EP1737270A1 - Appareil auditif avec réduction du couplage - Google Patents

Appareil auditif avec réduction du couplage Download PDF

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Publication number
EP1737270A1
EP1737270A1 EP06114883A EP06114883A EP1737270A1 EP 1737270 A1 EP1737270 A1 EP 1737270A1 EP 06114883 A EP06114883 A EP 06114883A EP 06114883 A EP06114883 A EP 06114883A EP 1737270 A1 EP1737270 A1 EP 1737270A1
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EP
European Patent Office
Prior art keywords
signal
hearing aid
feedback
output
test
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
EP06114883A
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German (de)
English (en)
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EP1737270B2 (fr
EP1737270B1 (fr
Inventor
Roland Barthel
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Sivantos GmbH
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Siemens Audioligische Technik GmbH
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Application filed by Siemens Audioligische Technik GmbH filed Critical Siemens Audioligische Technik GmbH
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Publication of EP1737270B2 publication Critical patent/EP1737270B2/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
    • H04R25/45—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback
    • H04R25/453—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback electronically

Definitions

  • the present invention relates to a hearing aid having an input transducer for receiving an input signal and converting to an electrical signal, a signal processing unit for processing the electrical signal, an output transducer for converting the processed electrical signal into an output signal perceivable by a user as an acoustic signal, a feedback reduction means for adjustably reducing or attenuating a feedback signal contained in the input signal, a signal source for outputting a test signal not directly originating from the input signal by the output transducer, measuring means for detecting a response signal originating from the output test signal from the input signal and an evaluation and control means for setting of parameters of the feedback reduction means based on the response signal.
  • Another approach to reducing feedback is to use an adaptive filter.
  • the feedback path is analyzed continuously or at certain intervals.
  • the output of the adaptive filter is adjusted to neutralize the feedback component in the input signal of the hearing aid.
  • a hearing aid with a feedback reduction device in which two different modes of operation are distinguished.
  • an input signal containing a feedback component is picked up by a microphone, amplified in an amplifier, and delivered via a handset.
  • a second operating mode of the known hearing aid from time to time, the signal path between the microphone and the handset is interrupted.
  • a test signal is generated and output via the handset, so that it after Passing the feedback path is received as a response signal from the microphone.
  • the parameters of the feedback reduction device are readjusted and maintained until the hearing aid device switches again into the second operating mode.
  • test signals generated in connection with the feedback compensation which either cover only a portion of the frequency range that can be transmitted by the hearing aid or else also comprise signal components perceptible by the user and are thus perceived as disturbing.
  • the object of the present invention is therefore to achieve the best possible measurement of the feedback path, without having to give the user as annoying felt test signals from the hearing aid.
  • This object is achieved in a hearing aid of the type mentioned fact that from the hearing aid of the user perceptible information signals can be delivered, wherein the information signals are output from the signal source and used as test signals.
  • the hearing aid according to the invention is, for example, a hearing aid worn behind the ear, a hearing aid worn in the ear, an implantable hearing aid or a pocket hearing aid. Furthermore, the hearing aid according to the invention may also be part of a plurality of devices for supplying a hearing aid system comprising hearing aid devices, eg part of a hearing aid device with two head-worn hearing aids for binaural care, part of a hearing aid system with a head-worn hearing aid and a portable external processor unit , Part of a fully or partially implantable hearing aid device system with multiple components, part of a hearing aid system with external auxiliary components like remote control unit or external microphone unit, etc.
  • hearing aid devices eg part of a hearing aid device with two head-worn hearing aids for binaural care, part of a hearing aid system with a head-worn hearing aid and a portable external processor unit , Part of a fully or partially implantable hearing aid device system with multiple components, part of a hearing aid system with external auxiliary components like remote control unit or external
  • a hearing aid includes an input transducer for receiving an input signal.
  • the input transducer is usually designed as a microphone that receives an acoustic signal and converts it into an electrical signal.
  • a hearing aid usually includes a signal processing unit for processing and frequency-dependent amplification of the electrical signal.
  • a preferably digital signal processor (DSP) is used, whose operation can be influenced by means of programs or parameters which can be transmitted to the hearing aid.
  • the mode of operation of the signal processing unit can be adapted both to the individual hearing loss of a hearing aid wearer and to the current hearing situation in which the hearing aid is currently being operated.
  • the thus changed electrical signal is finally fed to an output transducer.
  • This is usually designed as a handset, which converts the electrical output signal into an acoustic signal.
  • other embodiments are also possible here, e.g. an implantable output transducer that connects directly to an auditory ossicle and causes it to vibrate.
  • the starting point of the invention is a hearing aid device in which test signals can be generated in the hearing aid device and output via the earpiece. After passing through the feedback path, the test signals are recorded by the microphone of the hearing aid and then evaluated. From a comparison of this response signal with the output test signal conclusions about the feedback path can be obtained. Suitable measures for feedback suppression can then be carried out. For example, parameters of an adaptive feedback compensation filter can be used set so that a compensation of feedback signal components in the input signal of the microphone takes place.
  • test signals such signals which are generated anyway in the hearing aid and output via the output transducer. These signals are used, for example, to inform the user about current settings of the hearing aid. Such settings may relate, for example, to the volume setting or the setting of the current hearing program.
  • the emitted and user-perceivable signals used as test signals to estimate the feedback path may be used to inform the user of certain system conditions of the hearing aid. Such system states are e.g. the state of charge of the voltage source used.
  • the hearing aid according to the invention preferably provides a plurality of further signals that can be generated in the hearing aid and can be recognized by the user, as described e.g. are also known in mobile phones.
  • the output signals can be used to inform the user (announcements, word messages, name, address, etc.) or can be submitted for the user's entertainment. It may therefore also be such signals that are not generated when needed by means of a signal generator in the hearing aid, but also to those signals that are stored in a memory of the hearing aid and are read only when needed.
  • the signals used can also originate in an external device, for example a remote control for the hearing aid device, and from there, for example, initially transmitted as an electromagnetic signal to the hearing aid and converted by this into an acoustically perceptible signal and output.
  • an external device for example a remote control for the hearing aid device
  • the indication signals which can be emitted by the hearing aid device are preferably designed such that they cover the widest possible range of the frequency spectrum that can be transmitted by the hearing aid device. This ensures that the evaluation of the feedback path also takes place in a wide frequency range.
  • the invention offers the advantage that the delivery of the warning signals is desired by the user and is therefore not perceived as disturbing.
  • the alert signals can be delivered at a volume that is well above the level of permanent, subthreshold test signals. This greatly improves the measurement of the feedback path.
  • An analysis of the response signal picked up by the input transducer reveals which frequencies or frequency ranges are particularly strongly fed back.
  • An embodiment of the invention provides that in the signal path of the hearing aid between the input transducer and the output transducer existing filters are set so that certain frequencies or frequency ranges, which are particularly strongly fed back, are filtered. For example, Notch filters can be used to deliberately suppress certain frequencies.
  • Another embodiment of the invention provides an adaptive filter for which filter parameters are generated based on the response signal resulting from the emitted indication signal such that the expected feedback signal is subtracted from the microphone input signal.
  • This embodiment has the advantage that, as a rule, no restriction in which by the hearing aid in principle transmissible frequency spectrum is required.
  • the figure shows the much simplified block diagram of a hearing aid with a microphone 1 for receiving an acoustic input signal and conversion into an electrical signal.
  • the electrical signal is supplied to a signal processing unit 2 for the frequency-dependent amplification of the input signal and to compensate for the individual hearing loss of a user.
  • the processed signal is finally converted by a receiver 3 into an acoustic output signal AS and delivered to the auditory canal of a user.
  • part of the output signal AS output by the receiver 3 passes via the feedback path to the microphone 1.
  • the feedback signal RS thus forms part of the input signal ES in the microphone 1.
  • HR the transfer function for the feedback signal RS with HR. In this constellation, if the phase and gain conditions for the feedback signal RS required for the occurrence of feedback are met, typical unwanted feedback whistling occurs.
  • the hearing aid device comprises a signal source 4, by means of which information signals generated or stored in the hearing aid device can be output via the earpiece 3.
  • the indication signals serve, for example, to inform the user about certain settings of the hearing aid device, for example the set hearing program or the set volume.
  • the user can be made aware of certain system states of the hearing aid by means of the indication signals, such as the state of charge of the voltage source (not shown).
  • a large number of further warning signals is possible, by means of which the user is automatically made aware of certain events or supplied with specific information on demand. Examples include a time announcement or the retrieval of certain previously stored in a memory information such as names, addresses, telephone numbers, etc., which are available as voice signals.
  • the hint or information signals used are specially adapted to the particular use as test signals for estimating the feedback path.
  • the information signals cover the widest possible range of the frequency spectrum that can be transmitted by the hearing aid, so that the feedback behavior can be tested for precisely this frequency range.
  • the information signals are preferably not individual tones, but tone sequences, melodies, noises, etc.
  • the normal signal path through the hearing aid is advantageously interrupted or at least greatly attenuated by the microphone 1 via the signal processing unit 2 to the handset 3, so that the output signal AS contains at least essentially no further signal components in addition to the information signal during the delivery of an information signal , This simplifies the measurement of the transmission behavior for the feedback path.
  • the received as a result of the information signal output at the microphone 1 feedback signal RS is supplied in the hearing aid to a measuring, evaluation and control device 5, in which a comparison of the received signal with the output via the signal source 4 signal. From the comparison, conclusions can be drawn about the feedback path and in particular the transfer function HR. From the data thus obtained countermeasures in the hearing aid can be initiated, so that an unwanted feedback whistling is prevented even during normal operation of the hearing aid.
  • filter parameters in the signal processing unit 2 can be adjusted so that individual frequencies or frequency ranges are particularly strong are affected by feedback, are attenuated by adjustable filters in the signal processing unit 2.
  • the hearing aid according to the embodiment comprises an adaptive filter 6, by which the expected feedback signal is reproduced and subtracted from the microphone signal to cancel the feedback signal RS picked up by the microphone 1.
  • corresponding filter parameters are generated in the measuring, evaluation and control device 5 and set in the adaptive filter 6.
  • the invention has the advantage that a good adaptation of the adaptive filter 6 is ensured by the use of information signals which can be emitted by the hearing aid on many occasions and are desired by the user and are therefore not considered to be disturbing.

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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)
  • Circuit For Audible Band Transducer (AREA)
  • Amplifiers (AREA)
  • Control Of Amplification And Gain Control (AREA)
  • Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)
  • Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
EP06114883A 2005-06-21 2006-06-02 Appareil auditif avec réduction du couplage Not-in-force EP1737270B2 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102005028742A DE102005028742B3 (de) 2005-06-21 2005-06-21 Hörhilfegerät mit Mitteln zur Rückkopplungskompensation und Verfahren zur Rückkopplungsunterdrückung

Publications (3)

Publication Number Publication Date
EP1737270A1 true EP1737270A1 (fr) 2006-12-27
EP1737270B1 EP1737270B1 (fr) 2008-05-07
EP1737270B2 EP1737270B2 (fr) 2012-05-02

Family

ID=36649416

Family Applications (1)

Application Number Title Priority Date Filing Date
EP06114883A Not-in-force EP1737270B2 (fr) 2005-06-21 2006-06-02 Appareil auditif avec réduction du couplage

Country Status (5)

Country Link
US (1) US7801318B2 (fr)
EP (1) EP1737270B2 (fr)
AT (1) ATE394899T1 (fr)
DE (2) DE102005028742B3 (fr)
DK (1) DK1737270T4 (fr)

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102011106634A1 (de) * 2011-07-04 2013-01-10 Eberhard-Karls-Universität Tübingen Universitätsklinikum Hörgerät und Verfahren zum Eliminieren akustischer Rückkopplungen bei Verstärkung akustischer Signale
EP2661103A1 (fr) * 2012-05-02 2013-11-06 Oticon A/s Procédé de fixation d'un dispositif auditif

Families Citing this family (12)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7627129B2 (en) * 2002-11-21 2009-12-01 Fraunhofer-Gesellschaft Zur Foerderung Der Angewandten Forschung E.V. Apparatus and method for suppressing feedback
US11856375B2 (en) 2007-05-04 2023-12-26 Staton Techiya Llc Method and device for in-ear echo suppression
US11683643B2 (en) 2007-05-04 2023-06-20 Staton Techiya Llc Method and device for in ear canal echo suppression
EP2003928B1 (fr) * 2007-06-12 2018-10-31 Oticon A/S Système anti-feedback en ligne pour appareil d'aide auditive
US11291456B2 (en) 2007-07-12 2022-04-05 Staton Techiya, Llc Expandable sealing devices and methods
US8600067B2 (en) * 2008-09-19 2013-12-03 Personics Holdings Inc. Acoustic sealing analysis system
WO2010061539A1 (fr) * 2008-11-28 2010-06-03 パナソニック株式会社 Prothèse auditive
DE102009007079A1 (de) * 2009-02-02 2010-08-12 Siemens Medical Instruments Pte. Ltd. Verfahren zur Ermittlung des akustischen Rückkopplungsverhaltens eines Hörgeräts anhand von geometrischen Daten eines Ohrs
WO2010094033A2 (fr) 2009-02-13 2010-08-19 Personics Holdings Inc. Bouchon d'oreille et systèmes de pompage
EP2523471B1 (fr) 2011-05-09 2014-06-18 Bernafon AG Système de test permettant d'évaluer la performance de rétroaction d'un dispositif d'écoute
US9060237B2 (en) 2011-06-29 2015-06-16 Harman International Industries, Incorporated Musical measurement stimuli
EP3016407B1 (fr) * 2014-10-28 2019-12-11 Oticon A/s Système auditif pour estimer un trajet de rétroaction d'un dispositif auditif

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US4628530A (en) * 1983-02-23 1986-12-09 U. S. Philips Corporation Automatic equalizing system with DFT and FFT
EP0557847A1 (fr) * 1992-02-27 1993-09-01 Siemens Audiologische Technik GmbH Appareils portatif à tête pour sourds
US5259033A (en) * 1989-08-30 1993-11-02 Gn Danavox As Hearing aid having compensation for acoustic feedback
US20030161492A1 (en) * 2002-02-26 2003-08-28 Miller Douglas Alan Frequency response equalization system for hearing aid microphones
WO2004047484A1 (fr) * 2002-11-21 2004-06-03 Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. Procede et dispositif pour empecher une retroaction
US20050047620A1 (en) * 2003-09-03 2005-03-03 Resistance Technology, Inc. Hearing aid circuit reducing feedback

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DE3205686A1 (de) * 1982-02-17 1983-08-25 Robert Bosch Gmbh, 7000 Stuttgart Hoergeraet
GB8919591D0 (en) * 1989-08-30 1989-10-11 Gn Davavox As Hearing aid having compensation for acoustic feedback
US5402496A (en) * 1992-07-13 1995-03-28 Minnesota Mining And Manufacturing Company Auditory prosthesis, noise suppression apparatus and feedback suppression apparatus having focused adaptive filtering
CA2100015A1 (fr) 1992-07-29 1994-01-30 Resound Corporation Prothese auditive permettant l'elimination de la reaction acoustique commandee par l'utilisateur
US6219427B1 (en) * 1997-11-18 2001-04-17 Gn Resound As Feedback cancellation improvements
WO2000052102A1 (fr) 1999-03-05 2000-09-08 Cabot Corporation Procede relatif a l'elaboration de pigments colores
US7058182B2 (en) * 1999-10-06 2006-06-06 Gn Resound A/S Apparatus and methods for hearing aid performance measurement, fitting, and initialization
DE10048354A1 (de) * 2000-09-29 2002-05-08 Siemens Audiologische Technik Verfahren zum Betrieb eines Hörgerätesystems sowie Hörgerätesystem
US7627129B2 (en) 2002-11-21 2009-12-01 Fraunhofer-Gesellschaft Zur Foerderung Der Angewandten Forschung E.V. Apparatus and method for suppressing feedback

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4628530A (en) * 1983-02-23 1986-12-09 U. S. Philips Corporation Automatic equalizing system with DFT and FFT
US5259033A (en) * 1989-08-30 1993-11-02 Gn Danavox As Hearing aid having compensation for acoustic feedback
EP0557847A1 (fr) * 1992-02-27 1993-09-01 Siemens Audiologische Technik GmbH Appareils portatif à tête pour sourds
US20030161492A1 (en) * 2002-02-26 2003-08-28 Miller Douglas Alan Frequency response equalization system for hearing aid microphones
WO2004047484A1 (fr) * 2002-11-21 2004-06-03 Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. Procede et dispositif pour empecher une retroaction
US20050047620A1 (en) * 2003-09-03 2005-03-03 Resistance Technology, Inc. Hearing aid circuit reducing feedback

Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102011106634A1 (de) * 2011-07-04 2013-01-10 Eberhard-Karls-Universität Tübingen Universitätsklinikum Hörgerät und Verfahren zum Eliminieren akustischer Rückkopplungen bei Verstärkung akustischer Signale
WO2013004733A1 (fr) 2011-07-04 2013-01-10 Eberhard-Karls-Universität Tübingen Universitätsklinikum Appareil auditif et procédé d'élimination de rétrocouplages acoustiques lors de l'amplification de signaux acoustiques
DE102011106634B4 (de) * 2011-07-04 2015-02-19 Eberhard-Karls-Universität Tübingen Universitätsklinikum Hörgerät und Verfahren zum Eliminieren akustischer Rückkopplungen bei Verstärkung akustischer Signale
US9078073B2 (en) 2011-07-04 2015-07-07 Eberhard-Karls-Universitaet Tuebingen Universitaetsklinikum Hearing aid and method for eliminating acoustic feedback in the amplification of acoustic signals
EP2661103A1 (fr) * 2012-05-02 2013-11-06 Oticon A/s Procédé de fixation d'un dispositif auditif
US9432783B2 (en) 2012-05-02 2016-08-30 Oticon A/S Method of fitting a hearing device

Also Published As

Publication number Publication date
ATE394899T1 (de) 2008-05-15
DE502006000732D1 (de) 2008-06-19
DE102005028742B3 (de) 2006-09-21
EP1737270B2 (fr) 2012-05-02
DK1737270T4 (da) 2012-08-13
US20060285709A1 (en) 2006-12-21
EP1737270B1 (fr) 2008-05-07
DK1737270T3 (da) 2008-09-29
US7801318B2 (en) 2010-09-21

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