EP1406469B1 - Compensateur de la rétroaction dans les systèmes d'amplification acoustique, prothèse auditive, procédé pour la compensation de la rétroaction et utilisation de ce procédé dans les prothèses auditives - Google Patents

Compensateur de la rétroaction dans les systèmes d'amplification acoustique, prothèse auditive, procédé pour la compensation de la rétroaction et utilisation de ce procédé dans les prothèses auditives Download PDF

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Publication number
EP1406469B1
EP1406469B1 EP03021040A EP03021040A EP1406469B1 EP 1406469 B1 EP1406469 B1 EP 1406469B1 EP 03021040 A EP03021040 A EP 03021040A EP 03021040 A EP03021040 A EP 03021040A EP 1406469 B1 EP1406469 B1 EP 1406469B1
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EP
European Patent Office
Prior art keywords
feedback
signal
filter
path
compensation
Prior art date
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Revoked
Application number
EP03021040A
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German (de)
English (en)
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EP1406469A3 (fr
EP1406469A2 (fr
Inventor
Georg-Erwin Arndt
Tom Weidner
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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
Publication of EP1406469A2 publication Critical patent/EP1406469A2/fr
Publication of EP1406469A3 publication Critical patent/EP1406469A3/fr
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    • 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 invention relates to a feedback compensator in an acoustic amplification system for compensating a feedback signal resulting from amplification of an input signal due to a feedback path from an amplified output signal to the input signal.
  • the invention further relates to a hearing aid with such a feedback compensator, to a method for compensating a feedback signal in an acoustic amplification system, and to an application of the method in a hearing aid.
  • a compensation signal is generated which is subtracted from the input signal before amplification and which is such that a frequency causing a feedback is reduced to an intensity which is below a so-called stability limit.
  • the compensation signal is generated along a feedback compensation path with an adaptive feedback compensation filter which is adjusted by means of an adaptation unit and which simulates the feedback path.
  • a frequency limiting filter in the feedback compensation path limits the frequency range in which the compensation signal is generated.
  • the implementation overhead of feedback compensators is significant due to the generation of the feedback equivalent compensation path.
  • the generation of the feedback compensation signal usually takes place with a special adaptive feedback compensation filter, the so-called FIR filter (Finite Impulse Response).
  • FIR filter Finite Impulse Response
  • the input to the FIR filter is the frequency-limited amplified output, which is converted into the compensation signal by the FIR filter.
  • the effect of the FIR filter is set with an adaptation unit that adjusts so-called filter coefficients.
  • the adaptation is based on a comparison of an error signal, usually the input signal, with the amplified output signal.
  • An important prerequisite for a successful adaptation is that the two signals have undergone at least substantially the same filtering before the comparison.
  • a feedback compensator requires nodes and arithmetic operations in the signal or feedback path that require space and computational capacity. Furthermore, one needs buffer memory to process the signal, for example by means of the adaptation unit and the feedback compensation filter. The memory takes up space on the hearing aid device chip and must be co-supplied by the hearing aid device battery.
  • Different feedback compensators are for example from the WO 00/19605 known.
  • the bandwidth of the compensation signal is limited so that noise generated by the feedback compensation filter is minimized to the amplified output signal and limited to the unstable frequency range.
  • the in the WO 00/19605 specified feedback compensators work memory-efficient; however, they have complicated signal or feedback paths with multiple, complex addition computation operations and nodes.
  • an input signal is split into three signals.
  • the first two are combined again directly after each filtering and form the input signal for the Höros réellesignal kau.
  • a compensation signal of an adjustable FIR filter for feedback compensation is subtracted prior to processing.
  • the third signal is filtered by an adaptation unit of the feedback compensation filter as an error signal.
  • the compensation signal generated by the FIR filter is not only subtracted from the input signal for the hearing aid signal processing, but in addition it is subtracted from the error signal before it is fed to the adaptation unit.
  • This embodiment has three addition nodes, three splitting nodes and three filters for the compensation of the input signal and is correspondingly expensive to implement.
  • Another embodiment is based there on the complex use of two Höros réellesignal kauen.
  • an input signal is split into two signals.
  • the first signal is supplied to a first hearing aid device signal processing after filtering.
  • the second signal is filtered complementary to the first signal before being merged with a compensation signal. It is then supplied to an adaptation unit of an adjustable FIR filter as an error signal and to a second hearing aid device signal processing.
  • the output signal of the second signal processing is filtered on the one hand to the FIR filter and fed to the adaptation unit and on the other hand it is combined with an output signal of the first Höros réellesignal kau.
  • the choice of complementary filters affects the hearing aid signal processing.
  • the invention has for its object to provide a feedback compensator, a hearing aid with a feedback compensator, a method for compensating a feedback signal in an acoustic amplification system and a use of the method in a hearing aid, which require little memory and with a simple structure or process with few Nodes and addition arithmetic operations get along.
  • a feedback compensator in an acoustic amplification system for compensating a feedback signal resulting from amplification of an input signal due to a feedback path from an amplified output signal to the input signal, comprising an adaptive feedback compensation filter for forming a feedback compensation path replicating the feedback path Adaptation of the feedback compensation filter and a frequency limiting filter for limiting the frequency range of the feedback compensation path.
  • an input signal path of the input signal after splitting has two signal paths, the first signal path having a first filter and the second signal path having a second filter.
  • the first signal path is operatively connected after the first filter at a first node for subtracting a compensation signal with the feedback compensation filter and at a second node for error signal output with the adaptation unit.
  • An output of the second node and the second signal path are connected to a third node for addition, and an output of this third node is connected to an input of the amplification system.
  • a feedback compensator makes it possible to provide the adaptation unit and the feedback compensation filter with an output signal filtered with the same filter, so that only one buffer memory is necessary for the feedback compensation.
  • This is due to the inventive arrangement of the filters, nodes and addition computational operations in the signal path.
  • the feedback compensator according to the invention requires only two addition nodes and splitting nodes each, as well as a complementary filter pair. Accordingly, inexpensive and with little effort, the arrangement can be implemented.
  • In the feedback compensation path - only one filter is used to limit the frequency range. This has the advantage of reducing artifacts in the low-frequency range.
  • the control of the amplification system is independent of the parameters of the first and second filters as well as the frequency limiting filter, since the feedback compensation relates to the entire amplification system. This allows a flexible choice of filters.
  • the object relating to a hearing aid is solved by a hearing aid having a feedback compensator of the type described above.
  • the invention can be used in all known types of hearing aid devices, for example in behind the ear portable hearing aids, in the ear portable hearing aids, implantable hearing aids, hearing aid devices or Taschenbuchakun.
  • this acts on a multi-channel amplification system which, for example, consists of a filter bank which distributes the input signal to a plurality of frequency-specific matched amplification systems.
  • a multi-channel amplification system which, for example, consists of a filter bank which distributes the input signal to a plurality of frequency-specific matched amplification systems.
  • the frequency limiting filter is disposed between the output of the amplification system and the feedback compensator and the adaptation unit. This has the advantage that the Frequency limiting filter acts only on the feedback compensation path.
  • the first filter and the frequency limiting filter have an at least substantially equal filter function.
  • the two inputs to the adaptation unit then undergo substantially the same filtering, on the one hand the input signal to the first filter and on the other hand the amplified output signal of the frequency limiting filter. This leads to particularly good prerequisites for a fast and good adaptation by means of the adaptation unit.
  • An advantageous embodiment of the method has, as a further feature of the method, that the amplified output signal is passed via the frequency limiting filter to the adaptation unit and to the feedback compensation filter. This reduces the effect of the method on frequency ranges where feedback rarely occurs, and there reduces the generation of artifacts.
  • the frequency ranges of the feedback-prone signal component and of the feedback compensation path are selected such that they are at least approximately equal. This improves the process of adaptation in the adaptation unit.
  • the amplification is performed with a multi-channel amplification system, so that the method can transfer all its advantages also to the use of a multi-channel amplification system.
  • the object is achieved by the application of the method in a hearing aid.
  • FIG. 1 shows a schematic structure of a feedback compensator 1, which allows a good quality amplification of an acoustic input signal 3 with a hearing aid device signal processing 5, even if a feedback path 7 is present.
  • an output signal 9 can find input to the hearing aid device signal processing 5 together with the acoustic input signal 3.
  • the input acoustic signal 3 is changed by means of a feedback compensation path such that the feedback is omitted.
  • the acoustic input signal 3 splits at a splitting node 11 into two signal components, on the one hand in a feedback-prone signal component 13 and on the other hand in a feedback-endangered signal component 15.
  • Two complementary filters 17 and 19 perform the splitting in the frequency domain, so that for example the first filter 17 allows only frequencies greater than one kilohertz to pass through.
  • the feedback-prone signal component 13 is combined at an addition node 21 with an inverted compensation signal 23.
  • the compensation signal 23 is generated by means of a feedback compensation filter 25.
  • the input to the feedback compensation filter 25 is one with a Frequency-limiting filter 27 filtered output signal 29.
  • An adaptation unit 31 changes the coefficients of the feedback compensation filter 25, so that the filtered output signal 29 has energy after passing through the feedback compensation filter 25 predominantly in the frequency range of the feedback.
  • the prerequisite for a successful adaptation is a meaningful error signal 33.
  • a meaningful error signal 33 is taken from the feedback-endangering signal component 13 after being combined with the compensation signal 23 and supplied to the adaptation unit 31 for evaluation.
  • the feedback-endangered signal component 13 is combined with the feedback-endangered signal component 15 at a further node before it enters the hearing aid device signal processing 5. There it is amplified according to the hearing loss of Hörosowskiloss and forwarded to a speaker.
  • the signal course executed here is particularly advantageous in its sequence, since it manages with few nodes and arithmetic operations.
  • the feedback path 7 can be based on two feedback mechanisms, on the one hand on acoustic feedback directly from the loudspeaker to the input microphone and on the other hand on electromagnetic feedback, for example, from a loudspeaker coil to a telecoil within a hearing aid.
  • the feedback compensator 1 requires only one memory for the filtered output signal 29, since this is supplied to both the feedback compensation filter 25 and the adaptation unit 31 for processing.
  • the first filter 17 and the frequency limiting filter 27 set substantially with the same filter function, since then the signal paths to the adaptation unit 31, which begin with the output signal 9, the same filter:
  • the output signal 9 passes through the frequency limiting filter 27 and is then fed directly to the adaptation unit 31.
  • the output signal which reaches the input signal 3 along the feedback path 7 passes through the first filter 17, which is usually selected identically with the frequency limiting filter 27. In this way, a system for compensating feedback based on only two addition nodes is constructed only one buffer needed.
  • FIG. 2 a schematic structure of an alternative use of the feedback compensator 1 is shown.
  • the signal processing is performed by means of a multi-channel hearing aid signal processing 34.
  • the recombined signal after input in the multi-channel hearing aid signal processing 34 is distributed by means of a filter bank 35 to the various amplifiers 37 operating in the different frequency ranges.
  • the amplified signals are combined in an addition node 39 again to the amplified output signal 9.
  • the advantage of this embodiment is that the adaptation of the multi-channel hearing aid device signal processing 34 to the hearing loss of the hearing aid wearer is independent of the filter function of the frequency-limiting filter 27 or of the first filter 17.
  • An influence on the parameters of the multi-channel hearing aid signal processing unit 34 by the feedback compensator 1 is prevented by the inventive arrangement of the feedback compensator 1 and allows a separate setting of the parameters of the multi-channel hearing aid signal processing 34 and the parameters of the feedback compensator 1.

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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)
  • Amplifiers (AREA)

Claims (10)

  1. Compensateur de rétroaction (1) pour un système d'amplification acoustique pour compenser un signal de rétroaction se produisant lors d'une amplification du signal d'entrée en raison d'un trajet de rétroaction (7) entre un signal de sortie amplifié (9) et le signal d'entrée (3),
    avec un filtre adaptatif de compensation de rétroaction (25) pour former un chemin de compensation de rétroaction reproduisant le trajet de rétroaction (7),
    avec une unité d'adaptation (31) pour adapter le filtre de compensation de rétroaction (25), et
    avec un filtre de limitation en fréquence (27) pour limiter le domaine de fréquences du chemin de compensation de rétroaction,
    un chemin de signal d'entrée du signal d'entrée (3) comportant après une décomposition deux chemins de signal,
    le premier chemin de signal comportant un premier filtre (17) et le deuxième chemin de signal un deuxième filtre (19),
    le premier chemin de signal après le premier filtre au niveau d'un premier noeud étant connecté activement au filtre de compensation de rétroaction (25) pour la soustraction d'un signal de compensation (23) et à l'unité d'adaptation (31) pour l'émission d'un signal d'erreur,
    caractérisé en ce que
    la connexion active à l'unité d'adaptation (31) s'effectue au niveau d'un deuxième noeud et en ce qu'une sortie du deuxième noeud et le deuxième chemin de signal sont connectés à un troisième noeud pour l'addition,
    une sortie du troisième noeud étant connectée à une entrée du système d'amplification.
  2. Compensateur de rétroaction (1) selon la revendication 1,
    caractérisé en ce que le système d'amplification est un système d'amplification à canaux multiples.
  3. Compensateur de rétroaction (1) selon la revendication 1 ou 2, caractérisé en ce que le filtre de limitation en fréquence (27) est disposé entre la sortie du système d'amplification et le filtre de compensation de rétroaction (25).
  4. Compensateur de rétroaction (1) selon l'une des revendications 1 à 3, caractérisé en ce que le premier filtre (17) et le filtre de limitation en fréquence (27) ont une fonction filtrante au moins substantiellement identique.
  5. Prothèse auditive avec un compensateur de rétroaction (1) selon l'une des revendications 1 à 4.
  6. Procédé de compensation d'un signal de rétroaction, ledit signal de rétroaction se produisant lors d'une amplification d'un signal d'entrée acoustique (3) en raison d'un trajet de rétroaction (7) entre un signal de sortie amplifié (9) et le signal d'entrée acoustique (3), ledit trajet de rétroaction (7) étant reproduit au moyen d'un filtre adaptatif de compensation de rétroaction (25) commandé par une unité d'adaptation (31), et un filtre de limitation en fréquence (27) limitant le domaine de fréquences d'un chemin de compensation de rétroaction reproduisant le trajet de rétroaction (7),
    comportant les caractéristiques de procédé suivantes :
    - décomposer le signal d'entrée acoustique (3) en une partie de signal menacée de rétroaction (13) et une partie de signal non menacée de rétroaction (15),
    - réunir la partie de signal menacée de rétroaction (13) avec un signal de compensation (23) du filtre de compensation de rétroaction (25) en une partie de signal compensée en rétroaction, et
    - amener la partie de signal compensée en rétroaction à l'unité d'adaptation (31) pour l'évaluation du signal d'erreur,
    caractérisé par :
    - réunir la partie de signal non menacée de rétroaction (15) avec la partie de signal compensée en rétroaction en un signal compensé en rétroaction qui est ensuite amplifié.
  7. Procédé selon la revendication 6, le signal de sortie amplifié (9) étant acheminé via le filtre de limitation en fréquence (27) à l'unité d'adaptation (31) et au filtre de compensation de rétroaction (25).
  8. Procédé selon la revendication 6 ou 7, la partie de signal menacée de rétroaction (13) et le chemin de compensation de rétroaction étant limités au moins approximativement au même domaine de fréquences.
  9. Procédé selon l'une des revendications 6 à 8, l'amplification étant effectuée avec un système d'amplification à canaux multiples.
  10. Utilisation du procédé selon l'une des revendications 1 à 9 dans une prothèse auditive.
EP03021040A 2002-09-30 2003-09-17 Compensateur de la rétroaction dans les systèmes d'amplification acoustique, prothèse auditive, procédé pour la compensation de la rétroaction et utilisation de ce procédé dans les prothèses auditives Revoked EP1406469B1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE10245667 2002-09-30
DE10245667A DE10245667B4 (de) 2002-09-30 2002-09-30 Rückkopplungkompensator in einem akustischen Verstärkungssystem, Hörhilfsgerät, Verfahren zur Rückkopplungskompensation und Anwendung des Verfahrens in einem Hörhilfsgerät

Publications (3)

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EP1406469A2 EP1406469A2 (fr) 2004-04-07
EP1406469A3 EP1406469A3 (fr) 2008-03-26
EP1406469B1 true EP1406469B1 (fr) 2010-04-07

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EP03021040A Revoked EP1406469B1 (fr) 2002-09-30 2003-09-17 Compensateur de la rétroaction dans les systèmes d'amplification acoustique, prothèse auditive, procédé pour la compensation de la rétroaction et utilisation de ce procédé dans les prothèses auditives

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US (2) US6931137B2 (fr)
EP (1) EP1406469B1 (fr)
AT (1) ATE463934T1 (fr)
DE (2) DE10245667B4 (fr)
DK (1) DK1406469T3 (fr)

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US6876751B1 (en) * 1998-09-30 2005-04-05 House Ear Institute Band-limited adaptive feedback canceller for hearing aids
DK1119218T3 (en) * 2000-01-21 2018-09-10 Oticon As Electromagnetic feedback reduction in a communication device
US20040231862A1 (en) * 2003-05-22 2004-11-25 Kirn Michael D. Corrosion monitoring station
DE102005019149B3 (de) * 2005-04-25 2006-08-31 Siemens Audiologische Technik Gmbh Hörhilfevorrichtung mit Kompensation von akustischen und elektromagnetischen Rückkopplungssignalen
KR100678770B1 (ko) * 2005-08-24 2007-02-02 한양대학교 산학협력단 궤환 신호 제거 기능을 구비한 보청기
US20070183609A1 (en) * 2005-12-22 2007-08-09 Jenn Paul C C Hearing aid system without mechanical and acoustic feedback
DE102006020832B4 (de) * 2006-05-04 2016-10-27 Sivantos Gmbh Verfahren zum Unterdrücken von Rückkopplungen bei Hörvorrichtungen
US8280088B2 (en) * 2006-05-19 2012-10-02 Siemens Audiologische Technik Gmbh Hearing apparatus with feedback detection and corresponding method
EP1976334A3 (fr) * 2007-03-29 2016-10-05 Sivantos GmbH Procédé d'adaptation d'un appareil auditif avec normalisation des valeurs de traitement
JP5136396B2 (ja) * 2008-12-25 2013-02-06 ヤマハ株式会社 ハウリング抑制装置
DE102009031135A1 (de) * 2009-06-30 2011-01-27 Siemens Medical Instruments Pte. Ltd. Hörvorrichtung und Verfahren zur Unterdrückung von Rückkopplungen
EP2284833A1 (fr) * 2009-08-03 2011-02-16 Bernafon AG Procédé de surveillance de l'influence du bruit ambiant sur un filtre adaptatif pour la suppression de l'effet Larsen

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WO1995028034A2 (fr) * 1994-04-12 1995-10-19 Philips Electronics N.V. Systeme d'amplification de signaux a suppression d'echo amelioree
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AU6168099A (en) * 1998-09-30 2000-04-17 House Ear Institute Band-limited adaptive feedback canceller for hearing aids
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Also Published As

Publication number Publication date
DE50312584D1 (de) 2010-05-20
ATE463934T1 (de) 2010-04-15
DE10245667A1 (de) 2004-04-15
US7174027B2 (en) 2007-02-06
DE10245667B4 (de) 2004-12-30
US20040101147A1 (en) 2004-05-27
EP1406469A3 (fr) 2008-03-26
EP1406469A2 (fr) 2004-04-07
DK1406469T3 (da) 2010-08-02
US6931137B2 (en) 2005-08-16
US20050135646A1 (en) 2005-06-23

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