EP2023669A2 - Procédé destiné au fonctionnement d'un système d'appareil auditif et système d'appareil auditif - Google Patents

Procédé destiné au fonctionnement d'un système d'appareil auditif et système d'appareil auditif Download PDF

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Publication number
EP2023669A2
EP2023669A2 EP08104762A EP08104762A EP2023669A2 EP 2023669 A2 EP2023669 A2 EP 2023669A2 EP 08104762 A EP08104762 A EP 08104762A EP 08104762 A EP08104762 A EP 08104762A EP 2023669 A2 EP2023669 A2 EP 2023669A2
Authority
EP
European Patent Office
Prior art keywords
feedback
hearing aid
oscillations
aid system
frequency
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.)
Ceased
Application number
EP08104762A
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German (de)
English (en)
Other versions
EP2023669A3 (fr
Inventor
Henning Dr. Puder
Tobias Rosenkranz
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
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Application filed by Siemens Audiologische Technik GmbH filed Critical Siemens Audiologische Technik GmbH
Publication of EP2023669A2 publication Critical patent/EP2023669A2/fr
Publication of EP2023669A3 publication Critical patent/EP2023669A3/fr
Ceased legal-status Critical Current

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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
    • H04R25/45—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback
    • H04R25/453—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback electronically
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R2430/00—Signal processing covered by H04R, not provided for in its groups
    • H04R2430/03—Synergistic effects of band splitting and sub-band processing

Definitions

  • the invention relates to a method for operating a hearing aid system with at least two microphones arranged spatially separate from one another and sound-generating output units assigned to these microphones, as is the case in particular in binaural hearing aid systems.
  • the invention further relates to a hearing aid system for carrying out the method.
  • Hearing aids as medical aids, are intended to enable patients with hearing impairments to achieve as natural a hearing sensation as possible. It must be ensured that technically caused noise is suppressed as completely as possible. Such noise include, in particular caused by acoustic feedback whistling. Such acoustic feedbacks occur particularly in hearing aid systems when they operate with high gain and have their cause in feedback-induced oscillations of a certain frequency (feedback). Such a whistling is sometimes so loud that it is perceived as disturbing even in the environment of a hearing aid wearer.
  • Feedback caused by whistling can always occur when sound, which is recorded via a microphone of a hearing aid, amplified by a corresponding amplifier and output via a sound-emitting output unit, so for example via the handset of a hearing aid.
  • the sound output may return to the microphone again and is amplified further.
  • the sound gain must be greater than the attenuation of the sound on the way from the sound producing output unit back to the microphone.
  • the phase shift between originally from Microphone recorded sound and emitted by the sound-emitting output unit sound on the microphone 2 ⁇ or any multiple thereof.
  • the loop gain of a hearing aid system or hearing aid which is the product of the hearing aid gain and the attenuation of the feedback path, during an adjustment of the hearing aid by setting so-called notch (narrowband notch) filters in frequency ranges in which with an occurrence of feedback-induced oscillations is to be reduced.
  • notch narrowband notch
  • An incoming useful signal will always be applied to both components of a binaural hearing aid system almost simultaneously and at the same frequency.
  • By comparing the generated microphone signals via a so-called coherence analysis it is attempted to interpret signals with high coherence as useful signals and to interpret signals with low coherence as feedback-induced oscillations.
  • a disadvantage of this method is that with a constant occurrence of feedback-induced oscillations on a component of a binaural hearing aid system they are coupled after a short time on the sound generating output device in the microphone of the other component of the binaural hearing aid system, if the sound generated by the feedback oscillations is emitted sufficiently loud by the oscillating component.
  • a coherence analysis inevitably results in a high degree of coherence for signals generated in this way. As a result, these signals are interpreted as incoming useful signals.
  • the misinterpretation means that no measures are taken to suppress the feedback-related whistling.
  • the object of the present invention is to provide a possibility for operating a hearing aid system, wherein feedback-induced oscillations should be reliably detected and avoided without having to noticeably limit the functionality of the hearing aid system.
  • claim 1 The object is achieved by a method having the features of claim 1, the claims 2 to 9 indicate advantageous embodiments of such a method, claim 10 relates to a hearing aid system which is suitable for carrying out the method according to the invention and the claims 11 to 21 relate to advantageous embodiments of such a hearing aid system.
  • the invention relates to the core problems of feedback avoidance: detection reliability or artifact avoidance, adaptation speed and optimal parameter determination for algorithms for suppressing, avoiding or compensating for feedback-induced oscillations.
  • the invention can be applied to all hearing aid systems which have at least two microphones and at least two sound-emitting output units.
  • microphone signals from at least two microphones spaced apart from each other are compared.
  • By analyzing and comparing the microphone signals or signals derived therefrom it is possible to distinguish between feedback-induced oscillations and useful signals, even if these useful signals are similar to the feedback-induced oscillations with respect to the coherence measure.
  • the invention thus relates to a preferably binaural method for feedback suppression, which can be used inter alia for controlling an adaptive compensation filter in the frequency range in which feedback-induced oscillations are detected, the method not being based on a coherence function, but on an intelligent frequency-dependent power comparison the microphone signals of both hearing aids emanates.
  • This procedure is clearly superior to the known coherence method. This is partly due to the fact that on the one hand microphone signals can be incoherent by Kopfabschattungs monoe in some frequency components, even if they are not due to feedback-induced oscillations, resulting in undesirable signal attenuation.
  • feedback whistling occurs, it is precisely after a short time that the frequency components at which feedback occurs are particularly coherent since they can be received by both microphones. The cause is the acoustic coupling between the hearing aids, which is not completely excluded by Kopfabschattungs monoe.
  • the invention accordingly relates to a method for operating a hearing aid system having at least two microphones arranged separately from one another and sound generating output units assigned to these microphones, in which feedback-induced oscillations are detected by comparing the microphone signals or signals derived therefrom and initiating measures for reducing the feedback-induced oscillations when detected feedback-induced oscillations
  • the comparison of the microphone signals or signals derived therefrom comprises a frequency-selective power comparison.
  • the frequency-selective power comparison generates at least one quantitative or quantitatively evaluable signal which indicates feedback-related oscillations and their frequency.
  • this is done by the frequency-selective power comparison is performed so that the difference of the spectra of the two microphone signals formed, this difference is subjected to an offset correction and evaluated with respect to a threshold value.
  • the evaluation with respect to the threshold value takes place, for example, in such a way that values below the threshold value are cut off, while values above the threshold value flow in unadulterated into a further signal processing.
  • the procedure according to the invention includes a normalization of the spectral values to the power and thereby the inclusion of the spectral environment of the oscillation frequencies in their evaluation.
  • Fig. 1 shows a binaural hearing aid system, which is suitable for preventing the invention of feedback-induced oscillations.
  • This consists of two identical ear to be worn components, each with a microphone 1, 11, a signal processing unit 2, 12 and a speaker 3, 13 have.
  • Microphone 1, 11, signal processing unit 2, 12, and speakers 3, 13 form a signal amplification path, wherein in the signal processing unit 2, 12 amplifier modules and other signal processing components can be integrated, can be realized via the different algorithms for signal processing.
  • Incoming microphone signals are amplified to the speakers 3, 13 forwarded. If sound which is output via the loudspeaker 3, 13 returns to the microphone 1, 11, feedback-dependent oscillations (feedback) can arise on both sides of the binaural hearing aid system.
  • Incoming microphone signals are furthermore each fed to a comparison unit 4, 14.
  • a communication link 10 which is preferably designed wirelessly.
  • incoming microphone signals to the other comparison unit 14, 4 are transmitted, whereby each of the signals of both microphones 1, 11 provide input signals for the comparison units 4, 14.
  • the comparison units 4, 14 are designed such that they can detect feedback-induced oscillations based on a comparison of incoming microphone signals or signals derived therefrom, wherein they can perform at least one frequency-selective power comparison of the two microphone signals.
  • algorithms for carrying out further comparison operations can be created in the comparison units 4, 14.
  • the comparison units 4, 14 have the technical possibilities to generate from the frequency-selective power comparison at least one feedback-induced oscillations and their frequency indicative quantitative signal, which takes place for example in that the difference of the spectra of the two microphone signals formed this difference is subjected to an offset correction and evaluated with respect to a threshold value.
  • the components of the hearing aid system according to the invention to be carried close to the ear comprise a respective control unit 5, 15, which is supplied with the quantitative signal which is generated in this way and which is due to feedback-induced oscillation.
  • the control unit 5, 15 is designed so that it in turn can generate output signals that can be used to set adaptive filter algorithms.
  • the signal paths between the signal processing units 2, 12 and the associated loudspeakers 3, 13 are divided in the present example into several parallel paths, via which a particular frequency band is transmitted in each case. In each case further signal processing units 6, 16, 7, 17, 8, 18 are integrated into these signal paths, the effect of which essentially consists in the implementation of algorithms for suppressing feedback-induced oscillations. If therefore feedback-induced oscillations are detected by the control unit 5, 15 on the basis of the quantitative signal of the comparison unit 4, 14, the control unit 5, 15 will produce at least one output signal which, in turn, adjusts at least one adaptive compensation filter to reduce feedback induced oscillations to ensure optimal suppression of the feedback induced oscillations.
  • the comparison unit 4, 14 and the control unit 5, 15 form within the meaning of the invention means for identifying feedback-induced oscillations.
  • Fig. 2 to 5 shows the spectra of the microphone signals, whereby the frequencies on the x-axis are represented in the form of frequency components, the frequency components 0 to 60 corresponding to a frequency spectrum of 0 to 10 kHz.
  • Fig. 2 shows the spectra of the microphone signals of the two components of the binaural hearing aid system.
  • the power values are associated with narrow frequency bands surrounding the sampling frequencies in the acquisition of the spectra. In this way, one obtains a quasi-continuous envelope, which well represents the frequency response of the applied microphone signals, which relates to useful signals and feedback-induced oscillations alike.
  • the basic idea with the present invention is that feedbacks due to their narrowbandness make themselves felt as peak values in the spectrum, provided that not On both sides, feedback occurs at the same time and at the same frequencies, which is very unlikely - only noticeable on either side of the binaural hearing aid system. Since the two components of the binaural hearing device system have a communication connection, the spectra can be interchanged, which, using appropriate comparison operations, allows filtering out of such peak values, for example by differentiating the spectra, since the spectra otherwise have a strong similarity.
  • Fig. 3 shows a difference spectrum of the microphone signals of the two components of the binaural hearing aid system, wherein the difference was arbitrarily performed so that the spectrum of the right component of the hearing aid system was subtracted from the spectrum of the left component of the hearing aid system. Accordingly, in accordance with the described hearing situation, a negative value of the difference signal results in almost all frequency ranges. This trend is broken only by the two described peak values at just 20 frequency components and slightly above 30 frequency components.
  • the offset which appears in the difference spectrum due to the predominantly negative values of the difference signal, has a broadband character, it can be efficiently eliminated by subtracting the median of the spectral values and thus does not lead to the false detection of feedbacks.
  • Fig. 4 shows a corrected by the offset correction just described differential spectrum of the microphone signals of the two components of the binaural hearing aid system.
  • the two peak values occur at just under 20 frequency components and just above 30 frequency components even clearer. This makes it possible to establish a threshold value above which it can be assumed in the difference spectrum of a presence of feedback-induced oscillations.
  • Fig. 5 shows a difference spectrum of the microphone signals of the two components of the binaural hearing aid system, which is adjusted by a threshold value comparison. All values below the threshold value within the difference spectrum are set to zero, while the values lying above the threshold value are output in accordance with the actually determined power difference in the respective frequency range. With a suitable choice of the threshold value, each peak of such a corrected difference spectrum can be evaluated as a reliable indication of the occurrence of feedback-induced oscillations and used to trigger corresponding suppression mechanisms in order to prevent the occurrence of feedback-induced oscillations quickly and reliably.
  • the differential signal generated by the spectral evaluation according to the invention offers the possibility of a spectrally selective detection of feedback-induced oscillations and at the same time forms a quantitatively evaluable parameter which can be included in different ways in controls of automatic algorithms for feedback suppression.
  • the adaptation rate of an adaptive method (frequency domain NLMS algorithm) in the frequency domain in which corresponding feedbacks were detected, can be briefly increased selectively in the frequency components. Since the detection reliability for feedback-induced oscillations is very good and the increase in the adaptation speed is only selective, virtually no audible signal distortions occur.
  • the difference signal generated according to the invention can also be used to control the attenuation of frequency components in which Feedback can be detected to increase, which is exactly to the extent that the feedbacks disappear. This has the advantage over the use of notch filters that no frequency is completely eliminated. Also for the automatic adjustment of the damping properties of the quantitative statement content of the frequency-dependent difference signal is a significant advantage. A combination of both methods is also possible and leads to a rapid suppression of feedback without Nutzsignalverzerrache.
  • the advantage of the invention lies in the opening of a robust binaural method for feedback suppression based on the comparison of the spectral powers of the hearing aid components on both sides of the head.
  • the detection of feedback can be used for example both for adaptation control as well as for short-term selective damping. This ensures that feedback is effectively suppressed.
  • the invention is not limited to the illustrated embodiments, but can be extended by a variety of variants.
  • more than two microphone signals can also be compared with one another.
  • the signal processing in a hearing aid system according to the invention in parallel take place in several channels of the signal processing units.
  • the comparison of microphone signals or the generation of a feedback-related oscillations and their frequency indicative quantitative signal by the frequency-selective power comparison can then also be done in parallel in multiple channels. Measures for reducing detected feedback-induced oscillations are then advantageously limited to the respective channels.
  • the frequency-selective power comparison of microphone signals according to the invention may be performed only temporarily or continuously as a function of specific parameters, for example as a function of a set hearing program or the current volume setting of the hearing aid system.

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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)
EP08104762A 2007-08-09 2008-07-16 Procédé pour le fonctionnement d'un système d'appareil auditif et système d'appareil auditif Ceased EP2023669A3 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102007037659A DE102007037659B4 (de) 2007-08-09 2007-08-09 Verfahren zum Betrieb eines Hörgerätesystems und Hörgerätesystem

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EP2023669A2 true EP2023669A2 (fr) 2009-02-11
EP2023669A3 EP2023669A3 (fr) 2012-09-19

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EP08104762A Ceased EP2023669A3 (fr) 2007-08-09 2008-07-16 Procédé pour le fonctionnement d'un système d'appareil auditif et système d'appareil auditif

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US (1) US8116490B2 (fr)
EP (1) EP2023669A3 (fr)
DE (1) DE102007037659B4 (fr)

Families Citing this family (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DK2190217T3 (da) * 2008-11-24 2012-05-21 Oticon As Fremgangsmåde til reduktion af tilbagekobling i høreapparater samt tilsvarende anordning og tilsvarende computerprogramprodukt
DE102009016845B3 (de) * 2009-04-08 2010-08-05 Siemens Medical Instruments Pte. Ltd. Anordnung und Verfahren zur Erkennung von Rückkopplungen bei Hörvorrichtungen
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
DE102009021310B4 (de) * 2009-05-14 2011-02-24 Siemens Medical Instruments Pte. Ltd. Binaurale Hörvorrichtung und Verfahren zum Betrieb einer binauralen Hörvorrichtung mit Frequenzverzerrung
DE102013207080B4 (de) * 2013-04-19 2019-03-21 Sivantos Pte. Ltd. Binaurale Mikrofonanpassung mittels der eigenen Stimme
EP2988529B1 (fr) * 2014-08-20 2019-12-04 Sivantos Pte. Ltd. Frequence de division adaptative dans appareils d'aide auditive
US10856078B1 (en) * 2019-05-31 2020-12-01 Bose Corporation Systems and methods for audio feedback elimination
US11250833B1 (en) * 2020-09-16 2022-02-15 Apple Inc. Method and system for detecting and mitigating audio howl in headsets
US11825270B2 (en) * 2020-10-28 2023-11-21 Oticon A/S Binaural hearing aid system and a hearing aid comprising own voice estimation
WO2022225535A1 (fr) * 2021-04-23 2022-10-27 Eargo, Inc. Détection de tonalité dans des signaux audio de dispositif auditif
US11984109B2 (en) * 2022-09-01 2024-05-14 Gopro, Inc. Detection and mitigation of a wind whistle

Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE10110258C1 (de) 2001-03-02 2002-08-29 Siemens Audiologische Technik Verfahren zum Betrieb eines Hörhilfegerätes oder Hörgerätesystems sowie Hörhilfegerät oder Hörgerätesystem

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Publication number Priority date Publication date Assignee Title
AU733433B2 (en) * 1998-02-18 2001-05-17 Widex A/S A binaural digital hearing aid system
DE10020756B4 (de) * 2000-04-27 2004-08-05 Harman Becker Automotive Systems (Becker Division) Gmbh Vorrichtung und Verfahren zum geräuschabhängigen Anpassen eines akustischen Nutzsignals
DE10048354A1 (de) * 2000-09-29 2002-05-08 Siemens Audiologische Technik Verfahren zum Betrieb eines Hörgerätesystems sowie Hörgerätesystem

Patent Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE10110258C1 (de) 2001-03-02 2002-08-29 Siemens Audiologische Technik Verfahren zum Betrieb eines Hörhilfegerätes oder Hörgerätesystems sowie Hörhilfegerät oder Hörgerätesystem

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US8116490B2 (en) 2012-02-14
DE102007037659B4 (de) 2013-06-13
EP2023669A3 (fr) 2012-09-19
DE102007037659A1 (de) 2009-04-02
US20090041272A1 (en) 2009-02-12

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