EP3373600B1 - Dispositif d'aide auditive pour compensation des acouphènes - Google Patents

Dispositif d'aide auditive pour compensation des acouphènes Download PDF

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Publication number
EP3373600B1
EP3373600B1 EP18152456.2A EP18152456A EP3373600B1 EP 3373600 B1 EP3373600 B1 EP 3373600B1 EP 18152456 A EP18152456 A EP 18152456A EP 3373600 B1 EP3373600 B1 EP 3373600B1
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EP
European Patent Office
Prior art keywords
signal
tinnitus
acoustic
user
hearing aid
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
EP18152456.2A
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German (de)
English (en)
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EP3373600A1 (fr
Inventor
Mirko Arnold
Stefan Petrausch
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.)
Sivantos Pte Ltd
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Sivantos Pte Ltd
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Publication date
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Publication of EP3373600A1 publication Critical patent/EP3373600A1/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
    • H04R25/75—Electric tinnitus maskers providing an auditory perception
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
    • 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
    • H04R2460/01—Hearing devices using active noise cancellation
    • 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 invention relates to a hearing aid device, in particular a tinnitus therapy device, with a microphone and with a receiver which can be introduced into an auditory canal of a user or is at least partially arranged in the auditory canal.
  • Hearing aid devices are portable hearing aids that are used to care for the hard of hearing or the hearing impaired.
  • different designs of hearing aid devices such as behind-the-ear hearing aids (BTE) and hearing aids with an external receiver (RIC: receiver in the canal) and in-the-ear hearing aids (ITE) for
  • BTE behind-the-ear hearing aids
  • RIC receiver in the canal
  • ITE in-the-ear hearing aids
  • concha hearing aids or canal hearing aids ITE: In-The-Ear
  • CIC Completely-In-Channel
  • IIC Invisible-In-The-Channel
  • the hearing aids listed by way of example are worn on the outer ear or in the auditory canal of a hearing aid device user.
  • bone conduction hearing aids, implantable or vibrotactile hearing aids are also available on the market. The damaged hearing is stimulated either mechanically or electrically.
  • Such hearing aids have, in principle, an input transducer, an amplifier and an output transducer as essential components.
  • the input transducer is usually an acousto-electrical transducer, such as a microphone, and / or an electromagnetic receiver, for example an induction coil or a (radio frequency, RF) antenna.
  • the output transducer is usually as an electro-acoustic transducer, for example as a miniature loudspeaker (receiver), or as an electromechanical transducer, such as a bone conduction receiver, realized.
  • the amplifier is usually integrated in a signal processing device. The energy is usually supplied by a battery or a rechargeable accumulator.
  • Severe hearing loss as hearing impairment often triggers a neuroplastic reorganization of the central auditory system in the brain of the person concerned, and is therefore often a trigger and a cause of (chronic) tinnitus.
  • Tinnitus or ringing in the ears is generally understood to mean all types of head or ear noises that are not caused by acoustic signals from the environment that are introduced into the ear. A distinction is made between what is known as “subjective tinnitus” and what is known as “objective tinnitus”.
  • An objective or physical tinnitus is caused by a sound source in the body, especially in the inner ear, of the person affected.
  • the acoustic emissions (emissions) of this sound source into the ear canal can be measured as spontaneous otoacoustic emissions (SOAE).
  • SOAE spontaneous otoacoustic emissions
  • a subjective tinnitus is only perceptible to the person concerned and is mostly caused by a misdirected nerve activity in auditory and other parts of the brain, which is caused, for example, by the neuroplastic reorganization of the central auditory system described above.
  • tinnitus Although tinnitus is not dangerous, it is a major burden for many people affected. Chronic tinnitus, in particular, often leads to severe psychological problems and thus sometimes has a negative effect on the professional and social life of the person concerned. Furthermore, for example, concentration is disturbed and problems falling asleep are caused.
  • intoxicating devices tinnitus noiser, audio stimulator, tinnitus control instrument, tinnitus masker
  • the patient is offered a quiet, less disruptive noise as an acoustic signal with the aid of a tinnitus therapy device similar to a hearing aid device, a so-called noiser or masker.
  • tinnitus therapy devices are usually integrated as an additional function in hearing aids or hearing aid devices.
  • the acoustic signal is generated, for example, with a signal frequency which corresponds approximately to the perceived tinnitus frequency and is thus intended to cover (“mask”) the tinnitus.
  • a hearing aid device in which an acoustic output signal is generated in which one or more tinnitus frequencies of the user are suppressed.
  • This enables a neuroplastic reorganization of the patient's central auditory system, which reverses the maladaptive neuroplastic reorganization of the patient's central auditory system that causes tinnitus.
  • a tinnitus masking signal is generated in which the tinnitus frequency (s) is filtered out (suppressed) by means of a notch filter or a bandpass filter.
  • a hearing aid device as a tinnitus therapy device.
  • the known hearing aid device is designed for therapy of objective tinnitus.
  • the generated sound of the otoacoustic emission is recorded by means of a microphone.
  • a compensation or anti-sound signal is generated by means of a receiver in the ear canal, so that the otoacoustic emissions of objective tinnitus are suppressed.
  • a device for suppressing tinnitus is disclosed. This is used to measure the sound pressure due to the tinnitus in the ear canal. Furthermore, a second sound pressure is output with the opposite phase to the tinnitus sound pressure, but the same frequency and amplitude, so that a resulting total sound pressure is lower than the tinnitus sound pressure.
  • a hearing aid which is designed to generate sound waves.
  • the sound waves are emitted as sinusoidal vibrations or tones with a frequency that is the same as that of tinnitus, whereby the tinnitus can be eliminated by superimposing in phase opposition, but should not be fed to the ear as a vibration in the audio frequency range.
  • the invention is based on the object of specifying a particularly suitable hearing aid device, in particular for tinnitus therapy.
  • the object is achieved according to the invention with the features of claim 1.
  • Advantageous refinements and developments are the subject of the sub-claim.
  • the hearing aid device comprises a microphone and a receiver, which is at least partially arranged in an (outer) auditory canal of a user or can be inserted (inserted) into the auditory canal.
  • the receiver is intended and set up for insertion into the ear canal of a user.
  • ANR Active Noise Reduction
  • ANC Active Noise Cancellation
  • active sound compensation is provided to reduce the sensation of tinnitus, in which the aim is to erase or at least suppress or attenuate the or each tinnitus frequency by additional radiation of the acoustic compensation signal by the listener by superimposing the compensation signal with the acoustic ambient signal in the auditory canal.
  • the listener emits an acoustic compensation signal which, when superimposed on the ambient signal in the user's auditory canal, generates a resulting overall signal in which the or each tinnitus frequency of the user is suppressed or at least reduced.
  • frequencies with frequency values below 2 kHz (kilohertz) can be effectively attenuated.
  • the hearing aid device is designed to suppress or reduce a perceived subjective tinnitus (non-physical tinnitus).
  • a perceived subjective tinnitus non-physical tinnitus
  • the or each tinnitus frequency is a subjectively perceived tinnitus frequency of the person concerned.
  • the subject's subjective tinnitus frequencies are therefore not caused by a measurable sound source.
  • the term tinnitus is to be understood in particular as a subjective tinnitus
  • the term tinnitus frequency is to be understood in particular as a corresponding (subjective) tinnitus frequency of such a subjective tinnitus.
  • the active sound compensation does not take place by means of a compensation signal for an otoacoustic emission of an objective tinnitus. Rather, the compensation signal suppresses or reduces the or each (subjective) tinnitus frequency in an ambient signal coming from the outside to the ear, so that a neuroplastic reorganization of the central auditory system of the person concerned is made possible.
  • the user's auditory canal is thus not sound-blocking closed by means of the hearing aid device, so that in addition to the compensation signal generated by the listener, the acoustic ambient signal also penetrates the auditory canal.
  • the occlusion effect is thus essentially completely avoided. This is particularly advantageous for users who are not or only slightly impaired of hearing, since it enables a more natural sound image of the environment.
  • the acoustic compensation signal or the anti-noise is generated as a phase-inverted acoustic signal.
  • the anti-sound is generated in such a way that it corresponds to a sound corresponding to the or each tinnitus frequency in the ambient signal with as exactly the opposite polarity as possible. This enables reliable cancellation or suppression of the corresponding frequency ranges in the perceived ambient signal in the auditory canal.
  • the hearing aid device is designed in particular as a tinnitus therapy device.
  • the hearing aid device is equipped with a microphone for receiving an acoustic ambient signal and converting this ambient signal into an electrical input signal, and with a signal processing device for processing the electrical input signal into an electrical output signal, as well as with a receiver, which is at least partially arranged in an ear canal of a user, for converting the electrical input signal Output signal executed in an acoustic compensation signal.
  • the acoustic compensation signal is used for active sound compensation at the or each tinnitus frequency of the user.
  • an acoustic ambient signal is recorded by the microphone, which is analyzed as an electrical input signal by the signal processing device.
  • the signal processing device processes the electrical input signal into an electrical output signal with which the acoustic compensation signal is generated.
  • the acoustic compensation signal generated by the listener superimposes or interferes with the acoustic ambient signal in the ear canal of the user in such a way that the sound pressure occurring at the eardrum of the user is reduced or completely suppressed at the or each tinnitus frequency.
  • the remaining sound spectrum or frequency spectrum of the acoustic ambient signal is essentially not changed, so that a high sound quality is guaranteed for the user.
  • the or each tinnitus frequency of the user is stored in a memory of the signal processing device.
  • To record and determine the or each tinnitus frequency it is determined at which frequency or at which frequencies the user perceives acoustic signals which are not caused by acoustic signals entering the ear from outside (ambient signals). This recording takes place, for example, at a doctor or a hearing aid acoustician.
  • the or each recorded tinnitus frequency is then stored in the memory of the signal processing device.
  • the signal processing device uses the or each stored tinnitus frequency for processing the input signal.
  • a suitable compensation signal for canceling or suppressing the tinnitus frequencies can always be generated.
  • the signal processing device preferably also takes into account the transmission path within the hearing aid device, including the resulting phase differences between the ambient signal and the compensation signal to be generated.
  • a model of the acoustic transmission path of the hearing aid device it is possible, for example, for a model of the acoustic transmission path of the hearing aid device to be stored in the memory.
  • the microphone and the receiver are preferably arranged as close to one another as possible, so that any signal delays and phase differences that occur are reduced as far as possible.
  • the signal processing device preferably has a controller (that is to say a control device).
  • the controller is generally set up - in terms of program and / or circuitry - to operate the hearing device.
  • the controller is thus set up in particular to use the received input signal and the stored tinnitus frequencies and preferably with the aid of a model of the transfer function of the hearing aid device to generate an electronic output signal by setting the filter means, which produces an acoustic compensation signal for the listener for active sound compensation of the tinnitus frequencies in the ambient signal .
  • the controller is at least essentially formed by a microcontroller with a processor and a data memory, in which the functionality for operating the hearing device is implemented in the form of operating software (firmware), so that the operation of the hearing device - possibly in interaction with a user - is carried out automatically when the operating software is executed in the microcontroller.
  • operating software firmware
  • the controller is alternatively also formed by programmable electronic components, for example an application-specific integrated circuit (ASIC) in which the functionality for operating the hearing apparatus is implemented using circuitry.
  • ASIC application-specific integrated circuit
  • the controller is designed in particular to also effectively suppress tinnitus frequencies with frequency values greater than 2 kHz.
  • tinnitus frequencies with frequency values greater than 2 kHz.
  • a significant hearing loss in the patient in this frequency range so that even with an open, i.e. not sound-blocking, auditory canal, a significant attenuation of the tinnitus frequencies is already achieved.
  • acoustic filter means which acoustically attenuate in particular frequencies greater than 2 kHz.
  • the filter means are designed, for example, as electronic filters, in particular notch filters (notch filters).
  • active sound compensation or anti-noise is used in particular to dampen tinnitus frequencies less than approximately 2 kHz, with the filter means for acoustic damping of the tinnitus frequencies of the ambient signal being provided for frequencies greater than approximately 2 kHz.
  • This enables effective suppression or attenuation of one or more tinnitus frequencies of the user essentially over the entire (audible) frequency range.
  • FIGURE shows, in a schematic and simplified representation, a tinnitus therapy device worn on an ear of a user, with a microphone and with an earpiece, and with a signal processing device designed for active sound compensation.
  • the figure shows a hearing aid device designed as a tinnitus therapy device 2.
  • the tinnitus therapy device 2 is worn on an ear 4 of a tinnitus-affected user during operation.
  • the tinnitus therapy device 2 comprises a microphone 6 as an acousto-electrical transducer and a receiver 8 as an electro-acoustic transducer as well as a signal processing device 10, which is designed for active sound compensation of one or more tinnitus frequencies.
  • the microphone 6 is arranged at an input 12 of an (outer) auditory canal 14 of the ear 4. However, it is also conceivable for the microphone 6 to be arranged at least partially within the auditory canal 14. However, the earpiece 8 is always positioned further inside or deeper in the auditory canal 14 than the microphone 6. The auditory canal 14 extends from the entrance 12 to an eardrum 16 of the user.
  • the or each tinnitus frequency of the user is stored in a memory 18 of the signal processing device 10.
  • an acoustic ambient signal 20 is actively sound-compensated in such a way that the or each tinnitus frequency stored in the memory 18 is suppressed or reduced.
  • the tinnitus therapy device 2 is designed to be open, which means that the entrance 12 of the auditory canal 14 is not (completely) acoustically blocked by the tinnitus therapy device 2.
  • the acoustic ambient signal 20 reaches the auditory canal 14.
  • the ambient signal 20 continues to be received by the microphone 6 and converted into an electrical input signal 22.
  • the electrical input signal 22 is fed to the signal processing device 10, which processes it into an electrical output signal 24.
  • the electrical output signal 24 is fed to the earpiece 8, which emits it as an acoustic compensation signal (anti-noise) 26 into the ear canal 14.
  • the acoustic ambient signal 20 and the acoustic compensation signal 26 superimpose or interfere with one another to form a resulting overall signal 28, which has a reduced sound pressure at the eardrum 16 in the frequency range of the or each tinnitus frequency.
  • the acoustic compensation signal 26 is generated here as a phase-inverted acoustic signal of the acoustic ambient signal 20. This means that the acoustic compensation signal 26 corresponds, at least in the frequency range of the or each tinnitus frequency, to a sound of the acoustic ambient signal 20 with as exactly the opposite polarity as possible.
  • the acoustic ambient signal 20 is recorded with the microphone 6.
  • the signal processing device 10 uses the stored tinnitus frequency (s) and a model of an acoustic transfer function of the tinnitus therapy device 2 stored in the memory 18 to calculate the signal component of the ambient signal 20 that would still remain on the eardrum 16. For this signal component, the opposite polarity acoustic compensation signal 26 is then generated in the earpiece 8 for compensation.
  • the tinnitus therapy device 2 further comprises filter means, for example in the form of electronic notch filters (notch filters) 30, for acoustic damping in particular of tinnitus frequencies greater than 2 kHz.
  • filter means for example in the form of electronic notch filters (notch filters) 30, for acoustic damping in particular of tinnitus frequencies greater than 2 kHz.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Soundproofing, Sound Blocking, And Sound Damping (AREA)
  • Headphones And Earphones (AREA)

Claims (2)

  1. Appareil d'aide auditif (2), en particulier appareil de traitement des acouphènes,
    - avec un microphone (6) pour recevoir un signal acoustique d'environnement (20) et convertir ce signal d'environnement (20) en un signal d'entrée électrique (22),
    - avec un dispositif de traitement de signal (10) pour traiter le signal d'entrée électrique (22) en un signal de sortie électrique (24), dans lequel une ou plusieurs fréquences d'acouphènes de l'utilisateur est/sont stockée(s) dans une mémoire (18) du dispositif de traitement de signal (10), et
    - avec un récepteur (8) pouvant être inséré au moins partiellement dans un canal auditif (14) d'un utilisateur pour convertir le signal de sortie électrique (24) en un signal de compensation acoustique (26),
    caractérisé en ce,
    que le dispositif de traitement de signal (10) utilise la ou chaque fréquence d'acouphène mémorisée pour traiter le signal d'entrée (22), de sorte que le signal de compensation acoustique (26) émis au moyen du récepteur (8) dans la plage de la ou de chaque fréquence d'acouphène de l'utilisateur est inversé en phase de cette manière que le signal de compensation (26) produit dans le canal auditif de l'utilisateur un signal global résultant (28) lors d'une superposition avec le signal ambiant (20), dans lequel le niveau de pression acoustique du signal global (28) dans la plage de la ou de chaque fréquence d'acouphène de l'utilisateur est supprimé ou au moins réduit.
  2. Appareil d'aide auditif (2) selon la revendication 1,
    caractérisé en ce
    qu'un modèle d'une fonction de transfert de l'appareil d'aide auditif (2) est stockée dans la mémoire (18) du dispositif de traitement de signal (10), le dispositif de traitement de signal (10) calculant, au moyen du modèle et au moyen de la ou de chaque fréquence d'acouphène stockée dans la mémoire, la composante du signal ambiant (20), qui resterait sur le tympan (16) de l'utilisateur sans le signal de compensation (26), afin de générer le signal de compensation (26).
EP18152456.2A 2017-03-09 2018-01-19 Dispositif d'aide auditive pour compensation des acouphènes Active EP3373600B1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102017203947.7A DE102017203947A1 (de) 2017-03-09 2017-03-09 Verfahren zum Betreiben einer Hörhilfevorrichtung sowie Hörhilfevorrichtung

Publications (2)

Publication Number Publication Date
EP3373600A1 EP3373600A1 (fr) 2018-09-12
EP3373600B1 true EP3373600B1 (fr) 2021-03-03

Family

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Family Applications (1)

Application Number Title Priority Date Filing Date
EP18152456.2A Active EP3373600B1 (fr) 2017-03-09 2018-01-19 Dispositif d'aide auditive pour compensation des acouphènes

Country Status (5)

Country Link
US (1) US10805749B2 (fr)
EP (1) EP3373600B1 (fr)
CN (1) CN108574921B (fr)
DE (1) DE102017203947A1 (fr)
DK (1) DK3373600T3 (fr)

Families Citing this family (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US10582286B2 (en) * 2018-06-22 2020-03-03 University Of South Florida Method for treating debilitating hyperacusis
EP3687188B1 (fr) * 2019-01-25 2022-04-27 ams AG Système audio d'annulation de bruit et procédé de réglage d'une fonction de transfert cible d'un système audio d'annulation de bruit
CN113825081B (zh) * 2021-09-19 2024-04-23 武汉左点科技有限公司 一种基于掩蔽治疗系统的助听方法及装置

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US5721783A (en) * 1995-06-07 1998-02-24 Anderson; James C. Hearing aid with wireless remote processor
DK0820211T3 (da) 1996-07-09 2002-01-21 Siemens Audiologische Technik Programmerbart høreapparat
DE20110947U1 (de) * 2001-07-02 2001-12-06 Beyersdorffer Martin Hörvorrichtung zur Behandlung von Tinitusgehörleiden
US20050251226A1 (en) 2004-05-07 2005-11-10 D Angelo John P Suppression of tinnitus
DE102006016440A1 (de) 2006-04-07 2007-10-11 Siemens Audiologische Technik Gmbh Hörgerät
US8265314B2 (en) * 2007-04-25 2012-09-11 Schumaier Daniel R Preprogrammed hearing assistance device with program selection based on patient usage
DE102010039589A1 (de) 2010-08-20 2012-02-23 Siemens Medical Instruments Pte. Ltd. Hörhilfe- und/oder Tinnitus-Therapie-Gerät
EP2533550B2 (fr) 2011-06-06 2021-06-23 Oticon A/s Diminution du niveau sonore de tintement par traitement d'instrument auditif
CN103784253A (zh) 2012-11-02 2014-05-14 姜鸿彦 耳鸣声治疗装置
CN202859447U (zh) 2012-11-02 2013-04-10 姜鸿彦 耳鸣声治疗装置
CN103096230A (zh) 2013-01-15 2013-05-08 杭州爱听科技有限公司 全数字式助听器及其变通道匹配补偿方法
DK3232927T3 (da) * 2014-12-19 2022-01-10 Widex As Fremgangsmåde til at betjene et høreapparatsystem og et høreapparatsystem

Non-Patent Citations (1)

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Also Published As

Publication number Publication date
EP3373600A1 (fr) 2018-09-12
DE102017203947A1 (de) 2018-09-13
US10805749B2 (en) 2020-10-13
US20180262854A1 (en) 2018-09-13
DK3373600T3 (da) 2021-05-31
CN108574921A (zh) 2018-09-25
CN108574921B (zh) 2021-05-11

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