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EP3087761B1 - Aide auditive insérable dans le conduit auditif et système d'aide auditive - Google Patents

Aide auditive insérable dans le conduit auditif et système d'aide auditive Download PDF

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Publication number
EP3087761B1
EP3087761B1 EP14815354.7A EP14815354A EP3087761B1 EP 3087761 B1 EP3087761 B1 EP 3087761B1 EP 14815354 A EP14815354 A EP 14815354A EP 3087761 B1 EP3087761 B1 EP 3087761B1
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EP
European Patent Office
Prior art keywords
hearing aid
actuator
signals
hearing
eardrum
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Active
Application number
EP14815354.7A
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German (de)
English (en)
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EP3087761A1 (fr
Inventor
Ernst Dalhoff
Hans-Peter Zenner
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Eberhard Karls Universitaet Tuebingen
Original Assignee
Eberhard Karls Universitaet Tuebingen
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Publication of EP3087761A1 publication Critical patent/EP3087761A1/fr
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Classifications

    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
    • H04R25/604—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers
    • H04R25/606—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers acting directly on the eardrum, the ossicles or the skull, e.g. mastoid, tooth, maxillary or mandibular bone, or mechanically stimulating the cochlea, e.g. at the oval window
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R17/00—Piezoelectric transducers; Electrostrictive transducers
    • 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
    • H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
    • H04R25/554—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired using a wireless connection, e.g. between microphone and amplifier or using Tcoils
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/025—In the ear hearing aids [ITE] hearing aids
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2460/00—Details of hearing devices, i.e. of ear- or headphones covered by H04R1/10 or H04R5/033 but not provided for in any of their subgroups, or of hearing aids covered by H04R25/00 but not provided for in any of its subgroups
    • H04R2460/09—Non-occlusive ear tips, i.e. leaving the ear canal open, for both custom and non-custom tips

Definitions

  • the present invention relates to a hearing aid insertable into the auditory canal of a patient, with an actuator which effects a mechanical stimulation of the eardrum.
  • Hearing loss is a serious societal problem, as in developed countries an average of about 10 to 20% of the population is affected. Hearing loss is in many cases not curable until today, causing a reduction in the quality of life. Implantable and / or usable hearing systems offer a way out here.
  • An acoustic transducer generates (amplified) sound waves, which in turn causes vibrations in the tympanic membrane (eardrum).
  • a telephone handset is a very simple example of an acoustic transducer.
  • the ear piece of a telephone handset converts e.g. Voice signals in vibrations of a loudspeaker membrane, which it had previously received by wire transmission.
  • the speaker in turn sets the tympanic membrane in vibration.
  • the DE 692 04 555 T2 describes an acoustic transducer.
  • the acoustic transducer receives its input signal from an infrared receiver.
  • the modulated for sound reproduction signals are here irradiated via IR radiation from outside the ear into the outer ear, where the IR receiver is located with the speaker for acoustic coupling to the eardrum.
  • An electromagnetic transducer is known. Such electromagnetic transducers are used in most conventional hearing implants. They convert (electro) magnetic fields containing modulated audio information into vibrations that are applied to the eardrum or parts of the middle ear.
  • the transducer usually a magnet, is displaced by the electromagnetic field to exert a vibratory motion, for example, on the eardrum or ossicles, whereby the user of such an electromagnetically driven system perceives sound.
  • This way of sound perception has some advantages over acoustically operated systems, especially in terms of quality, efficiency and in particular to a feedback common to all acoustic hearing systems.
  • the mechanical stimulation of the ossicles as an alternative to conventional hearing aids, which amplifies the sound pressure in the ear canal, examined in the hearing research, with both an excitation in the middle ear and the eardrum in question.
  • the mechanical excitation is at high required gain over the conventional acoustic excitation advantageous in terms of fidelity (distorsions).
  • the attachment of a miniature magnet on the eardrum has been proposed, which is designed as a point-wise acting actuator and engages the umbo or the central region of the eardrum.
  • the excitation of the magnet can be done with a coil outside or inside the ear canal; please refer DE 20 44 870 A1 ,
  • the US Pat. No. 7,867,160 B2 describes a variant of this hearing aid, in which a adapted to the shape of the outer ear supply module transmits signals by means of light to the hearing aid, which sits on the outside of the eardrum.
  • the hearing aid has a voltage applied to the umbo support structure and a bimorph structure, which serves the pointwise excitation of the eardrum.
  • an optical transmission path is only for eye implants ( DE 197 05 988 C2 ) and later also for middle ear implants; please refer EP 1 470 737 B1 and Goll et al., "Concept and evaluation of an endaurally insertable middle-ear implant” in Med Eng Phys 35 (103), 532-536 ,
  • the optical transmission has the advantage over the electromechanical transmission that the energy loss is usually hardly dependent on the distance and orientation between transmitter and receiver, and also in comparable Transmission ratios can be built much smaller. This plays a major role in hearing implants that are to be used completely (ie with a receiver) in the relatively narrow middle ear. In addition, the significant distance dependence results in unwanted signal modulation when the transmission path is not geometrically highly stable.
  • a problem of all hearing aids that do not close the auditory canal is an acoustic feedback of the amplified sound to the receiving microphone, which in iD.R. attached behind the ear.
  • This problem can be reduced in implants or eardrum lenses; for example, Perkins et al., supra, shows a feedback gain margin in the range of 3 kHz of 12 ⁇ 8 dB relative to a microphone in the ear canal.
  • a microphone in the ear canal has the eminently important advantage of so-called open supply, the directional information, which results inter alia from the individual head-related amplitude transfer function of the sound to maintain unadulterated.
  • the sound-damping element may be formed as an acoustic diaphragm, which has in several levels arranged one behind the other and in the circumferential direction twisted, cascaded lamellae.
  • the EP 2 362 686 A2 describes a sound transducer for generating sound vibrations, which is insertable into the ear and is implanted in particular in the middle ear.
  • the sound transducer has a carrier layer and a piezoelectric layer, whereby a deflection of this membrane structure according to the bimorph principle is reached, so that the membrane structure can be set via applied electrical control signals in vibration and thereby produces sound vibrations in the range between 2 Hz and 20,000 to 30,000 Hz.
  • the transducer is to be implanted in or in front of the round or oval window in the middle ear and deliver corresponding sound waves there.
  • the edge of the transducer would then be fixed at the transition between eardrum and ear canal.
  • the present invention seeks to further develop the hearing aid mentioned above in such a way that it allows a better, preferably low-feedback stimulation of the eardrum.
  • the actuator has an inner surface assigned to the eardrum and an outer surface assigned to the auditory canal and is designed as a flat disk actuator, preferably as a piezo disk actuator whose deformation stimulates the eardrum by planar deformation, wherein the flat disk actuator is adapted to overlie the greater part of the eardrum, and wherein the inner surface is formed such that it can be applied to the eardrum by adhesion and only by the prevailing adhesion forces between the eardrum and the actuator on the
  • the eardrum remains, so that due to the surface tension in the boundary layer between the inner surface of the actuator and the eardrum, the deformation is transmitted to the eardrum.
  • the invention thus provides in a simple way an improved hearing aid.
  • the stimulation of the eardrum now takes place in one aspect and not over an element, as it is known from the prior art, which can be considered approximately acting as a pointwise actor acting on Umbo or the central region of the eardrum.
  • the stimulation is carried out by the deformation of an element which rests on the larger part of the eardrum on this, and due to the surface tension in the Boundary layer between inner surface of the actuator and eardrum transmits the deformation to the eardrum.
  • the stimulation of the eardrum takes place according to the invention not by vibration of a self-deformable actuator but by planar "in-itself" deformation of the eardrum by means of a surface deformable actuator.
  • the actuator is adapted to be applied with the help of adhesive forces on the ear canal facing side of the eardrum surface.
  • the actuator is held on the eardrum itself, a fixation of its edge on the wall of the ear canal or any other mechanical abutment is not required.
  • This feature is used for easy and quick use of the hearing aid. To use the hearing aid, no invasive surgery is required. Either the attending physician or a technician can attach the hearing aid to the eardrum, which preferably neither adhesive or similar fixatives must be used.
  • the proximal end of the outer ear in the immediate vicinity of the eardrum does not have the body's own mechanism, foreign particles from the inside of the outer ear to the outside of the outer ear. If the hearing aid is properly placed on the eardrum, it will remain firmly in the desired location due to the prevailing adhesion forces between the eardrum and the actuator. Should it be necessary for the hearing aid to be replaced, this can be done simply by pulling it off the eardrum. As a rule, the eardrum is not injured. This exchange can be relatively quick and outpatient.
  • a hearing aid with a preferably lenticular, hollow structure is formed by attachment of a rigid, preferably curved diaphragm, on the outer surface of the actuator facing away from the eardrum.
  • This visor assumes the function of an acoustic shutter, but does not require cascaded elements, as it is from the above-mentioned DE 101 54 390A1 is known. Since the diaphragm only oscillates with the negligible amplitude of the outermost periphery of the eardrum, depending on the diameter, the feedback of the eardrum's vibration, which is typically amplified by 30-40 dB in the hearing aid application, is significantly reduced in the microphone of the hearing aid. This microphone can be located in the ear canal or behind the ear.
  • the diaphragm may consist of a rigid material, and be formed flat or curved.
  • the diaphragm can additionally serve as a carrier for microelectronic elements and circuits, and preferably carry a chip battery, which serves the electrical supply of the circuits.
  • the hearing aid has at least one first receiver for energy signals, which preferably comprises at least one optoelectronic sensor which converts light energy into electrical energy, wherein the at least one first receiver preferably further comprises a planar array of optoelectronic sensors.
  • the power supply of the hearing aid is wireless, wherein the optical transmission of energy provides the further advantage that the energy losses are low, because light rays can also be directed to the receiver in the ear canal.
  • the light beams can be introduced into the auditory canal via optical fibers or generated in a supply module arranged in the auditory canal, which under certain circumstances can also be removed and replaced by the patient himself.
  • the supply module for example, can be charged extracorporeally with electrical energy, which is then converted into optical energy during use and guided from the hearing aid located inside the auditory canal to the inside of the auditory canal, where it is seated on the eardrum, where it is again converted into electrical energy.
  • the optical energy transmission is also largely insensitive to misalignment between transmitter and receiver.
  • the hearing aid has at least one second receiver for hearing signals, which preferably comprises a microphone unit which receives acoustic signals as auditory signals and converts them into electrical control signals for the actuator.
  • the advantage here is that the transmission of the audio signals is wireless. If the audio signals are transmitted as acoustic signals to the microphone unit, only the energy has to be transmitted wirelessly to the hearing aid.
  • the supply unit then has to essentially provide only the required electrical energy, for example by means of a rechargeable energy store, and comprise a light transmitter for the optical energy transmission.
  • the light signals can be emitted, for example, in the near infrared range, for example at about 800 nm.
  • the microphone unit may comprise one or more Elekretmikrophone that can be produced in the required small dimensions with sufficient sound quality.
  • the diaphragm of the microphone unit is arranged on the auditory canal side next to or on the diaphragm, that is above the acoustic diaphragm formed by the diaphragm, according to the inventors despite the spatial proximity of the microphone and actuator a good shielding of the microphone is ensured before feedback signals ,
  • Another advantage is that the microphone sits close to the eardrum, so that the recording of the acoustic signals by the hearing aid takes place there, where the healthy ear receives the acoustic signals with the eardrum.
  • the natural directional characteristic of the ear canal is thus still used despite the hearing aid, so that in particular the orientation hearing is still possible almost undisturbed.
  • the diaphragm and the surface coupling of the disc actuator to the eardrum make it possible in each case, but especially in their combination, that a microphone unit can be arranged directly on the inserted into the ear canal eardrum hearing aid, without causing a disturbing feedback on the eardrum transmits vibrations to the microphone comes.
  • the microphone unit has a membrane on which the at least one first receiver is at least partially arranged.
  • thin-film photodiodes can be used as the first receiver, which are arranged on the membrane of the microphone or formed as part of the membrane.
  • a spacer ring is arranged between the planar actuator and the diaphragm, preferably the diaphragm is designed to be rigid compared to the actuator, more preferably at least one ventilation opening leading into the cavity is provided in the diaphragm, which preferably has a diameter, which allows an exchange of air between the ear canal and the cavity only for low frequencies of preferably below 20 Hz, wherein the diameter of the vent opening is more preferably between 0.01 and 0, 1 mm.
  • disc actuator, diaphragm and spacer ring forms a closed air volume for acoustic frequencies.
  • tiny vent allows a low-frequency air exchange between the interior of the cavity and the air in the ear canal to avoid static pressure differences.
  • the hearing aid has a diameter between 4 and 10 mm, so that a large part of the surface of a tympanic membrane of a patient is available both for the stimulation and for the reception of the energy signals and the membrane of the microphone unit.
  • the total thickness of the hearing aid measured transversely to its diameter, in one embodiment is about 2 mm, wherein the proportion of the diaphragm at this thickness is not more than about 0.2 mm.
  • the inner surface of the actuator is preferably adapted to the shape of the eardrum in such a way that the inner surface can be attached to the eardrum centrically to the umbo.
  • the hearing aid comprises a control unit which converts energy signals of at least one first receiver and audio signals of at least one second receiver into control signals for the actuator.
  • This control unit can be arranged on the rigid diaphragm.
  • this control unit serves to provide the required conversion of the electrical output signals of the microphone unit into the drive signals for the disk actuator and the required electrical energy.
  • the control unit may also be carried out a signal processing, in which, for example, the pitches of the received acoustic signals changed and / or certain frequency ranges are amplified differently to meet the individual needs of the patient.
  • the present invention also relates to a hearing aid system having a supply module and the new hearing aid can be introduced into the ear canal of a patient, wherein the hearing aid a first receiver for energy signals and at least a second receiver are arranged for auditory signals, and wherein the Supply module has at least one transmitter for energy signals, which preferably comprises a light emitter, which is preferably selected from the group containing light guides, lasers, LEDs and OLEDs.
  • the supply module is used here to supply the hearing aid with electrical energy and is preferably used even in the ear canal, on the inner shape of which it is adapted. But it can also be arranged behind the ear, in which case the light radiation is conducted via optical fibers into the ear canal.
  • the supply module can also have a light transmitter, preferably an LED or a laser for auditory signals, in which case no microphone unit but other light receivers are arranged on the hearing aid, which convert the optically transmitted auditory signals into electrical signals, which are then used for the excitation of the actuator.
  • a light transmitter preferably an LED or a laser for auditory signals, in which case no microphone unit but other light receivers are arranged on the hearing aid, which convert the optically transmitted auditory signals into electrical signals, which are then used for the excitation of the actuator.
  • FIG. 1 For example, a human ear 10 of a patient P is shown schematically and partially in section. Sounds (sounds and noises) are bundled through the pinna 11 and directed along the ear canal (outer ear) 12 in the direction of the eardrum 14. The sound impinges on the eardrum 14 and is transmitted to the cochlea 15 via a system of bones (ossicular chain) 16 which serve as levers for amplification and acoustic matching transformation to a plunger or diaphragm 17, respectively. called the "oval window", to allow.
  • bones ossicular chain
  • the cochlea 15 is a spirally wound tube similar to a snail shell, about 35 mm long in the angled condition, divided over most of its entire length by a partition called the "basilar membrane".
  • a lower chamber of the cochlea is called “Scala tympani”, and an upper chamber is called “Scala vestibuli”.
  • the cochlea 15 is filled with a fluid (perilymph) having a viscosity approximately equal to the viscosity of water.
  • the Scala tympani is equipped with another membrane 18, called a "round window", which serves to accommodate the displacement of the fluid when the oval window 17 is deflected.
  • the basilar membrane When the oval window 17 is actuated acoustically via the auditory ossicles 16, the basilar membrane is correspondingly displaced and vibrates due to the movement of the fluid in the cochlea 15.
  • the displacement of the basilar membrane stimulates hair cells (sensory cells) which have a special structure the basilar membrane lie (not shown). Movements of these sensory hairs produce electrical discharges into fibers of the auditory nerve 19 through the mediation of spiral ganglion cells positioned in the modiolus or modiolar wall.
  • the human ear 10 is roughly subdivided into three regions, namely the outer ear with the ear canal 12, the middle ear 21 and the inner ear 22.
  • Pressure of the ossicles 16 on the oval window 17 vibrates the scala vestibuli up to the top of the cochlea 15 and down a screw hole (not shown) along the scala tympani back to the round window 18, which is the registered pressure by extension or vibration can compensate.
  • Fig. 2 shows an inserted into the ear 10 embodiment of a hearing aid system 24 according to the present invention.
  • the hearing aid system 24 comprises a supply module 25 arranged in the auditory canal 12 and adapted thereto, as well as a hearing aid 26 which is mounted on the eardrum 14 exclusively by adhesion forces.
  • the hearing aid 26 is mounted on the side of the eardrum 14, which is directed to the ear canal 12.
  • the supply module 25 can also be removed by the patient at any time, for example, to clean it or to charge electrical energy storage, the hearing aid 26 remains permanently in the ear canal 12, but can also be removed non-invasively and used again.
  • the supply module 25 supplies the hearing aid 26 via an optical connection 27 with electrical energy.
  • About the optical connection 27 can also Listening signals are transmitted that represent the sound to be reproduced.
  • the optical connection 27 can therefore be used both for signal transmission and for energy transmission, preferably simultaneously.
  • the sound passes from the outside into the auricle, is guided via the ear canal 12 to the eardrum 14 and forwarded from there via the ossicular chain 16 to the inner ear 22, which is shown here in the shape of a snail.
  • the hearing aid 26 is "glued" to the side of the eardrum 14 which faces the auditory canal 12.
  • the ossicular chain 16 is therefore also used for signal transmission from the eardrum 14 to the inner ear 22.
  • the transmission of auditory signals to the hearing aid 26 is not via the optical connection 27, but the acoustic signals 28, ie sound in the form of sounds and noises, go directly to the hearing aid 26, where it from a microphone unit 29th be caught and converted into electrical control signals 30, which drive an actuator 31, which rests with its inner surface 32 directly to the eardrum 14 and this deformed according to the sound, so mechanically stimulated.
  • an array 33 of optoelectronic sensors 34 is arranged facing the supply module 25, which receives energy signals in the form of light beams 35 via the optical connection 27, which are emitted by a light transmitter 36, which is arranged on the supply module 25.
  • LEDs are used as the light transmitter 36, which emit light beams 35 in the wavelength range of 800 nm.
  • the optoelectronic sensors 34 convert the light beams 35 into electrical energy used in the hearing aid 26 to mechanically stimulate the eardrum 14.
  • a storage element 37 for electrical energy is present, which supplies the light emitter 36 with the required energy.
  • the storage element 37 is inductively supplied either in situ via electromagnetic radiation or extracorporeally in a charging station with electrical energy.
  • the hearing aid 26 has a control unit 38, which activates the actuator 31 via the control signals 30 by means of the electrical energy provided by the array 33, which can be temporarily stored in a memory element 39 provided if necessary, and in dependence on the output signals of the microphone unit 29.
  • Fig. 4 the hearing aid 26 is shown in an enlarged and schematically illustrated embodiment.
  • the hearing aid 26 is arranged inside the ear canal 12 directly on the eardrum 14, which delimits the ear canal 12 from the middle ear 21.
  • the actuator 31 is a piezo disc actuator whose inner surface 32 rests centrally on the umbo 41 of the drumhead 14 and flat against the eardrum 14 by adhesion. With its outer surface 42, the actuator 31 on a in the direction of the ear canal 12 in the example shown outwardly curved aperture plate 43, with the edge 44 of the actuator 31 is connected at its edge 45 via a spacer ring 46, the hearing aid 26 has an outer diameter 47 a from 4 to 8 mm and a thickness 47b of about 2 mm.
  • Actuator 31, diaphragm 43 and spacer 46 limit in this example a lenticular cavity 48 which is connected via a small vent opening 49 in the diaphragm 43 with the ear canal 12.
  • the vent 49 has such a small diameter 50 (about 0.01 mm) that it allows air exchange between the ear canal 12 and the cavity 48 only for low frequencies, preferably below 20 Hz.
  • the actuator 31 has a membrane structure 51 comprising an inner carrier layer 52 made of silicon, an outer layer 53 of piezo material arranged on the carrier layer 52, an electrode layer 54 between carrier layer 52 and layer 53, and an electrode layer 55 on the inner surface 32.
  • an electrical voltage can be applied to the layer 53, which, depending on its polarity, results in the membrane structure 51 being directed outwards, ie in FIG Fig. 4 to the right, or swings inward, ie into the cavity 48, whereby the eardrum 14 is deformed correspondingly flat.
  • an AC voltage is applied to the electrode layers 54, 55, the diaphragm structure 51 is vibrated.
  • the piezo disk actuator may have a segmented or non-segmented membrane structure 51.
  • Such a piezo disk actuator is in principle from the aforementioned EP 2 362 686 A2 known.
  • the above-mentioned EP 2 362 686 A2 directed.
  • the diaphragm 43 is sufficiently rigid that the diaphragm 43 is not deformed in vibrations of the diaphragm structure 51 in the acoustic frequency range (20 to 30,000 Hz) caused by pressure changes in the cavity 48.
  • the vent 49 allows a low frequency air exchange between the cavity 48 and the air in the ear canal 12 to avoid static pressure differences.
  • the diaphragm 43 carries on its the outer tube 56 facing the ear canal 12, the array 33, the control unit 38 and the microphone unit 29, as shown schematically and not to scale Fig. 5 is shown, in which the diaphragm 43 is enlarged and shown in section.
  • the microphone unit 29 is embodied as an electret microphone and comprises a microphone converter 57 arranged on the outside 56, which converts vibrations of a diaphragm 58 caused by the acoustic signals 28 into electrical signals.
  • the array 33 of optoelectronic sensors 34 is arranged on the membrane 58. In this way, the entire surface of the diaphragm 58 stands both for Recording of the acoustic signals 28 as well as for the reception of the light beams 35 available, which not only ensures high sensitivity of the electret microphone but also for a position insensitivity of the optical energy transmission path 27.
  • 34 thin-film photodiodes can be used as sensors, as in the aforementioned EP 0 696 907 B1 are described. For further details, the above-mentioned EP 0 696 907 B1 directed.

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  • Engineering & Computer Science (AREA)
  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Neurosurgery (AREA)
  • Prostheses (AREA)
  • Measuring And Recording Apparatus For Diagnosis (AREA)

Claims (15)

  1. Aide auditive (26) pouvant être introduite dans le conduit auditif (12) d'un patient, comprenant un actionneur (31) qui provoque une stimulation mécanique du tympan (14),
    l'actionneur (31) possédant une surface intérieure (32) associée au tympan (14) et une surface extérieure (42) associée au conduit auditif (12) et étant réalisé sous la forme d'un actionneur à disque plat dont la déformation stimule le tympan (14) par une déformation à plat, l'actionneur à disque plat étant configuré pour reposer sur le tympan (14) au-dessus de la plus grande partie de celui-ci et la surface intérieure étant configurée de telle sorte qu'elle peut être appliquée à plat par adhérence contre le tympan (14) et demeure sur le tympan uniquement par les forces d'adhérence régnant entre le tympan (14) et l'actionneur (31), de sorte que la déformation est transmise au tympan (14) du fait de la tension superficielle dans la couche d'interface entre la surface intérieure de l'actionneur (31) et le tympan (14).
  2. Aide auditive selon la revendication 1, caractérisée en ce qu'un disque obturateur (43) est disposé sur l'actionneur (31) à l'écart de la surface extérieure (42), lequel délimite un espace creux (48) avec la surface extérieure (42).
  3. Aide auditive selon l'une des revendications 1 et 2, caractérisée en ce qu'elle comprend au moins un premier récepteur (33, 34) pour des signaux d'énergie (35).
  4. Aide auditive selon l'une des revendications 1 à 3, caractérisée en ce qu'elle comprend au moins un deuxième récepteur (29) pour des signaux auditifs (28).
  5. Aide auditive selon la revendication 4, caractérisée en ce que l'au moins un deuxième récepteur (29) comporte une unité de microphone (29) qui reçoit, en tant que signaux auditifs, des signaux acoustiques (28) et les convertit en signaux de commande électriques (30) pour l'actionneur (31).
  6. Aide auditive selon la revendication 5 et la revendication 3, caractérisée en ce que l'unité de microphone (29) possède une membrane (58) sur laquelle est disposé au moins en partie l'au moins un premier récepteur (33, 34).
  7. Aide auditive selon l'une des revendications 2 à 6, caractérisée en ce qu'une bague d'écartement (46) est disposée entre l'actionneur (31) plat et le disque obturateur (43).
  8. Aide auditive selon l'une des revendications 2 à 7, caractérisée en ce qu'au moins une ouverture de purge d'air (49) menant dans l'espace creux (48) se trouve dans le disque obturateur (43).
  9. Aide auditive selon la revendication 8, caractérisée en ce que l'ouverture de purge d'air (49) présente un diamètre (50) qui ne rend possible un échange d'air entre le conduit auditif (12) et l'espace creux (48) que pour les basses fréquences.
  10. Aide auditive selon la revendication 9, caractérisée en ce que le diamètre (50) de l'ouverture de purge d'air (49) est compris entre 0,01 et 0,1 mm.
  11. Aide auditive selon l'une des revendications 1 à 10, caractérisée en ce qu'elle présente un diamètre (47a) qui est compris entre 4 et 10 mm.
  12. Aide auditive selon l'une des revendications 1 à 11, caractérisée en ce que la surface intérieure (32) de l'actionneur (31) est adaptée à la forme du tympan (14) de telle sorte que la surface intérieure (32) peut être jointe contre le tympan (14) en étant centrée par rapport à l'ombilic (41).
  13. Aide auditive selon l'une des revendications 1 à 12, caractérisée en ce qu'elle comprend une unité de commande (38) qui convertit des signaux d'énergie (35) d'au moins un premier récepteur (33, 34) et des signaux auditifs (28) d'au moins un deuxième récepteur (29) en signaux de commande (30) pour l'actionneur (31).
  14. Système d'aide auditive, qui possède un module d'alimentation (25) et une aide auditive (26) pouvant être introduite dans le conduit auditif (12) d'un patient, un premier récepteur (33, 34) pour des signaux d'énergie (35) et au moins un deuxième récepteur (29) pour des signaux auditifs (28) étant disposés au niveau de l'aide auditive (26), et le module d'alimentation (25) possédant au moins un émetteur (36) pour des signaux d'énergie (35),
    caractérisé en ce que l'aide auditive (26) est l'aide auditive (26) selon l'une des revendications 1 à 13.
  15. Système d'aide auditive selon la revendication 14, caractérisé en ce que le module d'alimentation (25) est réalisé sous la forme d'une unité qui peut être introduite dans le conduit auditif (12) du patient.
EP14815354.7A 2013-12-23 2014-12-18 Aide auditive insérable dans le conduit auditif et système d'aide auditive Active EP3087761B1 (fr)

Applications Claiming Priority (2)

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DE102013114771.2A DE102013114771B4 (de) 2013-12-23 2013-12-23 In den Gehörgang einbringbare Hörhilfe und Hörhilfe-System
PCT/EP2014/078440 WO2015097056A1 (fr) 2013-12-23 2014-12-18 Aide auditive insérable dans le conduit auditif et système d'aide auditive

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EP (1) EP3087761B1 (fr)
CA (1) CA2934915C (fr)
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US10616699B2 (en) 2020-04-07
DE102013114771A1 (de) 2015-06-25
EP3087761A1 (fr) 2016-11-02
US20190158966A1 (en) 2019-05-23
ES2769599T3 (es) 2020-06-26
US20160323680A1 (en) 2016-11-03
CA2934915C (fr) 2021-08-31
US10219087B2 (en) 2019-02-26
WO2015097056A1 (fr) 2015-07-02
CA2934915A1 (fr) 2015-07-02
DK3087761T3 (da) 2020-01-20
DE102013114771B4 (de) 2018-06-28

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