EP2503795A2 - Appareil auditif avec dispositif de suppression de l'effet Larsen et procédé de fonctionnement de l'appareil auditif - Google Patents

Appareil auditif avec dispositif de suppression de l'effet Larsen et procédé de fonctionnement de l'appareil auditif Download PDF

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Publication number
EP2503795A2
EP2503795A2 EP12158347A EP12158347A EP2503795A2 EP 2503795 A2 EP2503795 A2 EP 2503795A2 EP 12158347 A EP12158347 A EP 12158347A EP 12158347 A EP12158347 A EP 12158347A EP 2503795 A2 EP2503795 A2 EP 2503795A2
Authority
EP
European Patent Office
Prior art keywords
filter
microphone
whitening
signal
hearing
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
EP12158347A
Other languages
German (de)
English (en)
Other versions
EP2503795A3 (fr
Inventor
Henning Puder
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
Original Assignee
Siemens Medical Instruments Pte Ltd
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 Medical Instruments Pte Ltd filed Critical Siemens Medical Instruments Pte Ltd
Publication of EP2503795A2 publication Critical patent/EP2503795A2/fr
Publication of EP2503795A3 publication Critical patent/EP2503795A3/fr
Ceased legal-status Critical Current

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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
    • 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
    • H04R25/552—Binaural

Definitions

  • the invention relates to a hearing device in which a microphone is coupled via a pre-whitening filter with a feedback suppression device.
  • the term hearing device is understood to mean in particular a hearing aid.
  • the term includes other portable acoustic devices such as headsets, headphones and the like.
  • Hearing aids are portable hearing aids that are used to care for the hearing impaired. To meet the numerous individual needs, different types of hearing aids are provided. They may include hearing aids such as behind-the-ear (BTE) hearing aids, external receiver (RIC) receivers (RIC) and in-the-ear (ITE) hearing aids, e.g. also include Concha hearing aids or canal hearing aids (ITE, CIC).
  • BTE behind-the-ear
  • RIC external receiver
  • ITE in-the-ear
  • ITE in-the-ear
  • the hearing aids listed by way of example are worn on the outer ear or in the ear canal.
  • bone conduction hearing aids, implantable or vibrotactile hearing aids are also available on the market. The stimulation of the damaged hearing takes place either mechanically or electrically.
  • Hearing aids have in principle as essential components an input transducer, an amplifier and an output transducer.
  • the input transducer is usually a sound receiver, z. As a microphone, and / or an electromagnetic receiver, for. B. an induction coil.
  • the output transducer is usually used as an electroacoustic transducer, z. As miniature speaker, or as an electromechanical transducer, z. B. bone conduction, realized.
  • the amplifier is usually integrated in a signal processing unit. This basic structure is in FIG. 1 shown using the example of a behind-the-ear hearing aid. In a hearing aid housing 1 for
  • one or more microphones 2 are installed for recording the sound from the environment.
  • a signal processing unit 3 which is also integrated in the hearing aid housing 1, processes the microphone signals and amplifies them.
  • the output signal of the signal processing unit 3 is transmitted to a loudspeaker or earpiece 4, which outputs an acoustic signal.
  • the sound is optionally transmitted via a sound tube, which is fixed with an earmold in the ear canal, to the eardrum of the device carrier.
  • an otoplastic can also be used as a dome (dome - dome) designated dome-shaped earpiece, which adapts to a form of the same when inserted into the ear canal.
  • tip In the context of an open fitting often a so-called tip (tip) is used, which has a particularly narrow shape so that it does not affect ventilation of the ear canal.
  • the power supply of the hearing device and in particular the signal processing unit 3 is effected by a likewise integrated into the hearing aid housing 1 battery. 5
  • a feedback canceller In order to avoid such a whistling sound, a feedback canceller (English: feedback canceller) may be provided, which may be part of the signal processing unit 3, for example.
  • a feedback path suppression model For a successful suppression of a whistling sound, a feedback path suppression model must first be adapted for the feedback path. During the adaptation, unwanted artefacts can occur, which are perceptible in the sound signal of the listener. This artefact formation can occur especially in the case of microphone signals with a tonal component.
  • a filter is referred to here, which reduces differences between the amplitudes of individual frequency components within a short-term spectrum of a microphone signal.
  • a filter is referred to here, which reduces differences between the amplitudes of individual frequency components within a short-term spectrum of a microphone signal.
  • Such leveling of the short-term spectrum corresponds to a reduction in the autocorrelation of the signal, i. his decorrelation.
  • a tonality of the microphone signal is reduced.
  • the frequency response of a pre-whitening filter corresponds to the inverted short-time spectrum of the signal to be whitened.
  • a disadvantage of using a pre-whitening filter is that the leveling also attenuates those spectral peaks in the short-term spectrum of the microphone signal that are characteristic of the whistling tone of the feedback. As a result, the adaptation of the model in the feedback suppression device is made more difficult because of the then only weakly expressed spectral peak. In particular, it becomes very slow.
  • a first microphone is coupled via a pre-whitening filter to a feedback suppression device.
  • the hearing device has a second microphone.
  • the hearing device is designed to have a frequency response of the pre-whitening filter (for the first microphone) depending on a signal from the second microphone.
  • the method according to the invention provides, in a first step, for detecting a first microphone signal of the first microphone and a second microphone signal of the second microphone.
  • the first microphone signal is filtered by the pre-whitening filter.
  • a frequency response of the pre-whitening filter for the first microphone signal is determined in dependence on the second microphone signal.
  • the feedback suppression device for the first microphone signal is then adapted.
  • the hearing device according to the invention and the method according to the invention have the advantage that the feedback suppression device is quickly adapted in the case of a feedback in the first microphone signal and yet no artifacts arise during the adaptation.
  • the adaptation of the feedback suppression device is here and below meant the adaptation of the model used by the feedback suppression device for the feedback path.
  • the artifacts are avoided by the pre-whitening filter.
  • filtering of the first microphone signal during feedback will not attenuate the spectral peak in the short-term spectrum of the first microphone signal. This allows the rapid adaptation of the feedback suppression device.
  • the pre-whitening filter may be coupled to an adaptive filter designed to provide filter coefficients for pre-whitening filtering in response to the microphone signal of the second microphone.
  • the pre-whitening filter then receives the filter coefficients from the adaptive filter and sets the frequency response based on the filter coefficients.
  • the filter coefficients are preferably also determined adaptively, ie continuously. Thus, even with a change in the short-term spectrum of the ambient sound signal always the appropriate filter coefficients are ready.
  • the filter coefficients may be determined, for example, on the basis of a least mean square algorithm or the Levinson-Durbin algorithm or a linear prediction or an autocorrelation determination.
  • the hearing device is advantageously developed if the feedback suppression device has a shadow filter.
  • a shadow filter can avoid noise and stability problems in particularly critical acoustic environments.
  • an estimation device for a feedback path can also be integrated into a useful signal path. This integration requires fewer filters to provide adaptive feedback cancellation.
  • the first microphone is arranged in a component of the hearing device, for example a hearing device, which is intended to be worn on an ear of a user of the hearing device, and the second microphone is arranged at a distance from this component. Due to the distance, it is very unlikely that a feedback with a whistling sound at a certain frequency will be formed simultaneously in both microphones. Thus, it is ensured that the pre-whitening no attenuation of the feedback component, ie the spectral peaks in the short-term spectra of the first microphone signal is caused.
  • the two microphones are arranged in components of the hearing device which are to be worn on different sides of the head of a user, thus e.g. in two hearing aids.
  • This development is based on the observation that in the two components feedback for the same frequency almost never occurs at the same time.
  • the ambient sound signals received by the two components are always very similar.
  • whitening of the signal portion of the ambient sound in the first microphone signal is possible by means of a pre-whitening filter whose frequency response is determined on the basis of the second microphone signal.
  • the signal component caused by local feedback in the first microphone is not attenuated.
  • the shading of the head causes the feedback signal, which manifests itself in one of the hearing aids, to arrive at the other not at all or only strongly attenuated, so that its pre-whitening filter has no attenuation in the feedback signal.
  • FIG. 2 a schematic construction of a binaural hearing aid 10 is shown.
  • the hearing aid 10 has as components a left hearing aid 12 and a right hearing aid 14, which are to be worn by a user of the hearing aid 10 at the ear.
  • the letters L (left) and R (right) indicate on which side of the head the hearing aids are worn.
  • the hearing aids 12 and 14 may be, for example, in-the-ear hearing aids or behind-the-ear hearing aids.
  • the two hearing aids 12 and 14 are connected to each other via a communication link 16. It may be, for example, a cable or a radio link. Via the communication link 16, between the hearing aids 12 and 14, e.g. Audio signals or other data are exchanged.
  • the left hearing device 12 has a first microphone 18, which is coupled via a pre-whitening filter 20 to a feedback suppression device 22.
  • the feedback suppression device 22 is coupled via a post-processing device 24 to a receiver 26 of the hearing device 12.
  • a second microphone 28 which is coupled to an adaptive filter 30. Filter coefficients determined by the adaptive filter 30 are transmitted via the communication link 16 to the pre-whitening filter 20.
  • a microphone signal of the first microphone 18 is whitened by the pre-whitening filter 20. This reduces the tonality of the microphone signal, thereby producing fewer artifacts in the output of the feedback suppression device 22 during adaptation of the feedback suppression device 22.
  • the feedback suppression device 22 may be based on an adaptive system identification that determines a feedback component in the signal received from the pre-whitening filter 20 based on a model for a local feedback path transfer function from the handset 26 to the microphone 18. The adaptation of the feedback suppression device 22 takes place on the basis of the feedback component contained in the microphone signal of the first microphone 18.
  • the frequency response of the pre-whitening filter 20, i. Its transmission behavior is determined by the filter coefficients which the pre-whitening filter 20 receives from the adaptive filter 30.
  • the adaptive filter 30 determines the filter coefficients based on a microphone signal of the second microphone 28.
  • the filter coefficients may be determined, for example, on the basis of a linear prediction.
  • a linear prediction it is also possible, for example, to use the Levinson-Durbin algorithm or, in general, a method for determining an autocorrelation function of the microphone signal.
  • inversion of an auto power density spectrum of the microphone signal is a method of determining a filter for pre-whitening.
  • the adaptive filter 30 may also be part of the left hearing device 12.
  • the postprocessing means 24 corrects the signal distortion caused by the pre-whitening filter 20 in the microphone signal, i. through the whites, undone.
  • the output signal of the feedback suppression device 22 can be processed, for example, with a filter whose transfer function is formed by inverting a current transfer function of the pre-whitening filter 20.
  • the postprocessing device 24 also includes an amplifier by which the equalized signal for operating the receiver 24 is amplified.
  • the right-hand hearing device 14 also has a pre-whitening filter and a feedback suppression unit, both of which, for the sake of clarity, in FIG. 2 are not shown. Filter coefficients for the pre-whitening filter of the right hearing aid 14 are determined via a second adaptive filter based on the microphone signal of the first microphone 18.
  • the pre-whitening by means of the pre-whitening filter 20 can also be combined with a frequency shift (English: frequency shifting).
  • a frequency shift (English: frequency shifting).
  • the frequency shift may be e.g. be effected by a single-sideband modulation, for example by means of a Hilbert filter.
  • the shift may be 20 Hz, for example.
  • the feedback suppression unit 22 adapts fast enough to prevent the generation of a whistling sound. Nevertheless, artefact formation is greatly reduced or even completely prevented.
  • FIG. 3 two diagrams D1 and D2 are shown. Both graphs D1, D2 each show two graphs of frequency responses of pre-whitening filters.
  • the abscissa axis of the diagrams D1 and D2 indicates the frequency f (in kilohertz), the ordinate axis the amplitude A (in decibels).
  • Diagram D1 shows a frequency response F1 and a frequency response F2.
  • the frequency response F1 was determined on the basis of the microphone signal of the microphone 18 of the left hearing aid 12, the frequency response F2 on the basis of the microphone signal of the microphone 28 of the right hearing aid 14. By means of the two microphones 18, 28 an ambient sound was detected. A feedback was not present in both hearing aids 12, 14.
  • the filter coefficients underlying the frequency responses were determined in the case of the frequency response F2 by means of the adaptive filter 30 (right microphone signal) or in the case of the frequency response F1 by means of the adaptive filter of the left hearing aid 12 (left microphone signal).
  • frequency responses F3 and F4 are shown.
  • the frequency response F3 corresponds to the frequency response F1, as it results at another time, if the adaptive filter has adapted to a change in the ambient sound.
  • the frequency response F4 corresponds to the frequency response F2 at the other time.
  • FIG. 4 are shown in three diagrams D3, D4 and D5 respectively further frequency responses, which have been determined on the basis of the microphone signals of the left microphone 18 and the right microphone 28.
  • the diagrams D3 to D5 again show frequency responses, as they result at different times.
  • Diagrams D3 to D5 show frequency responses to pre-whitening filters as they result when acoustic feedback is present on the left hearing aid 12, causing one or more whistling sounds to be generated by the left hearing aid 12.
  • Diagram D3 shows a frequency response F5 for a pre-whitening filter, which was determined based on the left microphone signal.
  • the frequency response F5 has a strong notch 32.
  • the notch 32 is located at the Frequency of a whistling sound caused by the feedback. If the filter coefficients giving the frequency response F5 were also used to whiten the left microphone signal in the pre-whitening filter 20, because of the notch 32, this would result in a strong attenuation of the signal derived from the feedback, ie the whistling sound caused spectral peak in the short-term spectrum of the microphone signal of the left microphone 18 would be attenuated. Accordingly, an adaptation of the downstream feedback suppression unit 22 would slow down.
  • a frequency response F6 determined on the basis of the microphone signal of the right hearing aid 14 by the adaptive filter 30 is not affected by the feedback in a frequency range 34 in which the frequency of the whistle tone lies.
  • the frequency response F6 thus represents only the ambient sound.
  • FIG. 5 To illustrate the operation of the feedback suppression device 22, the left hearing aid 12 is shown in FIG FIG. 2 shown hearing aid 10 again shown in more detail.
  • the feedback suppression device 22 has an estimation unit 36, by means of which an estimated transfer function H is determined for a transfer function H of a feedback path.
  • the transfer function H will be referred to as the estimated feedback path H.
  • the estimated feedback path H represents the already mentioned model for the feedback path.
  • a feedback portion 42 is estimated from an output signal 38 of a processing unit 40.
  • the estimated feedback component 42 is subtracted from the output signal of the pre-whitening filter 20 by means of a calculation unit 44. With an ideal adaptation of the estimation unit 36, this would remove a feedback component in an output signal of the pre-whitening filter 20.
  • the output signal of the calculation unit 44 is transmitted to the processing unit 40 as a useful signal.
  • the output signal forms an error signal 46 for adapting the estimation unit 36, ie for adapting the estimated feedback path ⁇ .
  • the processing unit 40 may, for example, effect a selective amplification of individual frequency ranges for which a hearing ability of the user of the hearing aid 10 is impaired.
  • FIG. 5 The functioning of the post-processing device 24 is also illustrated in greater detail.
  • To current filter coefficients PW for the pre-whitening filter 20 receives an adjustable filter 48 of the post-processing device 24 via a communication connection 16 'filter coefficients PW -1 , by means of which the frequency response of the adjustable filter 48 is set.
  • the filter coefficients PW -1 result in a frequency response of the adjustable filter 48, which is inversely to that of the pre-whitening filter 20 operated with the filter coefficients PW, so that filtering of the output signal 38 of the processing unit 40 with the adjustable filter 48 causes the already described equalization.
  • the amplifier 50 then effects the already described amplification of the equalized signal for the operation of the handset 26th
  • a signal namely the estimated feedback component 42
  • the estimation unit 36 determines the useful signal path, which here leads from the microphone 18 via the pre-whitening filter 20, the calculation unit 44, the processing unit 40 and the post-processing device 24 to the handset 26.
  • FIG. 6 is a hearing aid 12 'of a binaural hearing aid 10 not shown' shown.
  • elements of the hearing aid 12 ' which correspond in their function elements of the hearing aid 12, provided with the same, but painted reference numerals.
  • the adaptation of an estimation unit 36' on the basis of a "pre-whitened" signal can be performed without the need to filter signals with the inverted frequency response.
  • a signal output by a handset 26 'need not be equalized at the hearing aid 12', thereby avoiding potential problems with stable operation of the inverse filter necessary for equalization and possible noise in the output signal.
  • the hearing aid 12 ' can thus also in environments be used in which a white of a microphone signal of a microphone 18 'causes a relatively strong distortion.
  • no filter coefficients for an inverse filtering, namely the equalization have to be calculated.
  • the estimation unit 36 ' is part of a feedback suppression device 22' of the hearing aid 12 '. It forms, together with a calculation unit 44 ', a shadow filter 52 with which a feedback path ⁇ is estimated in the manner described in connection with the estimation unit 36 and the calculation unit 44. A return of an output signal of a processing unit 40 'to the estimation unit 36' via another pre-whitening filter 20 ''.
  • the two pre-whitening filters 20 'and 20 are connected via a communication connection 16" to an adaptive filter, not shown, which corresponds to the adaptive filter 30.
  • a rapid adaptation of the estimation unit 36' is also provided in the hearing device 12 ' the named reasons.
  • a feedback filter 36 "and a computing unit 44" is effected directly in the non-whitened microphone signal.
  • a transfer function of the feedback filter 36 " that is, its frequency response, it corresponds to that of the estimation unit 36 'estimated transfer function h of the feedback path.
  • the estimation means 36' transmits to corresponding coefficients of the feedback filter 36 ''.
  • the shadow filter 52 is thus an estimated feedback path ⁇ without having to change a useful signal on a useful signal path connecting the microphone 18 'to the handset 26', since the shadow filter 52 processes the whitened signals of the pre-whitening filters 20 'and 20 "in the case of the feedback filter 36 "allows artifact-free processing of the microphone signal of the microphone 18 'through the feedback filter 36".
  • FIG. 6 An amplifier of the hearing aid 12 'provided for operating the handset 26' and corresponding to the amplifier 50 is shown in FIG FIG. 6 not shown

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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)
  • Circuit For Audible Band Transducer (AREA)
  • Tone Control, Compression And Expansion, Limiting Amplitude (AREA)
EP12158347.0A 2011-03-25 2012-03-07 Appareil auditif avec dispositif de suppression de l'effet Larsen et procédé de fonctionnement de l'appareil auditif Ceased EP2503795A3 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102011006129A DE102011006129B4 (de) 2011-03-25 2011-03-25 Hörvorrichtung mit Rückkopplungsunterdrückungseinrichtung und Verfahren zum Betreiben der Hörvorrichtung

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EP2503795A2 true EP2503795A2 (fr) 2012-09-26
EP2503795A3 EP2503795A3 (fr) 2016-04-20

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EP12158347.0A Ceased EP2503795A3 (fr) 2011-03-25 2012-03-07 Appareil auditif avec dispositif de suppression de l'effet Larsen et procédé de fonctionnement de l'appareil auditif

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US (1) US20120243716A1 (fr)
EP (1) EP2503795A3 (fr)
DE (1) DE102011006129B4 (fr)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3065417A1 (fr) * 2015-03-05 2016-09-07 Sivantos Pte. Ltd. Procede de suppression d'un bruit parasite dans un systeme acoustique

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US11019414B2 (en) * 2012-10-17 2021-05-25 Wave Sciences, LLC Wearable directional microphone array system and audio processing method
WO2017106325A1 (fr) * 2015-12-15 2017-06-22 Westone Laboratories Égalisation basse pression sonique ambiante
US10186279B2 (en) * 2016-06-21 2019-01-22 Revx Technologies Device for detecting, monitoring, and cancelling ghost echoes in an audio signal
JP6471199B2 (ja) * 2017-07-18 2019-02-13 リオン株式会社 フィードバックキャンセラ及び補聴器
CN114866380A (zh) * 2021-02-03 2022-08-05 维沃移动通信有限公司 信号处理方法、装置、通信设备及存储介质
CN113596665A (zh) * 2021-07-29 2021-11-02 北京小米移动软件有限公司 啸叫声的抑制方法、装置、耳机及存储介质

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WO2007113282A1 (fr) * 2006-04-01 2007-10-11 Widex A/S Appareil auditif et procédé permettant de commander la vitesse d'adaptation dans des systèmes anti-rétroaction pour appareils auditifs
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
EP2086250B1 (fr) * 2008-02-01 2020-05-13 Oticon A/S Système d'écoute avec système d'annulation de rétroaction acoustique amélioré, procédé et utilisation
US8594173B2 (en) * 2008-08-25 2013-11-26 Dolby Laboratories Licensing Corporation Method for determining updated filter coefficients of an adaptive filter adapted by an LMS algorithm with pre-whitening
US8655001B1 (en) * 2009-02-13 2014-02-18 Advanced Bionics Ag In-the-canal hearing aid using two microphones

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Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3065417A1 (fr) * 2015-03-05 2016-09-07 Sivantos Pte. Ltd. Procede de suppression d'un bruit parasite dans un systeme acoustique
US9824675B2 (en) 2015-03-05 2017-11-21 Sivantos Pte. Ltd. Method for suppressing interference noise in an acoustic system and acoustic system

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DE102011006129B4 (de) 2013-06-06
US20120243716A1 (en) 2012-09-27
EP2503795A3 (fr) 2016-04-20
DE102011006129A1 (de) 2012-09-27

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