EP1239700A2 - Prothèse auditive ou un système de prothèses audives et ainsi que leur méthode d'utilitsation - Google Patents

Prothèse auditive ou un système de prothèses audives et ainsi que leur méthode d'utilitsation Download PDF

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Publication number
EP1239700A2
EP1239700A2 EP02003475A EP02003475A EP1239700A2 EP 1239700 A2 EP1239700 A2 EP 1239700A2 EP 02003475 A EP02003475 A EP 02003475A EP 02003475 A EP02003475 A EP 02003475A EP 1239700 A2 EP1239700 A2 EP 1239700A2
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EP
European Patent Office
Prior art keywords
hearing aid
microphone
feedback
oscillations
signal
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
EP02003475A
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German (de)
English (en)
Other versions
EP1239700B1 (fr
EP1239700A3 (fr
EP1239700B2 (fr
Inventor
Volker Dr. Hohmann
Volkmar Hamacher
Inga Dr. Holube
Birger Prof. Kollmeier
Thomas Wittkop
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 GmbH
Original Assignee
Siemens Audiologische Technik GmbH
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Application filed by Siemens Audiologische Technik GmbH filed Critical Siemens Audiologische Technik GmbH
Publication of EP1239700A2 publication Critical patent/EP1239700A2/fr
Publication of EP1239700A3 publication Critical patent/EP1239700A3/fr
Publication of EP1239700B1 publication Critical patent/EP1239700B1/fr
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    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Electric hearing aids
    • H04R25/55—Electric hearing aids using an external connection, either wireless or wired
    • H04R25/552—Binaural
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Electric hearing aids
    • H04R25/40—Arrangements for obtaining a desired directivity characteristic
    • H04R25/407—Circuits for combining signals of a plurality of transducers
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Electric hearing aids
    • H04R25/45—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback
    • H04R25/453—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback electronically

Definitions

  • the invention relates to a method for operating a hearing aid or hearing aid system with at least a first Microphone for generating a first microphone signal and a spaced-apart second microphone for generating a second microphone signal.
  • the invention further relates to a Hearing aid or hearing aid system for performing the method.
  • the first class includes the so-called compensation algorithms, which with the help of adaptive filters the feedback portion in the Estimate the microphone signal and neutralize it by subtraction and therefore do not impair hearing aid amplification. Indeed put these compensation methods uncorrelated, i.e. ideally "white", input signals ahead. Tonale Input signals that always have a high temporal correlation lead to an incorrect estimate of the feedback path, which can mistakenly lead to that tonal input signal itself is subtracted.
  • the second class contains the algorithms that only then become active if there are feedback-related oscillations are. They generally contain a mechanism to detect oscillations of the microphone signal continuously supervised. Become feedback-typical oscillations detected, the hearing aid gain is reduced so far that the loop gain is below the critical limit sinks.
  • the gain reduction can e.g. by lowering a frequency channel or by activating a suitable one narrow-band notch filter. adversely is that the oscillation detectors in principle not between tonal input signals and feedback whistles can distinguish. The result is that tonal input signals mistaken for feedback oscillations and then inadmissible through the reduction mechanism (e.g. notch filter) be lowered in level.
  • the compensation algorithms often become decorrelating acting delay elements in the signal processing chain introduced to prevent tonal signal sections with a length that is characteristic of speech signals be attacked noticeably.
  • due to Echo effects and irritation through desynchronized visual and auditory information only delays in the millisecond range allowed. Therefore, for example, the reduction of music signals, often over a significantly longer period Period are correlated, cannot be avoided.
  • a another countermeasure is to adapt the filter so slow that all relevant tonal useful signals not be attacked.
  • this also has the consequence that the compensation filter changes rapidly Feedback paths can no longer follow fast enough, so that feedback-related oscillations for a certain time arise and only disappear when the Feedback path has stabilized and the filter is sufficient again is adapted enough.
  • the object of the present invention is to provide a method for Operation of a hearing aid or hearing aid system and a Specify hearing aid or hearing aid system in which feedback-related Oscillations can be avoided without doing so the sound quality deteriorate noticeably.
  • T2 is one Feedback suppression arrangement with adaptive filtering known for a hearing prosthesis, which in a special Embodiment has two microphones. A detection of Oscillations are not carried out.
  • the invention can be used with all common hearing aid types can be used, for example, behind the ear wearable Hearing aids, in the ear portable hearing aids, implantable hearing aids or handheld devices. Farther one of several can be used to care for the hearing impaired Existing hearing aid systems are used, e.g. a hearing aid system with two hearing aids worn on the head for binaural care.
  • microphone signals are at least two spaced microphones generated. At least it has to a microphone be arranged so that it is feedback-related Hearing aid device does not oscillate or at most in a weakened form.
  • useful signals are said to be similar in the microphones concerned Way to be included.
  • the tonal useful signals then differ from the microphones hardly generated any microphone signals, so this are recognized as useful signals.
  • feedback-related signals recorded very differently by the microphones, so that this results from the comparison of the microphone signals as feedback recognized and reduced by suitable measures can be.
  • the distance between the microphones, their microphone signals can be compared with each other, for example by the Attaching a microphone to a collar clip become.
  • Another possibility is a hearing aid system with two hearing aids for binaural care. The comparison can then between a microphone signal or a derived signal of a hearing aid with a Microphone signal or a signal derived therefrom second hearing aid. Useful signals are then from the two microphones recorded approximately the same and due to feedback Oscillations on a hearing aid arise, are not detected by the other hearing aid.
  • a signal path is provided for signal transmission is between the hearing aids a signal path is provided. The signal transmission can done wirelessly or wired.
  • the derived one Signal comprises characteristic parameters of the microphone signal, that are relevant to detecting oscillations are. For example, these are the oscillation frequencies of the Microphone signal and the signal strength at the respective oscillation frequencies.
  • the invention forms oscillations by means of these narrow-band filter, whose cut-off frequencies roughly match the To eliminate oscillation frequencies.
  • the Filters can e.g. be designed as a notch filter. Enough a notch filter does not turn off when it is detected again of oscillations further notch filters at the respective frequency activated.
  • Is an adaptive filter for reduction in a hearing aid device feedback-related oscillations used so is detected according to a variant of the invention when feedback-related Oscillations the adaptive compensation filter customized.
  • the operating parameters of the filter are changed so that an increase in the Adaptation speed takes place.
  • the rate of adaptation is reversed of the adaptive compensation filter reduced, if no feedback-related oscillations are detected become.
  • This principle can also be applied analogously to frequency range-based Apply compensation filter. Either the correlation analysis to identify feedback-related Oscillations as well as the regulation of the adaptation speed can advantageously be frequency-specific.
  • Detects a hearing aid device due to feedback At least oscillations based on a correlation analysis two microphone signals (cross correlation), so there is another way to reduce these oscillations therein, uncorrelated frequency components of the microphone signals to suppress. Then only the signal components processed further, essentially in all microphone signals are equally present.
  • the hearing aid shown schematically in Figure 1 includes a microphone 1, a signal processing unit 2 and one Handset 3. Receives sound that is output through the handset 3 becomes microphone 1 again, feedback-related Oscillations (feedback) arise. Conditions for this are that the so-called loop gain of the system, i.e. the product of hearing aid amplification and attenuation of the feedback path is greater than 1 and that the phase shift this loop gain an integer Corresponds to multiples of 360 °.
  • an evaluation and control unit 5 in addition to the Microphone signal of the microphone 1 another microphone signal supplied by a microphone 4.
  • the two microphones 1 and 4 are arranged so that useful sound from both microphones is in is recorded approximately equally.
  • the microphone 4 for example on a collar clip outside the housing, in which the microphone 1 is arranged attached.
  • the evaluation and control unit 5 are those emanating from the microphones Microphone signals analyzed and compared. For example, through auto correlation analysis Oscillations in the individual microphone signals are detected become. If there are oscillations in both microphone signals, so their frequencies are determined and compared with each other. With oscillations in both microphone signals are equally present, it is with great certainty around tonal input signals. With oscillations that only in a microphone signal, especially that of a microphone 1 outgoing microphone signal are present with a high probability of feedback-related oscillations. To eliminate them, the Signal processing unit 2 by means of the evaluation and control unit 5. For example, for filtering out the oscillation frequencies in the signal processing unit 2 narrowband Notch filter can be activated and adjusted.
  • the microphone signals of the Microphones 1 and 4 also initially each have a signal preprocessing unit 6 and 7 can be supplied.
  • the signal preprocessing can, for example, an A / D conversion or a Include signal pre-amplification.
  • FIG. 2 shows two hearing aids 11 and 11 ', each with one Microphone 12 or 12 ', a signal processing unit 13 or 13 'and a receiver 14 or 14'.
  • One oscillation detector each 15 or 15 ' continuously monitors the microphone signal on oscillations and determined when oscillations are detected the oscillation frequencies.
  • the signal path 17 an exchange of the detected oscillation frequencies.
  • the comparison units 16 and 16 ' the oscillation frequencies of the hearing aid in question with the oscillation frequencies of the other hearing aid compared.
  • Notch filter does not turn off, so if Oscillations of further notch filters N2 to NN or N2 'to NN' be activated at the respective frequencies.
  • the invention is not based on the illustrated embodiments limited, but expandable by a variety of variants.
  • feedback-related can be used to identify Oscillations also have more than two microphone signals be compared with each other.
  • the signal processing in parallel with a hearing aid according to the invention take place in several channels of the signal processing unit.
  • the comparison of microphone signals or the correlation analysis can then also run in parallel in several channels respectively. Measures to reduce detected feedback-related Oscillations are then advantageous only to that channels concerned.
  • the comparison or the correlation analysis of microphone signals continuously or depending on certain parameters e.g. the set hearing program or volume setting

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  • Engineering & Computer Science (AREA)
  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Circuit For Audible Band Transducer (AREA)
  • Electrically Operated Instructional Devices (AREA)
  • Measurement Of Mechanical Vibrations Or Ultrasonic Waves (AREA)
EP02003475.7A 2001-03-02 2002-02-14 Prothèse auditive ou un système de prothèses audives et ainsi que leur méthode d'utilitsation Expired - Lifetime EP1239700B2 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE10110258A DE10110258C1 (de) 2001-03-02 2001-03-02 Verfahren zum Betrieb eines Hörhilfegerätes oder Hörgerätesystems sowie Hörhilfegerät oder Hörgerätesystem
DE10110258 2001-03-02

Publications (4)

Publication Number Publication Date
EP1239700A2 true EP1239700A2 (fr) 2002-09-11
EP1239700A3 EP1239700A3 (fr) 2006-08-02
EP1239700B1 EP1239700B1 (fr) 2008-05-07
EP1239700B2 EP1239700B2 (fr) 2017-07-26

Family

ID=7676185

Family Applications (1)

Application Number Title Priority Date Filing Date
EP02003475.7A Expired - Lifetime EP1239700B2 (fr) 2001-03-02 2002-02-14 Prothèse auditive ou un système de prothèses audives et ainsi que leur méthode d'utilitsation

Country Status (5)

Country Link
US (1) US7013015B2 (fr)
EP (1) EP1239700B2 (fr)
AT (1) ATE394896T1 (fr)
DE (2) DE10110258C1 (fr)
DK (1) DK1239700T4 (fr)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1748678A3 (fr) * 2005-07-25 2009-09-23 Siemens Audiologische Technik GmbH Appareil auditif et procédé pour la réduction des rétroactions

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US7639827B2 (en) * 2003-10-01 2009-12-29 Phonak Ag Hearing system which is responsive to acoustical feedback
US20060139030A1 (en) * 2004-12-17 2006-06-29 Hubbard Bradley J System and method for diagnosing manufacturing defects in a hearing instrument
DE102005008318B4 (de) * 2005-02-23 2013-07-04 Siemens Audiologische Technik Gmbh Hörhilfegerät mit benutzergesteuerter Einmessautomatik
US20070183609A1 (en) * 2005-12-22 2007-08-09 Jenn Paul C C Hearing aid system without mechanical and acoustic feedback
DE102006019694B3 (de) 2006-04-27 2007-10-18 Siemens Audiologische Technik Gmbh Verfahren zum Einstellen eines Hörgeräts mit Hochfrequenzverstärkung
US8767975B2 (en) * 2007-06-21 2014-07-01 Bose Corporation Sound discrimination method and apparatus
DE102007037659B4 (de) 2007-08-09 2013-06-13 Siemens Audiologische Technik Gmbh Verfahren zum Betrieb eines Hörgerätesystems und Hörgerätesystem
EP2046073B1 (fr) * 2007-10-03 2017-03-08 Oticon A/S Système d'assistance auditive avec agencement de réponse pour prédire et annuler la réponse acoustique, procédé et utilisation
US8588445B2 (en) * 2008-01-10 2013-11-19 Panasonic Corporation Hearing aid processing apparatus, adjustment apparatus, hearing aid processing system, hearing aid processing method, and program and integrated circuit thereof
DK2086250T3 (da) * 2008-02-01 2020-07-06 Oticon As Lyttesystem med et forbedret feedback-undertrykkelsessystem, en fremgangsmåde og anvendelse
US8611554B2 (en) * 2008-04-22 2013-12-17 Bose Corporation Hearing assistance apparatus
WO2010019660A2 (fr) * 2008-08-12 2010-02-18 Intricon Corporation Commutateur pour aide auditive
US8767987B2 (en) * 2008-08-12 2014-07-01 Intricon Corporation Ear contact pressure wave hearing aid switch
DK2190217T3 (da) * 2008-11-24 2012-05-21 Oticon As Fremgangsmåde til reduktion af tilbagekobling i høreapparater samt tilsvarende anordning og tilsvarende computerprogramprodukt
EP2246845A1 (fr) * 2009-04-21 2010-11-03 Siemens Medical Instruments Pte. Ltd. Procédé et dispositif de traitement de signal acoustique pour évaluer les coefficients de codage prédictifs linéaires
DE112011102933T5 (de) * 2010-09-03 2013-07-18 Med-El Elektromedizinische Geräte GmbH Im Mittelohr implantierbares Mikrofon
US9078077B2 (en) 2010-10-21 2015-07-07 Bose Corporation Estimation of synthetic audio prototypes with frequency-based input signal decomposition
JP6069830B2 (ja) * 2011-12-08 2017-02-01 ソニー株式会社 耳孔装着型収音装置、信号処理装置、収音方法
US9654874B2 (en) * 2013-12-16 2017-05-16 Qualcomm Incorporated Systems and methods for feedback detection
US11109164B2 (en) * 2017-10-31 2021-08-31 Widex A/S Method of operating a hearing aid system and a hearing aid system
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Publication number Priority date Publication date Assignee Title
EP1748678A3 (fr) * 2005-07-25 2009-09-23 Siemens Audiologische Technik GmbH Appareil auditif et procédé pour la réduction des rétroactions

Also Published As

Publication number Publication date
DE10110258C1 (de) 2002-08-29
US20020176594A1 (en) 2002-11-28
DK1239700T3 (da) 2008-09-01
DK1239700T4 (da) 2017-11-06
EP1239700B1 (fr) 2008-05-07
ATE394896T1 (de) 2008-05-15
EP1239700A3 (fr) 2006-08-02
DE50212199D1 (de) 2008-06-19
EP1239700B2 (fr) 2017-07-26
US7013015B2 (en) 2006-03-14

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