EP2357852B1 - Procédé de compensation d'un signal de contre-réaction et dispositif auditif - Google Patents

Procédé de compensation d'un signal de contre-réaction et dispositif auditif Download PDF

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Publication number
EP2357852B1
EP2357852B1 EP11150197.9A EP11150197A EP2357852B1 EP 2357852 B1 EP2357852 B1 EP 2357852B1 EP 11150197 A EP11150197 A EP 11150197A EP 2357852 B1 EP2357852 B1 EP 2357852B1
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EP
European Patent Office
Prior art keywords
signal
input
feedback
compensation
transducer apparatus
Prior art date
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Application number
EP11150197.9A
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German (de)
English (en)
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EP2357852A1 (fr
Inventor
Sebastian Pape
Stefan Petrausch
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Sivantos Pte Ltd
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Siemens Medical Instruments Pte Ltd
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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
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R3/00—Circuits for transducers, loudspeakers or microphones
    • H04R3/02—Circuits for transducers, loudspeakers or microphones for preventing acoustic reaction, i.e. acoustic oscillatory feedback

Definitions

  • the present invention relates to a method of compensating a feedback signal in a hearing apparatus having input transducer means, signal processing means and output transducer means by compensating for a feedback signal fed back from the output transducer means or the signal processing means to the input transducer means.
  • the present invention relates to a corresponding hearing device.
  • a hearing device is understood here to mean any sound-transmitting device which can be worn in or on the head, in particular a hearing device, a headset, headphones and the like.
  • Hearing aids are portable hearing aids that are used to care for the hearing impaired.
  • different types of hearing aids such as behind-the-ear hearing aids (BTE), hearing aid with external receiver (RIC: receiver in the canal) and in-the-ear hearing aids (IDO), e.g. Concha hearing aids or canal hearing aids (ITE, CIC).
  • BTE behind-the-ear hearing aids
  • RIC hearing aid with external receiver
  • IDO in-the-ear hearing aids
  • ITE canal hearing aids
  • 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 carrying behind the ear, one or more microphones 2 for receiving the sound from the environment are installed.
  • 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.
  • 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
  • an adaptive filter simulates the acoustic feedback path by minimizing the energy after the subtraction point.
  • the problem is that the desired or useful signal from the point of view of the coupling compensator forms the interference signal.
  • the wanted signal is usually strongly correlated with the feedback signal, so that it is difficult to discriminate between the feedback signal and the wanted signal.
  • the correct adjustment of the adaptation speed for the feedback path is extremely important. If the adaptation is too slow, a feedback whistle will be audible for a period of time. If the adaptation is too fast, so-called musical artifacts result, ie. H. the feedback compensator tries to suppress the useful signal. Frequently, feedback detectors are necessary for the correct adaptation speed. In addition, the performance of the feedback detector is very important to the performance of the complete feedback compensator.
  • FIG. 2 A typical construction of a feedback compensator in a hearing aid with a feedback detector is shown in FIG. 2 shown.
  • a microphone 10 picks up a sound signal and passes it on to a signal processing device 11.
  • the output signal resulting from the signal processing device 11 is forwarded to an output transducer or loudspeaker 12.
  • the sound leaving the speaker 13 penetrates part of the eardrum or ear and the other part is fed back as a feedback signal 14 via the respective current feedback path (RKP) 15 to the microphone 10.
  • the feedback sound is summed with the useful signal 16 and the sum gives the acoustic input signal for the microphone 10.
  • the signal processing device 11 has a conventional signal processor (SP) 17 and a feedback compensator (RKK) 18. In addition, a feedback detector (RKD) 19 is provided.
  • the output signal of the signal processor 17 is supplied to both the speaker 12 and the feedback compensator 18. The latter simulates the feedback path and supplies a corresponding compensation signal, which is subtracted by a subtractor 20 from the signal of the microphone 10. The resulting signal is provided to the signal processor 17 as an input. In addition, it becomes the
  • the signal 30 from the microphone 10 and the difference signal 40 to the subtracter 20 are fed to the feedback detector 19, which determines whether or not there is a feedback situation.
  • the feedback compensator 18 and possibly also the signal processor 17 are controlled.
  • the feedback compensator 18 is often an adaptive filter which attempts to model the acoustic feedback path. Ideally, the feedback compensator 18 filters the output signal of the signal processor 17 in the same way as the acoustic feedback path 15. This results in a complete suppression of the feedback signal 14 at the subtracter 20. Often, however, the feedback compensator 18 is mismatched or simply too slow for the rapid changes of the feedback path. Therefore, often one or more feedback detectors 19 are necessary to adjust the rate of adaptation of the feedback compensator 18.
  • These feedback detectors 19 typically analyze either the microphone signal 30 before the subtractor 20 or the compensated signal 40 after the subtractor 20, which should be feedback-free. It is also possible, as already indicated above, to influence the signal processor 17, for example, by reducing the gain in such a way that feedback whistling is avoided.
  • the object of the present invention is thus to recognize a feedback situation as quickly as possible and, if appropriate, to take appropriate compensation measures.
  • a corresponding method and a corresponding hearing device are to be provided.
  • this object is achieved by a method according to claim 1.
  • Determining a likelihood is also understood to mean the “detection” (ie 100% probability) of incisions (peak minima).
  • a feedback situation can therefore be recognized solely by the fact that equidistant notches are detected in the transfer function and their distance to a transfer function with compensated feedback is ascertained. Depending on this, then a corresponding compensation can be initiated without it has already come to a feedback whistle.
  • the determination of the probability takes place during a speech break during the intended operation of the hearing device.
  • a speech break during the intended operation of the hearing device.
  • the transfer function from the input signal to the output signal may correspond to a comb filter. Taking into account the feedback signal then results for the useful signal, a constant transfer function.
  • the determination of the probability can take place in a noisy frequency range of the input signal.
  • a broadband input signal is usually given, in which numerous incisions can be clearly pronounced.
  • the feedback signal can be verified by frequency or phase modulating the output signal and the cuts in frequency or phase modulation to be analyzed.
  • the security of the decision of the existence of a feedback situation can be increased.
  • the compensation is carried out by an adaptive filter and the adaptation speed is changed as a function of the determined probability.
  • the changing of the compensation may be such that the transfer function of a compensated signal resulting from a mixing of the input signal with a compensation signal for compensating the feedback signal to the output signal in the largest part of a predetermined spectral range to be influenced by the compensating essentially runs without gradients. If so, ideal compensation of the feedback signal is achieved.
  • the basic approach of the present invention is to detect mis-adaptation to the feedback path without audible feedback whistling.
  • the invention makes use of the comb filter effect, which is based on the superimposition of a useful signal with a feedback signal. Adding two correlated signals with a small delay results in a destructive or constructive overlay, and cuts or peaks can be detected in the frequency response (cf. FIG. 3 ).
  • the feedback compensator FBC
  • the transfer function TM of the microphone signal 30 received from the microphone 10 see FIG FIG. 2
  • the transfer function TC of the compensated signal 40 to the compensated output signal is ideally perfectly flat, as shown in FIG FIG. 4 is shown. It has no slope and is constant over the whole considered frequency range (here from 2000 to 4000 Hz).
  • the transfer function TM of the microphone input 16 to the output 13 is an infinite impulse response of a comb filter having a typical distribution with significant frequency spikes.
  • the feedback compensation is 80%. So there is a mismatch of 20%.
  • FIG. 5 Before frequency peaks 22 in the transfer function TM of the microphone signal 30 to the output signal 13 somewhat pronounced. This mismatch results in that the transfer function TC of the compensated signal to the output signal 13 is no longer completely flat, which is shown in FIG. 6 is indicated.
  • the transfer functions of FIGS. 9 and 10 In the transfer function TM of the microphone signal now distinct frequency peaks 25 can be seen.
  • the transfer function TC of the compensated signal 40 then also has distinct peaks 26 equally spaced apart from one another.
  • the transfer function TM from the microphone signal 30 is primarily characterized by cuts 21 (minima compared to the functional average value) at 100% compensation, while at low compensation (30%) the transfer function is characterized primarily by frequency peaks 26 (maxima compared to the functional mean value) is.
  • the transition from the incision-embossed transfer function to the peak embossed transfer function is fluid. The transition can be observed without audible artifacts. This is the basis of the present invention.
  • the quality of the feedback adaptation can be judged.
  • the feedback path can be optimized before the hearing aid begins to whistle or with which the gain can be reduced before the device begins to whistle.
  • the advantage of using the comb filter effect is therefore to be able to predict the occurrence of feedback whistles before it starts.
  • the feedback path can be adapted early enough to prevent whistling.
  • the invention is therefore to examine the input signal with respect to contained comb filter portions in order to detect feedback-critical states at an early stage. In order to clearly recognize the comb filter as an effect of the incoming loudspeaker or receiver signal, several possibilities have been proposed above.
  • phase shaker in which the modulation of the output signal is used.
  • a modulation is impressed on the output signal, which then leads to a vibrating movement of the notches in the frequency response of the input signal. This provides an additional feature to identify feedback.
  • FIG. 11 shows an implementation of the method described above for determining a change of a feedback situation or for adaptation to a changed feedback situation in a hearing aid.
  • the structure of the hearing device including the feedback path 15 substantially corresponds to that of FIG. 2 , It is therefore with respect to in FIG the same components and reference numbers to the description of FIG. 2 directed.
  • the hearing aid of FIG. 11 a notch detector (ND) 24, a threshold decision unit (TD) 27, a modulation detector 28 (MD), and an AND gate (AND) 29.
  • the notch detector 24 picks up the microphone signal 30 and determines therefrom a probability w for a notch (incision, ie acute minimum) and the corresponding frequency f of the notch.
  • the threshold value decision unit 27 it is decided whether there is a deviation from the ideal case by comparing the probability w with a threshold value.
  • a corresponding output signal is supplied to the AND gate 29.
  • the notch frequency f is supplied to the notch detector 24 to the modulation detector 28. This examines whether the Notchfrequenz f performs a vibrating motion. A corresponding output signal is passed to the AND gate 29. If the respective conditions are met in the two decision units 27 and 28, then the feedback compensator (RKK) 18 is correspondingly driven by the output signal of the AND gate 29, z. B. the adaptation speed is changed.
  • RKK feedback compensator
  • the hearing aid has a phase modulator (PM) 31 after the signal processor (SP) 17, which phase-modulates the output signal to the loudspeaker 12.
  • the feedback signal 14 is also phase modulated and the modulation is recordable via the signal path through the microphone 10 and the notch detector 24 in the modulation detector 28. If there is modulation and the probability for a notch falls below a certain threshold (cf. FIG. 5 . 7 and 9 ), the adaptation speed of the feedback compensator is increased.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Circuit For Audible Band Transducer (AREA)

Claims (9)

  1. Procédé de compensation d'un signal de contre-réaction sur un appareil auditif comprenant un dispositif convertisseur d'entrée (10), un dispositif de traitement de signal (17) destiné à traiter un signal d'entrée (30) délivré par le dispositif convertisseur d'entrée (10) en un signal de sortie et un dispositif convertisseur de sortie (12) destiné à convertir le signal de sortie en un signal de sortie sonore (13) par
    - compensation d'un signal de contre-réaction (14) qui est renvoyé par le dispositif convertisseur de sortie (12) ou le dispositif de traitement de signal (17) au dispositif convertisseur d'entrée (10),
    caractérisé par
    - la détermination d'une probabilité (w) avec laquelle le spectre d'un signal d'entrée, qui est issu directement du dispositif convertisseur d'entrée (10) ou qui est un signal différentiel entre le signal provenant directement du dispositif convertisseur d'entrée (10) et un signal de compensation servant à la compensation, possède plusieurs creux (21) équidistants les uns des autres,
    - la modification de la compensation ou d'un gain du dispositif de traitement de signal (17) en fonction de la probabilité (w) déterminée.
  2. Procédé selon la revendication 1, selon lequel la détermination de la probabilité (w) est effectuée dans une phase de parole pendant l'utilisation de l'appareil auditif conformément à sa fonction.
  3. Procédé selon la revendication 1 ou 2, selon lequel une fonction de transfert (TM) du signal d'entrée vers le signal de sortie correspond à un filtre en peigne.
  4. Procédé selon l'une des revendications précédentes, selon lequel la détermination de la probabilité est effectuée dans une plage de fréquences du signal d'entrée perturbée par du bruit.
  5. Procédé selon l'une des revendications précédentes, selon lequel le signal de contre-réaction (14) est vérifié en ce que le signal de sortie est modulé en phase et les creux (21) sont analysés du point de vue de la modulation de phase.
  6. Procédé selon l'une des revendications précédentes, selon lequel la compensation est effectuée par le biais d'un filtre adaptatif (18) et la vitesse d'adaptation est modifiée en fonction de la probabilité (w).
  7. Procédé selon la revendication 6, selon lequel la modification de la compensation est effectuée de telle sorte que la fonction de transfert d'un signal compensé (40), lequel est produit par un mélange du signal d'entrée (30) avec un signal de compensation pour la compensation du signal de contre-réaction, vers le signal de sortie se déroule sensiblement sans gradient dans la plus grande partie d'une plage spectrale prédéfinie qui doit être influencée par la compensation.
  8. Procédé selon l'une des revendications précédentes, selon lequel les creux (21) du signal équidistants les uns des autres sont comparés après le dispositif convertisseur d'entrée (10) directement avec les mêmes creux espacés d'un signal compensé (40) en vue de la validation d'une détection d'une situation de contre-réaction.
  9. Appareil auditif comprenant
    - un dispositif convertisseur d'entrée (10),
    - un dispositif de traitement de signal (17) destiné à traiter le signal d'entrée (30) délivré par le dispositif convertisseur d'entrée (10) en un signal de sortie,
    - un dispositif convertisseur de sortie (12) destiné à convertir le signal de sortie en un signal de sortie sonore (13) et
    - un dispositif de compensation (18) destiné à compenser un signal de contre-réaction (14) qui est renvoyé par le dispositif convertisseur de sortie (12) ou le dispositif de traitement de signal (17) au dispositif convertisseur d'entrée (10),
    caractérisé par
    - un dispositif de détection (24) destiné à déterminer une probabilité (w) avec laquelle le spectre du signal d'entrée (30), qui est issu directement du dispositif convertisseur d'entrée (10) ou qui est un signal différentiel entre le signal provenant directement du dispositif convertisseur d'entrée (10) et un signal de compensation servant à la compensation, possède plusieurs creux (21) équidistants les uns des autres,
    - le dispositif de compensation (18) pouvant être commandé en fonction de la probabilité (w) déterminée.
EP11150197.9A 2010-02-09 2011-01-05 Procédé de compensation d'un signal de contre-réaction et dispositif auditif Active EP2357852B1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102010007336A DE102010007336B4 (de) 2010-02-09 2010-02-09 Verfahren zum Kompensieren eines Rückkopplungssignals und Hörvorrichtung

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EP2357852A1 EP2357852A1 (fr) 2011-08-17
EP2357852B1 true EP2357852B1 (fr) 2015-07-22

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US (1) US8396236B2 (fr)
EP (1) EP2357852B1 (fr)
DE (1) DE102010007336B4 (fr)
DK (1) DK2357852T3 (fr)

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Publication number Priority date Publication date Assignee Title
KR101671389B1 (ko) * 2010-03-05 2016-11-01 삼성전자 주식회사 가변 대역 폭 적응 노치 필터, 및 가변 대역 폭 적응 노치 필터를 이용하여 하울링을 제거하는 방법 및 장치
US9763006B2 (en) 2015-03-26 2017-09-12 International Business Machines Corporation Noise reduction in a microphone using vowel detection

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DE10162559B4 (de) 2001-12-19 2006-08-10 Siemens Ag Verfahren und Vorrichtung zur Unterdrückung von periodischen Störsignalen
EP1602259A2 (fr) * 2003-03-04 2005-12-07 Oticon A/S Filtre numerique et dispositif d'audition
US8116473B2 (en) * 2006-03-13 2012-02-14 Starkey Laboratories, Inc. Output phase modulation entrainment containment for digital filters
DE102006029194B4 (de) 2006-06-26 2010-04-15 Siemens Audiologische Technik Gmbh Vorrichtung und Verfahren zur Schrittweitensteuerung eines adaptiven Filters
US8045738B2 (en) * 2008-10-31 2011-10-25 Zounds Hearing, Inc. System for managing feedback

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US20110194715A1 (en) 2011-08-11
US8396236B2 (en) 2013-03-12
DE102010007336A1 (de) 2011-08-11
DK2357852T3 (da) 2015-11-02
EP2357852A1 (fr) 2011-08-17
DE102010007336B4 (de) 2013-08-08

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