program for driving the intracochlear transducer or for regulating a battery recharge) after implantation can be transcutaneously, ie wirelessly transmitted through the closed skin, into the implant and thereby changed can. In this case, the software modules are preferably dynamic, or in other words adaptive, designed to come to the best possible rehabilitation of the respective hearing impairment. In particular, the software modules may be designed to be adaptive, and parameter adjustment may be done by "training" by the implant carrier and other aids.
Weiterhin kann die Signalverarbeitungselektronik ein Softwaremodul enthalten, das eine möglichst optimale Stimulation auf der Basis eines lernfähigen neuronalen Netzwerkes erreicht. Das Training dieses neuronalen Netzwerks kann durch den Implantatträger erfolgen und/oder unter Zuhilfenahme weiterer externer Hilfsmittel.Furthermore, the signal processing electronics may include a software module that achieves the best possible stimulation on the basis of a learning neural network. The training of this neural network can be done by the implant wearer and / or with the help of other external aids.
Die Speicheranordnung zum Speichern von Betriebsparametern und die Speicheranordnung zur Aufnahme und Wiedergabe des Betriebsprogramms können als voneinander unabhängige Speicher implementiert sein; es kann sich jedoch auch um einen einzigen Speicher handeln, in dem sowohl Betriebsparameter als auch Betriebsprogramme abgelegt werden können.The memory arrangement for storing operating parameters and the memory arrangement for recording and reproducing the operating program can be implemented as independent memories; However, it can also be a single memory in which both operating parameters and operating programs can be stored.
Die vorliegende Lösung erlaubt eine Anpassung des Systems an Gegebenheiten, die erst nach Implantation des implantierbaren Systems erfassbar sind. So sind beispielsweise bei einem mindestens teilweise implantierbaren Hörsystem zur Rehabilitation einer monauralen oder binauralen Innenohrstörung sowie eines Tinnitus mit mechanischer Stimulation des Innenohres die sensorischen (Schallsensor beziehungsweise Mikrofon) und aktorischen (intracochleärer Wandler) biologischen Schnittstellen immer abhängig von den anatomischen, biologischen und neurophysiologischen Gegebenheiten, zum Beispiel von dem interindividuellen Einheilprozess. Diese Schnittstellenparameter können individuell insbesondere auch zeitvariant sein. So können beispielsweise das Übertragungsverhalten eines implantierten Mikrofons aufgrund von Gewebebelagen und das Übertragungsverhalten des an das Innenohr angekoppelten intracochleären elektromechanischen Wandlers aufgrund unterschiedlicher Ankopplungsqualität interindividuell und individuell variieren. Solche Unterschiede der Schnittstellenparameter, die sich bei den aus dem Stand der Technik bekannten Vorrichtungen nicht einmal durch den Austausch des Implantats mindern beziehungsweise eliminieren ließen, können vorliegend durch Veränderung beziehungsweise Verbesserung der Signalverarbeitung des Implantats optimiert werden.The present solution allows an adaptation of the system to conditions that are detectable only after implantation of the implantable system. Thus, for example, in an at least partially implantable hearing system for the rehabilitation of a monaural or binaural inner ear disorder and tinnitus with mechanical stimulation of the inner ear, the sensory (sound sensor or microphone) and actoric (intracochlear transducer) biological interfaces are always dependent on the anatomical, biological and neurophysiological conditions, for example, of the interindividual healing process. These interface parameters can be individual and also time-variant, in particular. Thus, for example, the transmission behavior of an implanted microphone due to tissue layers and the transmission behavior of the coupled to the inner ear intracochlear electromechanical transducer due to different coupling quality vary individually and individually. Such differences in the interface parameters, which can not even be reduced or eliminated in the devices known from the prior art by exchanging the implant, can be optimized here by changing or improving the signal processing of the implant.
Bei einem mindestens teilweise implantierbaren Hörsystem kann es sinnvoll oder notwendig werden, nach Implantation verbesserte Signalverarbeitungsalgorithmen zu implementieren. Dabei sind insbesondere zu nennen:
- Sprachanalyseverfahren (zum Beispiel Optimierung einer Fast-Fourier-Transformation (FFT)),
- statische oder adaptive Störschallerkennungsverfahren,
- statische oder adaptive Störschallunterdrückungsverfahren,
- Verfahren zur Optimierung des systeminternen Signal-Rauschabstandes,
- optimierte Signalverarbeitungsstrategien bei progredienter Hörstörung,
- ausgangspegelbegrenzende Verfahren zum Schutz des Patienten bei Implantatfehlfunktionen beziehungsweise externen Fehlprogrammierungen,
- Verfahren zur Vorverarbeitung mehrerer Sensor-(Mikrofon-)signale, insbesondere bei binauraler Positionierung der Sensoren,
- Verfahren zur binauralen Verarbeitung zweier oder mehrerer Sensorsignale bei binauraler Sensorpositionierung, zum Beispiel Optimierung des räumlichen Hörens beziehungsweise Raumorientierung,
- Phasen- beziehungsweise Gruppenlaufzeit-Optimierung bei binauraler Signalverarbeitung,
- Verfahren zur optimierten Ansteuerung der Ausgangsstimulatoren, insbesondere bei binauraler Positionierung der Stimulatoren.
- Speech analysis method (for example, optimization of a Fast Fourier Transform (FFT)),
- static or adaptive noise detection methods,
- static or adaptive noise reduction methods,
- Method for optimizing the system-internal signal-to-noise ratio,
- optimized signal processing strategies for progressive hearing impairment,
- Output level limiting method for protecting the patient in case of implant malfunction or external malfunction programming,
- Method for preprocessing a plurality of sensor (microphone) signals, in particular for binaural positioning of the sensors,
- Method for the binaural processing of two or more sensor signals in the case of binaural sensor positioning, for example optimization of spatial hearing or spatial orientation,
- Phase or group delay optimization in binaural signal processing,
- Method for optimized control of the output stimulators, in particular for binaural positioning of the stimulators.
Mit dem vorliegenden System lassen sich auch nach der Implantation unter anderem die folgenden Signalverarbeitungsalgorithmen implementieren:
- Verfahren zur Optimierung des Betriebsverhaltens des intracochleären Ausgangswandlers (zum Beispiel Frequenz- und Phasengangoptimierung, Verbesserung des Impuls-übertragungsverhaltens),
- Sprachsignal-Kompressionsverfahren bei Innenohrschwerhörigkeiten,
- Signalverarbeitungsmethoden zur Recruitment-Kompensation bei Innenohrschwerhörigkeiten.
- Method for optimizing the operating behavior of the intracochlear output transducer (for example frequency and phase response optimization, improvement of the pulse transmission behavior),
- Speech signal compression method for inner ear hearing loss,
- Signal processing methods for recruitment compensation for inner ear hearing loss.
Des weiteren ist bei Implantatsystemen mit einer sekundären Energieversorgungseinheit, das heißt einem nachladbaren Akkumulatorsystem, aber auch bei Systemen mit primärer Batterieversorgung davon auszugehen, dass diese elektrischen Energiespeicher mit voranschreitender Technologie immer größere Lebensdauern und damit steigende Verweilzeiten im Patienten ermöglichen. Es ist davon auszugehen, dass die Grundlagen- und Applikätionsforschung für Signalverarbeitungsalgorithmen schnelle Fortschritte macht. Die Notwendigkeit oder der Patientenwunsch einer Betriebssoftwareanpassung beziehungsweise -veränderung wird daher voraussichtlich vor Ablauf der Lebensdauer der implantatinternen Energiequelle eintreten. Das vorliegend beschriebene System erlaubt eine derartige Anpassung der Betriebsprogramme des Implantats auch im bereits implantierten Zustand.Furthermore, in implant systems with a secondary power supply unit, that is to say a rechargeable battery system, but also in systems with a primary battery supply, it can be assumed that these electrical energy storage devices are progressing Technology to enable ever longer lifetimes and thus increasing residence times in the patient. It is expected that basic and applied science research will make rapid progress in signal processing algorithms. The need or the patient's desire for an operating software adaptation or change is therefore likely to occur before the end of the life of the internal implant energy source. The system described here allows such an adaptation of the operating programs of the implant even in the already implanted state.
Vorzugsweise ist ferner eine Zwischenspeicheranordnung vorgesehen, in welcher von der externen Einheit über die Telemetrieeinrichtung übermittelte Daten vor dem Weiterleiten an den Signalprozessor zwischengespeichert werden können. Auf diese Weise lässt sich der Übertragungsvorgang von der externen Einheit zu dem implantierten System abschließen, bevor die über die Telemetrieeinrichtung übermittelten Daten an den Signalprozessor weitergeleitet werden.Preferably, a buffer memory arrangement is further provided, in which data transmitted by the external unit via the telemetry device can be buffered before forwarding to the signal processor. In this way, the transmission process from the external unit to the implanted system can be completed before the data transmitted via the telemetry device are forwarded to the signal processor.
Des weiteren kann eine Überprüfungslogik vorgesehen sein, die in der Zwischenspeicheranordnung gespeicherte Daten vor dem Weiterleiten an den Signalprozessor einer Überprüfung unterzieht. Es kann ein Mikroprozessorbaustein, insbesondere ein Mikrocontroller, zum implantatinternen Steuern des Signalprozessors über einen Datenbus vorgesehen sein, wobei zweckmäßig die Überprüfungslogik und die Zwischenspeicheranordnung in dem Mikroprozessorbaustein implementiert sind und wobei über den Datenbus und die Telemetrieeinrichtung auch Programmteile oder ganze Softwaremodule zwischen der Außenwelt, dem Mikroprozessorbaustein und dem Signalprozessor übermittelt werden können.Furthermore, a check logic may be provided which subjects the data stored in the latch arrangement to a check prior to routing to the signal processor. It may be a microprocessor module, in particular a microcontroller, provided for implant-internal control of the signal processor via a data bus, expediently the verification logic and the buffer arrangement are implemented in the microprocessor module and wherein via the data bus and the telemetry and program parts or entire software modules between the outside world, the Microprocessor module and the signal processor can be transmitted.
Dem Mikroprozessorbaustein ist vorzugsweise eine implantierbare Speicheranordnung zum Speichern eines Arbeitsprogramms für den Mikroprozessorbaustein zugeordnet, und mindestens Teile des Arbeitsprogramms für den Mikroprozessorbaustein können durch von der externen Einheit über die Telemetrieeinrichtung übermittelte Daten geändert oder ausgetauscht werden.The microprocessor chip is preferably associated with an implantable memory device for storing a work program for the microprocessor chip, and at least parts of the work program for the microprocessor chip may be changed or replaced by data transmitted from the external device via the telemetry device.
In weiterer Ausgestaltung der Erfindung können mindestens zwei Speicherbereiche zur Aufnahme und Wiedergabe mindestens des Betriebsprogramms des Signalprozessors vorgesehen sein. Dies trägt zur Fehlersicherheit des Systems bei, indem durch das mehrfache Vorhandensein des Speicherbereichs, welcher das beziehungsweise die Betriebsprogramme enthält, beispielsweise nach einer Übertragung von extern oder aber beim Einschalten des Implantats eine Überprüfung der Fehlerfreiheit der Software durchgeführt werden kann.In a further embodiment of the invention, at least two memory areas may be provided for recording and reproducing at least the operating program of the signal processor. This contributes to the error safety of the system, in that by the multiple presence of the memory area which contains the operating program (s), for example after a transmission from external or when the implant is switched on, a check can be carried out for the correctness of the software.
Analog hierzu kann auch die Zwischenspeicheranordnung mindestens zwei Speicherbereiche zur Aufnahme und Wiedergabe von von der externen Einheit über die Telemetrieeinrichtung übermittelten Daten aufweisen, so dass nach einer Datenübertragung von der externen Einheit noch im Bereich des Zwischenspeichers eine Überprüfung der Fehlerfreiheit der übermittelten Daten vorgenommen werden kann. Die Speicherbereiche können zur beispielsweise komplementären Ablage der von der externen Einheit übermittelten Daten ausgelegt sein. Mindestens einer der Speicherbereiche der Zwischenspeicheranordnung kann aber auch zur Aufnahme nur eines Teils der von der externen Einheit übermittelten Daten ausgelegt sein, wobei in diesem Fall die Überprüfung der Fehlerfreiheit der übermittelten Daten abschnittsweise erfolgt.Analogously, the buffer memory 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 a data transmission from the external unit or in the area of the cache memory, a check of the accuracy of the transmitted data can be made. The memory areas can be designed for, for example, complementary storage of the data transmitted by the external unit. However, at least one of the memory areas of the buffer arrangement can also be designed to accommodate only a part of the data transmitted by the external unit, in which case the checking of freedom from error of the transmitted data takes place in sections.
Um zu gewährleisten, dass bei Übertragungsfehlern ein erneuter Übertragungsvorgang gestartet werden kann, kann dem Signalprozessor ferner ein vorprogrammierter, nicht überschreibbarer Festspeicherbereich zugeordnet sein, in welchem die für einen "Minimalbetrieb" des Systems erforderlichen Anweisungen und Parameter gespeichert sind, beispielsweise Anweisungen, die nach einem "Systemabsturz" zumindest einen fehlerfreien Betrieb der Telemetrieeinrichtung zum Empfang eines Betriebsprogramms sowie Anweisungen zum Einspeichern desselben in die Steuerlogik gewährleisten.In order to ensure that transmission errors can be restarted, the signal processor may also be associated with a preprogrammed non-rewritable memory area in which the instructions and parameters required for a "minimum operation" of the system are stored, for example instructions following a "Crash" at least ensure error-free operation of the telemetry device for receiving an operating program and instructions for storing the same in the control logic.
Wie bereits erwähnt, ist die Telemetrieeinrichtung in vorteilhafter Weise außer zum Empfang von Betriebsprogrammen von der externen Einheit auch zur Übermittlung von Betriebsparametem zwischen dem implantierbaren Teil des Systems und der externen Einheit ausgelegt, so dass einerseits solche Parameter von einem Arzt, einem Hörgeräteakustiker oder dem Träger des Systems selbst eingestellt werden können (zum Beispiel Lautstärke), andererseits das System aber auch Parameter an die externe Einheit übermitteln kann, beispielsweise um den Status des Systems zu überprüfen.As already mentioned, in addition to receiving operating programs from the external unit, the telemetry device is also advantageously designed for the transmission of operating parameters between the implantable part of the system and the external unit, such that on the one hand such parameters are provided by a physician, a hearing healthcare professional or the wearer On the other hand, the system can also transmit parameters to the external unit, for example, to check the status of the system.
Ein vollständig implantierbares Hörsystem der vorliegend erläuterten Art kann implantatseitig neben dem intracochleären Wandler und der Signalverarbeitungseinheit mindestens einen implantierbaren Schallsensor und ein nachladbares elektrisches Speicherelement aufweisen, wobei in einem solchen Fall bevorzugt eine drahtlose, transkutane Ladevorrichtung zum Laden des Speicherelements vorgesehen ist. Es versteht sich jedoch, dass zur Energieversorgung auch eine Primärzelle oder eine andere Energieversorgungseinheit vorhanden sein kann, die keine transkutane Nachladung benötigt. Dies gilt insbesondere, wenn man berücksichtigt, dass in naher Zukunft vor allem durch Weiterentwicklung der Prozessortechnologie mit wesentlicher Verminderung des Energiebedarfs für elektronische Signalverarbeitung zu rechnen ist, so dass für implantierbare Hörsysteme neue Energieversorgungsformen praktisch anwendbar werden, zum Beispiel eine den Seebeck-Effekt nutzende Energieversorgung, wie sie in
Bei teilimplantierbarer Ausbildung des Hörsystems sind mindestens ein Schallsensor, die elektronische Signalverarbeitungseinheit, die Energieversorgungseinheit sowie eine Modulator/Sender-Einheit in einem extern am Körper, vorzugsweise am Kopf über dem Implantat, zu tragenden externen Modul enthalten. Das Implantat weist den ausgangsseitigen elektromechanischen, intracochleären Wandler auf, ist aber energetisch passiv und empfängt seine Betriebsenergie und Steuerdaten für den intracochleären Wandler über die Modulator/Sender-Einheit im externen Modul.In teilimplantierbarer training of the hearing system at least one sound sensor, the electronic signal processing unit, the power supply unit and a modulator / transmitter unit in a externally on the body, preferably on the head above the implant to be worn external module included. The implant has the output side electromechanical intracochlear transducer, but is energetically passive and receives its operating and control data for the intracochlear transducer via the modulator / transmitter unit in the external module.
Das beschriebene System kann bei vollimplantierbarer Auslegung ebenso wie bei teilimplantierbarem Aufbau monaural oder binaural ausgelegt sein. Ein binaurales System zur Rehabilitation einer Hörstörung beider Ohren weist zwei Systemeinheiten auf, die jeweils einem der beiden Ohren zugeordnet sind. Dabei können die beiden Systemeinheiten einander im wesentlichen gleich sein. Es kann aber auch die eine Systemeinheit als Master-Einheit und die andere Systemeinheit als von der Master-Einheit gesteuerte Slave-Einheit ausgelegt sein. Die Signalverarbeitungsmodule der beiden Systemeinheiten können auf beliebige Weise, insbesondere über eine drahtgebundene implantierbare Leitungsverbindung oder über eine drahtlose Verbindung, vorzugsweise eine bidirektionale Hochfrequenzstrecke, eine körperschallgekoppelte Ultraschallstrecke oder eine die elektrische Leitfähigkeit des Gewebes des Implantatträgers ausnutzende Datenübertragungsstrecke, so miteinander kommunizieren, dass in beiden Systemeinheiten eine optimierte binaurale Signalverarbeitung und Wandler-Array-Ansteuerung erreicht wird.The system described can be designed monaural or binaural in vollimplantierbarer design as well as teilimplantierbarem structure. A binaural system for rehabilitation of hearing impairment in both ears has two system units, each associated with one of the two ears. In this case, the two system units can be substantially equal to each other. However, one system unit may also be designed as the master unit and the other system unit as a slave unit controlled by the master unit. The signal processing modules of the two system units can communicate with each other in any way, in particular via a wired implantable line connection or via a wireless connection, preferably a bidirectional high-frequency link, a structure-borne sound-coupled ultrasound link or a data transmission path utilizing the electrical conductivity of the tissue of the implant carrier, such that in both system units an optimized binaural signal processing and transducer array drive is achieved.
Bevorzugte Ausführungsbeispiele des erfindungsgemäßen Hörsystems beziehungsweise möglicher teil- und vollimplantierbarer Gesamtsysteme sind nachstehend unter Bezugnahme auf die beiliegenden Zeichnungen näher beschrieben. Es zeigen:
- FIG. 1
- schematisch einen Schnitt durch einen Teil des menschliches Mittelohres mit implantiertem intracochleärem Wandler,
- FIG. 2
- schematisch den prinzipiellen Aufbau des intracochleären Wandlers gemäß
FIG. 1 , - FIG. 3
- einen Schnitt entlang der Linie III-III der
FIG. 4 für eine abgewandelte Ausführungs- form des intracochleären Wandlers gemäßFIG. 1 , - FIG. 4
- eine Seitenansicht des intracochleären Wandlers gemäß
FIG. 3 , - FIG. 5
- ein Blockschaltbild eines vollimplantierbaren Hörsystems zur Rehabilitation einer Mittel- und/oder Innenohrstörung und/oder eines Tinnitus,
- FIG. 6
- ein vollimplantierbares Hörsystem gemäß vorliegender Erfindung sowie
- FIG. 7
- ein teilimplantierbares Hörsystem gemäß vorliegender Erfindung.
- FIG. 1
- FIG. 2 schematically shows a section through part of the human middle ear with implanted intracochlear transducer, FIG.
- FIG. 2
- schematically the basic structure of the intracochlear transducer according to
FIG. 1 . - FIG. 3
- a section along the line III-III of
FIG. 4 for a modified embodiment of the intracochlear transducer according to FIGFIG. 1 . - FIG. 4
- a side view of the intracochlear transducer according to
FIG. 3 . - FIG. 5
- a block diagram of a fully implantable hearing system for the rehabilitation of a middle and / or inner ear disorder and / or tinnitus,
- FIG. 6
- a fully implantable hearing system according to the present invention as well as
- FIG. 7
- a partially implantable hearing system according to the present invention.
Durch die Perforation der Steigbügelfußplatte 11 hindurch ist in das Innenohr ein intracochleärer elektromechanischer Wandler 18, 18' als Ganzes eingebracht. Die in
Weiterhin kann ein mechanisches Dämpfungselement 28 vorgesehen sein, das die Schwingungen des Wandlers 18, 18' von der Zuleitung 20 entkoppelt und somit eine Übertragung der Wandlerschwingungen auf die Mittelohrossikel vermeidet oder mindestens reduziert, die bei Verwendung eines ortsnahen Schallsensors (Mikrofons) des implantierbaren Hörsystems zu einer unerwünschten Rückkopplung führen könnten.Furthermore, a mechanical damping
Der elektromechanische Wandler 18, 18' arbeitet nach dem Prinzip der dynamischen volumenänderung aufgrund einer dynamischen Oberflächenvergrößerung beziehungsweise -verkleinerung entsprechend dem elektrischen, ansteuernden Wandlerwechselspannungssignal. Die erforderlichen Volumenveränderungen für einen adäquaten, äquivalenten Schalldruckpegel von ca. 100 dB SPL ergeben sich zu etwa 2·10-4 Mikroliter. Der Gesamtdurchmesser der Wandler-Anordnung liegt im Bereich von 0,2 mm bis 2,0 mm. Die Eintauchtiefe des Wandlers liegt im Bereich von 0,3 bis 2 mm, die Länge des aktiven Wandlerelements im gleichen Bereich.The
Bei Anlegen einer elektrischen Wechselspannung an den piezoelektrischen Rohrabschnitt 30 ergibt sich eine entsprechende dynamische Radiusveränderung, die zu der beschriebenen dynamischen Volumenverschiebung in der intracochleären Flüssigkeit führt. Das gesamte Wandlerelement 30, 31, 32 ist in dieser Ausführungsform vorzugsweise mit einer biokompatiblen dünnen Ummantelung 33 umgeben. Die Ummantelung 33 besteht vorzugsweise aus einem elastischen Polymer wie zum Beispiel Silikon, das sich als Trägermaterial für Cochlea-Implantat-Elektroden hervorragend bewährt hat.Upon application of an electrical alternating voltage to the
Die
Die digitalen Ausgangssignale des Signalprozessors 44 werden in einer Digital-AnalogWandler (D/A)- und Treibereinheit 45 in Analogsignale umgewandelt und auf den zur Ansteuerung des Wandlers 18, 18' gewünschten Pegel gebracht. Diese Einheit 45 kann unter Umständen völlig entfallen, wenn zum Beispiel bei Verwendung eines elektromagnetischen intracochleären Ausgangswandlers ein beispielsweise pulsweitenmoduliertes, serielles digitales Ausgangssignal des Signalprozessors 44 direkt an den Ausgangswandler übermittelt wird.The digital output signals of the
Bei der in
Der Mikrocontroller 47 kommuniziert bei der dargestellten implantierbaren Ausführungsform über einen Datenbus 49 mit einem Telemetriesystem (TS) 50. Dieses Telemetriesystem 50 kommuniziert seinerseits durch die bei 51 angedeutete geschlossene Haut beispielweise über eine nicht dargestellte induktive Spulenkopplung drahtlos bidirektional mit einem externen Programmiersystem (PS) 52. Das Programmiersystem 52 kann vorteilhaft ein PC-basiertes System mit entsprechender Programmier-, Bearbeitungs-, Darstellungs- und Verwaltungssoftware sein. Über diese Telemetrieschnittstelle wird die zu verändernde beziehungsweise ganz auszutauschende Betriebssoftware des Implantatsystems übertragen und zunächst in dem Speicherbereich S4 und/oder S5 des Mikrocontrollers 47 zwischengespeichert. So kann zum Beispiel der Speicherbereich S5 für eine komplementäre Ablage der von dem externen System übermittelten Daten benutzt werden, und eine einfache Verifikation der Softwareübertragung durch einen Lesevorgang über die Telemetrieschnittstelle kann durchgeführt werden, um die Koinzidenz der Inhalte der Speicherbereiche S4 und S5 zu überprüfen, bevor der Inhalt des wiederholt beschreibbaren Speicher S3 geändert oder ausgetauscht wird.The
Die Betriebssoftware des mindestens teilweise implantierbaren Hörsystems soll gemäß der vorliegend verwendeten Nomenklatur sowohl die Betriebssoftware des Mikrocontrollers 47 (zum Beispiel Housekeeping-Funktionen, wie Energiemanagement oder Telemetriefunktionen) als auch die Betriebssoftware des digitalen Signalprozessors 44 umfassen. So kann zum Beispiel eine einfache Verifikation der Softwareübertragung durch einen Lesevorgang über die Telemetrieschnittstelle durchgeführt werden, bevor die Betriebssoftware oder die entsprechenden Signalverarbeitungsanteile dieser Software in den Programmspeicherbereich S1 des digitalen Signalprozessors 44 über den Datenbus 48 übertragen werden. Ferner kann auch das Arbeitsprogramm für den Mikrocontroller 47, das beispielsweise in dem wiederholt beschreibbaren Speicher S3 eingespeichert ist, über die Telemetrieschnittstelle 50 ganz oder teilweise mit Hilfe der externen Einheit 52 geändert oder ausgetauscht werden.According to the nomenclature used here, the operating software of the at least partially implantable hearing system should comprise 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
Alle elektronischen Komponenten des Implantatsystems werden durch eine primäre oder sekundäre Batterie 30 mit elektrischer Betriebsenergie versorgt.All electronic components of the implant system are powered by a primary or
Das Mikrofon 42 kann vorteilhaft in der aus
Zu dem Ladesystem gehört auch eine an den Ausgang des Ladegerätes 55 angeschlossene Ladespule 56, die vorzugsweise in der aus
Das Elektronikmodul 41 ist bei der Anordnung nach
Sowohl das vollimplantierbare als auch das teilimplantierbare Hörsystem können monoaural oder binaural ausgelegt sein. Ein binaurales System zur Rehabilitation einer Hörstörung beider Ohren weist zwei Systemeinheiten auf, die jeweils einem der beiden Ohren zugeordnet sind. Dabei können die beiden Systemeinheiten einander im wesentlichen gleich sein. Es kann aber auch die eine Systemeinheit als Master-Einheit und die andere Systemeinheit als von der Master-Einheit gesteuerte Slave-Einheit ausgelegt sein. Die Signalverarbeitungsmodule der beiden Systemeinheiten können auf beliebige Weise, insbesondere über eine drahtgebundene implantierbare Leitungsverbindung oder über eine drahtlose Verbindung, vorzugsweise eine bidirektionale Hochfrequenzstrecke, eine körperschallgekoppelte Ultraschallstrecke oder eine die elektrische Leitfähigkeit des Gewebes des Implantatträgers ausnutzende Datenübertragungsstrecke, so miteinander kommunizieren, dass in beiden Systemeinheiten eine optimierte binaurale Signalverarbeitung erreicht wird.Both the fully implantable and the partially implantable hearing system can be designed to be monaural or binaural. A binaural system for rehabilitation of hearing impairment in both ears has two system units, each associated with one of the two ears. In this case, the two system units can be substantially equal to each other. However, one system unit may also be designed as the master unit and the other system unit as a slave unit controlled by the master unit. The signal processing modules of the two system units can communicate with each other in any way, in particular via a wired implantable line connection or via a wireless connection, preferably a bidirectional high-frequency link, a structure-borne sound-coupled ultrasound link or a data transmission path utilizing the electrical conductivity of the tissue of the implant carrier, such that in both system units an optimized binaural signal processing is achieved.
Folgende Kombinationsmöglichkeiten sind vorsehbar:
- Beide Elektronikmodule können jeweils einen digitalen Signalprozessor gemäß vorstehender Beschreibung enthalten, wobei die Betriebssoftware beider Prozessoren wie beschrieben transkutan veränderbar ist. Dann sorgt die Verbindung beider Module im wesentlichen für den Datenaustausch zur optimierten binauralen Signalverarbeitung zum Beispiel der Sensorsignale.
- Nur ein Modul enthält den beschriebenen digitalen Signalprozessor, wobei dann die Modulverbindung neben der Sensordatenübertragung zur binauralen Schallanalyse und -verrechnung auch für die Ausgangsignalübermittlung zu dem kontralateralen Wandler sorgt, wobei in dem kontralateralen Modul der elektronische Wandlertreiber untergebracht sein kann. In diesem Fall ist die Betriebssoftware des gesamten binauralen Systems nur in einem Modul abgelegt und wird auch nur dort transkutan über eine nur einseitig vorhandene Telemetrieeinheit von extern verändert. In diesem Fall kann auch die energetische Versorgung des gesamten binauralen Systems in nur einem Elektronikmodul untergebracht sein, wobei die energetische Versorgung des kontralateralen Moduls drahtgebunden oder drahtlos geschieht.
- Both electronic modules can each contain a digital signal processor according to the above description, wherein the operating software of both processors as described transcutaneously changeable. Then, the connection of both modules essentially ensures the exchange of data for optimized binaural signal processing, for example of the sensor signals.
- Only one module contains the digital signal processor described, in which case the module connection, in addition to the sensor data transmission for binaural sound analysis and accounting, also provides the output signal transmission to the contralateral converter, wherein the electronic converter driver can be accommodated in the contralateral module. In this case, the operating software of the entire binaural system is stored only in one module and is only transactively changed externally via a single-sided telemetry unit. In this case, the energetic supply of the entire binaural system can be accommodated in only one electronic module, wherein the energetic supply of the contralateral module is wired or wireless.
Claims (19)
- An at least partially implantable hearing system for rehabilitation of a hearing disorder comprising at least one sensor, such as a microphone (42), for picking up sound, an electronic arrangement (41; 62, 65) for audio signal processing and amplification, an electrical power supply unit (53) which supplies individual components of the system with power, and an actoric output-side arrangement for direct mechanical stimulation of a lymphatic inner ear space, wherein the actoric output-side arrangement consists of an intracochlear electromechanical transducer (18, 18'), characterized in that the intracochlear electromechanical transducer (18, 18') operates according to the principle of dynamic volume change as a result of dynamic surface enlargement or reduction in conformity with an electrical alternating voltage transducer control signal.
- The hearing system of claim 1, characterized in that the intracochlear transducer (18, 18') has a surface at least a major portion of which is designed to vibrate.
- The hearing system of one of the preceding claims, characterized in that the intracochlear transducer (18, 18') is adapted for surgical access through the oval window or an artificial cochlear window, such as a promontorial window.
- The hearing system of one of the preceding claims, characterized in that the intracochlear transducer (18, 18') is disposed at the end of a flexible carrier (26), particularly a polymer carrier.
- The hearing system of one of the preceding claims, characterized in that the intracochlear transducer (18, 18') is a piezoelectric electromechanical transducer.
- The hearing system of claim 5, characterized in that the intracochlear transducer (18, 18') comprises a piezoelectric tube section (30) with a cylindrical cross-section, the inner and outer circumferential surfaces of which having metal coatings which define electrical transducer electrodes (31, 32).
- The hearing system of one of the preceding claims, characterized in that the intracochlear transducer (18, 18') has an active transducer element (30, 31, 32), wherein at least this transducer element has a biocompatible cover (33) which in particular is made of an elastic polymer such as silicone.
- The hearing system of claim 7, characterized in that at least one opening (35, 37) of the cover (33) for entry and exit of intracochlear lymph is adapted to cause by means of a dynamic change of radius of the transducer (18') direct lymph displacement and hence an intracochlear volume displacement.
- The hearing system of claims 6 and 8, characterized in that openings (35, 37) are provided at the lower tubular end and in the upper part of the cover (33).
- The hearing system of claim 9, characterized in that the tubular surface of the intracochlear transducer (18') and the cross-sectional surface of the entry and exit openings (35, 37) are designed to provide for a hydraulic transformation such that higher lymph velocities and consequently higher cochlea stimulation levels are attained than those obtained by a direct surface change of the transducer itself.
- The hearing system of one of the preceding claims, characterized in that the intracochlear transducer (18, 18') is designed such that its first mechanical resonance frequency is at the upper spectral end of the transmission range.
- The hearing system of one of the preceding claims, characterized in that a mechanical attenuation element (28) is provided which decouples vibrations of the intracochlear transducer (18, 18') from the transducer feed line (20).
- The hearing system of claims 4 and 12, characterized in that the material of the attenuation element (28) at a cross-section geometry similar to that of the carrier (26) is selected such that there is a large mechanical impedance difference as compared to the carrier material in order to achieve high attenuation values.
- The hearing system of one of the preceding claims, characterized in that a digital signal processor (44) is provided for audio signal processing and conditioning and/or for generating digital signals for tinnitus masking.
- The hearing system of claim 14, characterized by a preferably computer-based telemetry means (50) for transmitting data from an implanted part (41) of the system to an external unit (52), particularly to an external programming system.
- The hearing system of claim 14 or 15, characterized in that a rewritable implantable storage arrangement (S1, S2) is assigned to the signal processor (44) for storage and retrieval of an operating program, and in that at least parts of the operating program are adapted to be modified or replaced by data transmitted from the external unit (52) via the telemetry means (50).
- The hearing system of claim 16, characterized in that additionally a buffer storage arrangement (S4, S5) is provided which is adapted to buffer data transmitted from the external unit (52) via the telemetry means (50) before said data being relayed to the signal processor (44), and in that preferably a checking logic (47) is provided for checking data stored in the buffer storage arrangement (S4, S5) before said data being relayed to the signal processor (44).
- The hearing system of claim 17, characterized by a microprocessor module (47) for control of the audio signal processing and conditioning arrangement (43, 44, 45) and/or for generating digital signals for tinnitus masking.
- The hearing system according to claim 18, characterized in that an implantable storage arrangement (S3) for storage of an operating program for the microprocessor module is assigned to the microprocessor module (47), and in that at least parts of the operating program for the microprocessor module are adapted to be modified or replaced by data transmitted from the external unit (52) via the telemetry means (50).
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
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DE10046938A DE10046938A1 (en) | 2000-09-21 | 2000-09-21 | At least partially implantable hearing system with direct mechanical stimulation of a lymphatic space in the inner ear |
DE10046938 | 2000-09-21 |
Publications (3)
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EP1191815A2 EP1191815A2 (en) | 2002-03-27 |
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EP01118050A Expired - Lifetime EP1191815B1 (en) | 2000-09-21 | 2001-07-25 | At least partially implantable hearing system with direct mechanical stimulation of a lymphatic space of the internal ear |
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EP (1) | EP1191815B1 (en) |
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Families Citing this family (55)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE10212726A1 (en) * | 2002-03-21 | 2003-10-02 | Armin Bernhard | Sound transducer for an implantable hearing aid |
WO2004024212A2 (en) * | 2002-09-10 | 2004-03-25 | Vibrant Med-El Hearing Technology Gmbh | Implantable medical devices with multiple transducers |
EP1435757A1 (en) * | 2002-12-30 | 2004-07-07 | Andrzej Zarowski | Device implantable in a bony wall of the inner ear |
WO2005124722A2 (en) * | 2004-06-12 | 2005-12-29 | Spl Development, Inc. | Aural rehabilitation system and method |
US8401212B2 (en) | 2007-10-12 | 2013-03-19 | Earlens Corporation | Multifunction system and method for integrated hearing and communication with noise cancellation and feedback management |
US7668325B2 (en) | 2005-05-03 | 2010-02-23 | Earlens Corporation | Hearing system having an open chamber for housing components and reducing the occlusion effect |
US20080205679A1 (en) * | 2005-07-18 | 2008-08-28 | Darbut Alexander L | In-Ear Auditory Device and Methods of Using Same |
US20070127757A2 (en) * | 2005-07-18 | 2007-06-07 | Soundquest, Inc. | Behind-The-Ear-Auditory Device |
US7801542B1 (en) * | 2005-12-19 | 2010-09-21 | Stewart Brett B | Automatic management of geographic information pertaining to social networks, groups of users, or assets |
US8014871B2 (en) * | 2006-01-09 | 2011-09-06 | Cochlear Limited | Implantable interferometer microphone |
EP2129428A4 (en) * | 2007-03-29 | 2011-05-04 | Med El Elektromed Geraete Gmbh | Implantable auditory stimulation systems having a transducer and a transduction medium |
DE102007031114B4 (en) * | 2007-06-29 | 2013-10-10 | Eberhard-Karls-Universität Tübingen Universitätsklinikum | Hearing implant with multidirectional acting actuator |
AU2008282451B2 (en) * | 2007-07-27 | 2013-09-26 | Second Sight Medical Products | Implantable device for the brain |
US20090287277A1 (en) * | 2008-05-19 | 2009-11-19 | Otologics, Llc | Implantable neurostimulation electrode interface |
KR101568452B1 (en) | 2008-06-17 | 2015-11-20 | 이어렌즈 코포레이션 | Optical electro-mechanical hearing devices with separate power and signal components |
GB2490822B (en) | 2008-07-11 | 2013-02-27 | Brain Basket Llc | Magnetostrictive auditory system |
US20100069997A1 (en) * | 2008-09-16 | 2010-03-18 | Otologics, Llc | Neurostimulation apparatus |
WO2010033932A1 (en) | 2008-09-22 | 2010-03-25 | Earlens Corporation | Transducer devices and methods for hearing |
WO2010105291A1 (en) | 2009-03-16 | 2010-09-23 | Cochlear Limited | Transcutaneous modulated power link for a medical implant |
WO2009065971A2 (en) * | 2009-03-24 | 2009-05-28 | Phonak Ag | Fully or partially implantable hearing system |
US9044588B2 (en) * | 2009-04-16 | 2015-06-02 | Cochlear Limited | Reference electrode apparatus and method for neurostimulation implants |
WO2010138911A1 (en) | 2009-05-29 | 2010-12-02 | Otologics, Llc | Implantable auditory stimulation system and method with offset implanted microphones |
EP2438768B1 (en) * | 2009-06-05 | 2016-03-16 | Earlens Corporation | Optically coupled acoustic middle ear implant device |
US9544700B2 (en) * | 2009-06-15 | 2017-01-10 | Earlens Corporation | Optically coupled active ossicular replacement prosthesis |
EP2443843A4 (en) | 2009-06-18 | 2013-12-04 | SoundBeam LLC | Eardrum implantable devices for hearing systems and methods |
WO2010148324A1 (en) * | 2009-06-18 | 2010-12-23 | SoundBeam LLC | Optically coupled cochlear implant systems and methods |
CN102598715B (en) | 2009-06-22 | 2015-08-05 | 伊尔莱茵斯公司 | optical coupling bone conduction device, system and method |
WO2011005500A2 (en) | 2009-06-22 | 2011-01-13 | SoundBeam LLC | Round window coupled hearing systems and methods |
WO2010151647A2 (en) * | 2009-06-24 | 2010-12-29 | SoundBeam LLC | Optically coupled cochlear actuator systems and methods |
WO2010151636A2 (en) | 2009-06-24 | 2010-12-29 | SoundBeam LLC | Optical cochlear stimulation devices and methods |
WO2011095229A1 (en) | 2010-02-08 | 2011-08-11 | Advanced Bionics Ag | Fully implantable hearing aid |
DE102010009453A1 (en) | 2010-02-26 | 2011-09-01 | Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. | Sound transducer for insertion in an ear |
US8594806B2 (en) | 2010-04-30 | 2013-11-26 | Cyberonics, Inc. | Recharging and communication lead for an implantable device |
DK3245990T3 (en) * | 2010-11-23 | 2019-08-19 | Nat Univ Ireland Maynooth | METHOD AND APPARATUS FOR SENSORY SUBSTITUTION |
EP3758394A1 (en) | 2010-12-20 | 2020-12-30 | Earlens Corporation | Anatomically customized ear canal hearing apparatus |
US9301066B2 (en) | 2011-10-06 | 2016-03-29 | Brain Basket, LLC | Auditory comprehension and audibility device |
JP6437915B2 (en) * | 2012-08-20 | 2018-12-12 | ベター ヒアリング エス.エー.エー.ケー. テクノロジーズ リミテッドBetter Hearing S.A.A.K. Technologies Ltd | Hearing aid |
US9343923B2 (en) | 2012-08-23 | 2016-05-17 | Cyberonics, Inc. | Implantable medical device with backscatter signal based communication |
US9935498B2 (en) | 2012-09-25 | 2018-04-03 | Cyberonics, Inc. | Communication efficiency with an implantable medical device using a circulator and a backscatter signal |
CN103784255A (en) * | 2012-10-29 | 2014-05-14 | 赵士星 | Hearing auxiliary system |
US10034103B2 (en) | 2014-03-18 | 2018-07-24 | Earlens Corporation | High fidelity and reduced feedback contact hearing apparatus and methods |
DK3169396T3 (en) | 2014-07-14 | 2021-06-28 | Earlens Corp | Sliding bias and peak limitation for optical hearing aids |
US9924276B2 (en) | 2014-11-26 | 2018-03-20 | Earlens Corporation | Adjustable venting for hearing instruments |
US10525265B2 (en) * | 2014-12-09 | 2020-01-07 | Cochlear Limited | Impulse noise management |
KR101648195B1 (en) * | 2015-05-19 | 2016-08-16 | 김형준 | Audio-type TENS therapy device and method |
EP3355801B1 (en) | 2015-10-02 | 2021-05-19 | Earlens Corporation | Drug delivery customized ear canal apparatus |
US10492010B2 (en) | 2015-12-30 | 2019-11-26 | Earlens Corporations | Damping in contact hearing systems |
US10178483B2 (en) | 2015-12-30 | 2019-01-08 | Earlens Corporation | Light based hearing systems, apparatus, and methods |
US11350226B2 (en) | 2015-12-30 | 2022-05-31 | Earlens Corporation | Charging protocol for rechargeable hearing systems |
US11071869B2 (en) | 2016-02-24 | 2021-07-27 | Cochlear Limited | Implantable device having removable portion |
EP3510796A4 (en) | 2016-09-09 | 2020-04-29 | Earlens Corporation | Contact hearing systems, apparatus and methods |
US11253193B2 (en) * | 2016-11-08 | 2022-02-22 | Cochlear Limited | Utilization of vocal acoustic biomarkers for assistive listening device utilization |
WO2018093733A1 (en) | 2016-11-15 | 2018-05-24 | Earlens Corporation | Improved impression procedure |
WO2019173470A1 (en) | 2018-03-07 | 2019-09-12 | Earlens Corporation | Contact hearing device and retention structure materials |
WO2019199680A1 (en) | 2018-04-09 | 2019-10-17 | Earlens Corporation | Dynamic filter |
Family Cites Families (50)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3557775A (en) | 1963-12-27 | 1971-01-26 | Jack Lawrence Mahoney | Method of implanting a hearing aid |
US3712962A (en) | 1971-04-05 | 1973-01-23 | J Epley | Implantable piezoelectric hearing aid |
US3764748A (en) * | 1972-05-19 | 1973-10-09 | J Branch | Implanted hearing aids |
US4352960A (en) | 1980-09-30 | 1982-10-05 | Baptist Medical Center Of Oklahoma, Inc. | Magnetic transcutaneous mount for external device of an associated implant |
US4441210A (en) | 1981-09-18 | 1984-04-03 | Hochmair Erwin S | Transcutaneous signal transmission system and methods |
US4729366A (en) | 1984-12-04 | 1988-03-08 | Medical Devices Group, Inc. | Implantable hearing aid and method of improving hearing |
US4593696A (en) | 1985-01-17 | 1986-06-10 | Hochmair Ingeborg | Auditory stimulation using CW and pulsed signals |
US4894728A (en) * | 1985-02-27 | 1990-01-16 | Goodman Robert M | Data acquisition and recording system |
EP0200321A3 (en) * | 1985-03-20 | 1987-03-11 | Ingeborg J. Hochmair | Transcutaneous signal transmission system |
US5015225A (en) | 1985-05-22 | 1991-05-14 | Xomed, Inc. | Implantable electromagnetic middle-ear bone-conduction hearing aid device |
US4947432B1 (en) * | 1986-02-03 | 1993-03-09 | Programmable hearing aid | |
US4989251A (en) * | 1988-05-10 | 1991-01-29 | Diaphon Development Ab | Hearing aid programming interface and method |
US4988333A (en) | 1988-09-09 | 1991-01-29 | Storz Instrument Company | Implantable middle ear hearing aid system and acoustic coupler therefor |
US5015224A (en) | 1988-10-17 | 1991-05-14 | Maniglia Anthony J | Partially implantable hearing aid device |
DE8815877U1 (en) | 1988-12-22 | 1989-04-27 | Junker, Franz, 7505 Ettlingen, De | |
DE3940632C1 (en) | 1989-06-02 | 1990-12-06 | Hortmann Gmbh, 7449 Neckartenzlingen, De | Hearing aid directly exciting inner ear - has microphone encapsulated for implantation in tympanic cavity or mastoid region |
US5271397A (en) | 1989-09-08 | 1993-12-21 | Cochlear Pty. Ltd. | Multi-peak speech processor |
US5095904A (en) | 1989-09-08 | 1992-03-17 | Cochlear Pty. Ltd. | Multi-peak speech procession |
US5603726A (en) | 1989-09-22 | 1997-02-18 | Alfred E. Mann Foundation For Scientific Research | Multichannel cochlear implant system including wearable speech processor |
DE4104359A1 (en) | 1991-02-13 | 1992-08-20 | Implex Gmbh | CHARGING SYSTEM FOR IMPLANTABLE HOERHILFEN AND TINNITUS MASKERS |
DE4104358A1 (en) | 1991-02-13 | 1992-08-20 | Implex Gmbh | IMPLANTABLE HOER DEVICE FOR EXCITING THE INNER EAR |
US5597380A (en) | 1991-07-02 | 1997-01-28 | Cochlear Ltd. | Spectral maxima sound processor |
EP0537385A1 (en) | 1991-10-14 | 1993-04-21 | DORN GmbH | Apparatus for tinnitus therapy |
DE4221866C2 (en) * | 1992-07-03 | 1994-06-23 | Guenter Hortmann | Hearing aid for stimulating the inner ear |
US5360388A (en) | 1992-10-09 | 1994-11-01 | The University Of Virginia Patents Foundation | Round window electromagnetic implantable hearing aid |
US5531787A (en) | 1993-01-25 | 1996-07-02 | Lesinski; S. George | Implantable auditory system with micromachined microsensor and microactuator |
US5624376A (en) | 1993-07-01 | 1997-04-29 | Symphonix Devices, Inc. | Implantable and external hearing systems having a floating mass transducer |
US5581747A (en) * | 1994-11-25 | 1996-12-03 | Starkey Labs., Inc. | Communication system for programmable devices employing a circuit shift register |
US5601617A (en) | 1995-04-26 | 1997-02-11 | Advanced Bionics Corporation | Multichannel cochlear prosthesis with flexible control of stimulus waveforms |
US5626629A (en) | 1995-05-31 | 1997-05-06 | Advanced Bionics Corporation | Programming of a speech processor for an implantable cochlear stimulator |
US5772575A (en) | 1995-09-22 | 1998-06-30 | S. George Lesinski | Implantable hearing aid |
WO1997013127A1 (en) * | 1995-09-29 | 1997-04-10 | International Business Machines Corporation | Mechanical signal processor based on micromechanical oscillators and intelligent acoustic detectors and systems based thereon |
AU711172B2 (en) * | 1995-11-13 | 1999-10-07 | Cochlear Limited | Implantable microphone for cochlear implants and the like |
US5795287A (en) | 1996-01-03 | 1998-08-18 | Symphonix Devices, Inc. | Tinnitus masker for direct drive hearing devices |
KR19990082641A (en) * | 1996-02-15 | 1999-11-25 | 알만드 피. 뉴커만스 | Improved biocensor transducer |
EP0891684B1 (en) | 1996-03-25 | 2008-11-12 | S. George Lesinski | Attaching of an implantable hearing aid microactuator |
US6161046A (en) * | 1996-04-09 | 2000-12-12 | Maniglia; Anthony J. | Totally implantable cochlear implant for improvement of partial and total sensorineural hearing loss |
US5881158A (en) * | 1996-05-24 | 1999-03-09 | United States Surgical Corporation | Microphones for an implantable hearing aid |
AU3960697A (en) | 1996-07-19 | 1998-02-10 | Armand P. Neukermans | Biocompatible, implantable hearing aid microactuator |
DE19638158C2 (en) | 1996-09-18 | 2000-08-31 | Implex Hear Tech Ag | Implantable microphone |
US5814095A (en) * | 1996-09-18 | 1998-09-29 | Implex Gmbh Spezialhorgerate | Implantable microphone and implantable hearing aids utilizing same |
DE19758573C2 (en) | 1997-11-26 | 2001-03-01 | Implex Hear Tech Ag | Fixation element for an implantable microphone |
DE19827898C1 (en) | 1998-06-23 | 1999-11-11 | Hans Leysieffer | Electrical energy supply for an implant, eg. a hearing aid |
US6368267B1 (en) * | 1998-10-14 | 2002-04-09 | Sound Techniques Systems, Llc | Stapedial-saccular strut and method |
DE19858398C1 (en) | 1998-12-17 | 2000-03-02 | Implex Hear Tech Ag | Tinnitus treatment implant comprises a gas-tight biocompatible electroacoustic transducer for implantation in a mastoid cavity |
US6473651B1 (en) * | 1999-03-02 | 2002-10-29 | Advanced Bionics Corporation | Fluid filled microphone balloon to be implanted in the middle ear |
DE19915846C1 (en) * | 1999-04-08 | 2000-08-31 | Implex Hear Tech Ag | Partially implantable system for rehabilitating hearing trouble includes a cordless telemetry device to transfer data between an implantable part, an external unit and an energy supply. |
US6259951B1 (en) * | 1999-05-14 | 2001-07-10 | Advanced Bionics Corporation | Implantable cochlear stimulator system incorporating combination electrode/transducer |
US6415186B1 (en) * | 2000-01-14 | 2002-07-02 | Advanced Bionics Corporation | Active feed forward power control loop |
US6496734B1 (en) * | 2000-04-24 | 2002-12-17 | Cochlear Limited | Auditory prosthesis with automated voice muting using the stapedius muscle reflex |
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2000
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EP1191815A2 (en) | 2002-03-27 |
DE50115855D1 (en) | 2011-06-01 |
EP1191815A3 (en) | 2009-10-21 |
DK1191815T3 (en) | 2011-07-18 |
US20020035309A1 (en) | 2002-03-21 |
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