EP1401242B1 - Compensation de la rétroaction pour prothèses auditives avec système d'estimation de la distance - Google Patents

Compensation de la rétroaction pour prothèses auditives avec système d'estimation de la distance Download PDF

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Publication number
EP1401242B1
EP1401242B1 EP03021037A EP03021037A EP1401242B1 EP 1401242 B1 EP1401242 B1 EP 1401242B1 EP 03021037 A EP03021037 A EP 03021037A EP 03021037 A EP03021037 A EP 03021037A EP 1401242 B1 EP1401242 B1 EP 1401242B1
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EP
European Patent Office
Prior art keywords
signal
feedback
facility
reduction
input
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.)
Expired - Lifetime
Application number
EP03021037A
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German (de)
English (en)
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EP1401242A3 (fr
EP1401242A2 (fr
Inventor
Torsten Dr. Niederdränk
Herve Schulz
Tom Weidner
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Sivantos GmbH
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Siemens Audioligische Technik GmbH
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Publication of EP1401242A3 publication Critical patent/EP1401242A3/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 present invention relates to a device for feedback compensation in hearing aids with a signal input device for receiving an input signal including a feedback signal, a feedback reduction device for adjustable reduction or attenuation of the feedback signal and a signal output device for outputting a signal output with reduced feedback signal. Moreover, the present invention relates to a corresponding method for feedback compensation.
  • the hearing aid gain is greater than the feedback attenuation, the feedback is noticeable by a whistling of the hearing aid, which is very unpleasant for the hearing aid wearer.
  • feedback compensation is not mandatory, but feedback compensation could still result in artifacts.
  • Another problem is when the feedback signal, for example, in a very tight earmold relatively small and the useful signal is relatively large. Such a constellation often leads to a misadaptation of the hearing device to the feedback paths, which may also result in artifacts.
  • a hearing aid with improved separation of noise signals known.
  • a variable high pass filter having a cutoff frequency that is variable in response to the feedback control signal applied via the control input of the filter, and a sensor with feedback filter, level detector, and smoothing loop, wherein the sensor and the high pass filter cooperatively define both a settling time and a trip time , which is smaller than the settling time, high-frequency low-frequency signals are attenuated in response to the past timing of the filtered signal, so as to attenuate high-amplitude steady low-frequency noise signals.
  • the cutoff frequency is slowly increased in the presence of high frequency low frequency noise, but rapidly decreased when the noise ceases.
  • the object of the present invention is to provide efficient feedback compensation while reducing the risk of artifact formation.
  • a device for feedback compensation in hearing aids having a signal input device (3) for receiving an input signal, which is influenced by feedback, a feedback reduction device (5, 12, 13, 14) for adjustable reduction, compensation or attenuation of the feedback and signal output means (1) for outputting a reduced feedback portion output signal, and estimating means (6 to 11) connected between said signal input means (3) and said feedback reducing means (5, 12, 13, 14) and with determining from the input signal an estimated value of a system distance defined by the distance of the loop gain of the feedback system to its predetermined stability limit, such that parameters of the feedback reduction device (5, 12, 13, 14) can be controlled on the basis of the estimated value.
  • the above object is further achieved according to the invention by a method for feedback compensation in hearing aids by receiving an input signal which is influenced by a feedback, adjustable reducing, compensating or attenuating the feedback and outputting a output signal with a reduced feedback component, as well as estimating a system separation achieved by the distance of the loop gain of the feedback system is defined to its predetermined stability limit, and controlling the reducing, compensating or damping of the feedback based on the estimated value.
  • the invention is based on the idea that the amplification of a hearing aid in each frequency range must be below a stability limit at which the coupling begins and the hearing aid wearer or patient perceives a whistle.
  • the distance from the amplification of the hearing aid (more precisely the product of the amplification of the hearing aid with the gain of the feedback) to a stability limit V stable is referred to as system distance.
  • the stability limit is usually referred to as the situation in which the product of the feedback gain or attenuation and the loop gain is equal to one.
  • the system spacing is very important for the performance of an adaptive feedback compensation filter, as it detects the signal-to-noise ratios (S / N) for the adaptation.
  • the step size of an adaptive feedback compensator can be adapted to the system spacing or the stability reserve for improved adaptation behavior. It makes a clear difference whether the feedback compensator should adapt in the supercritical case or in the subcritical case.
  • the system spacing is estimated by detecting a first signal component and a second signal component of the input signal, forming an estimated signal for the second signal component in particular by means of a model from the first signal component and determining the estimated value from the difference between the estimated signal and the second signal component.
  • a model-based estimate of the system distance can be made and the function of a feedback compensator can be controlled or adjusted. If, for example, a very large system distance is detected, ie a very stable situation in which there is no feedback, then, for example, the feedback compensator is switched off or its parameters changed (eg extremely slow adaptation times). As a result, unnecessary artifacts can be avoided, even with critical input signals.
  • the function of the feedback compensator can be changed, for example, to a significantly increased adaptation speed. This would allow a faster adaptation and thus feedback suppression.
  • the estimation of the system distance can be based on a model, eg for speech. Conveniently, the input signal is decomposed into a high-frequency first signal component and a low-frequency second signal component. With two-channel devices, these signal components are already present.
  • the low-frequency signal components are generally not affected by the feedback, corresponding characteristics of the input signal, such as amplitude, modulation depth, etc., can be determined from the low-frequency signal component without the influence of a feedback disturbs.
  • the high-frequency components of the input signal can then be idealized from the characteristics of the low-frequency components without feedback.
  • a comparison between the estimated high-frequency signal component and the actual high-frequency signal component leads to the system distance with which the feedback compensation can be performed variably.
  • FIG. 1 concretely stated.
  • the feedback waveform is shown.
  • the output signal of a receiver 1 of a hearing device is fed back via a feedback path 2 to the microphone 3 of the hearing aid.
  • a useful signal for example speech, is fed into the microphone 3.
  • a hearing aid signal processing 4 amplifies the microphone signal to the output to the handset or loudspeaker 1.
  • a feedback compensator 5 simulates the feedback path 2 and subtracts the result from the input signal of the microphone 3, whereby the feedback path 2 is attenuated.
  • the feedback compensator 5 is constantly active and can lead to artifacts in hearing aids with a small feedback path, such as hearing aids with cross-connection or closed supply.
  • the operation of the feedback compensator 5 according to FIG. 2 to control in the simplest case on and off.
  • a estimation unit which estimates the system distance, so that the feedback compensator 5 is activated only at very low or negative Sytemabstand.
  • the estimating device consists of a high-pass filter 6 and a low-pass filter 7. These are connected in parallel to the usual signal path between the microphone 3 and hearing aid signal processing 4 and decompose the output signal of the microphone 3, ie the input signal of the hearing aid, into a high-frequency and a low-frequency component.
  • a feature extraction unit 8 or 9 is connected in each case.
  • the features obtained from the feature extraction unit 9 are linked to model data of a model 10 and the resulting data are compared in an evaluation unit 11 with the data of the feature extraction unit 8.
  • the comparison result is a measure of the system distance with which the feedback compensator 5 is driven.
  • the function of the estimation unit can be described as follows:
  • the input signal of the hearing aid is divided by the high-pass filter 6 and the low-pass filter 7 into a high-frequency part and a low-frequency part.
  • the threshold between high frequency and low frequency is chosen so that the usually occurring couplings are arranged in the high frequency range. For example, the threshold is 1.5 kHz.
  • the low-pass signal is examined in feature extraction unit 9 for salient features. Examples of such features are energy content in the frequency band, signal-to-noise ratio, etc. It is assumed that the signal in the low-frequency range is undisturbed, ie not affected by feedback. With the aid of the model 10, which reproduces, for example, the typical frequency response of a speech signal, the characteristics of the associated high-pass signal are estimated from the features of the low-pass signal and forwarded to the evaluation unit or the comparator 11. In parallel, the actual features of the high-pass signal in the feature extraction unit 8 are determined and also passed to the comparator 11. There, the actual features of the high-pass signal are compared with the estimated features of the high-pass signal.
  • the feedback compensator 5 can be switched off or operated minimized in its effect.
  • the estimated signal does not match the actual signal, then feedback can be assumed.
  • the corresponding feedback signal can be obtained, for example, from the difference between the two spectra of the estimated and the actual signal. If now through the feedback the system distance became too low or negative, the feedback compensator 5 can be activated. In the event, however, that the system distance is still large enough, for example more than 3 dB, the feedback compensator 5 also does not need to be activated here.
  • a suitable model 10 is stored for the respective current hearing situation, such as, for example, speech at rest, music, etc.
  • the appropriate model should be determined in real time and used for the estimation.
  • FIG. 3 Another embodiment of the feedback compensator control according to the invention is shown in FIG. 3 shown.
  • the hearing aid is already designed for multi-channel internal data processing. This means that the input signal, ie the output signal of the microphone 3, is split by the filters 6 and 7 into frequency bands. A feedback compensation takes place in the present case only in the high-pass signal.
  • a hearing aid signal processing 41, 42 is provided in each case. In front of the receiver 1, the signals of the two channels are added.
  • the estimation unit 8 to 11 After the input signal is already divided into several channels, the estimation unit 8 to 11 only needs to continue with the respective feature extraction.
  • the further signal processing is analogous to the embodiment of FIG. 2 ,
  • FIG. 4 Another embodiment of the present invention is in FIG. 4 played.
  • the hearing aid features not like in the case of FIG. 2 via a feedback compensator 5, but via a gain or compression control 12. With it, the gain or the compression of the hearing aid can be varied. In the event that the system distance is too low, either by the useful signal or the feedback signal, the amplification of the hearing aid can be reduced so far that it works again stable.
  • the necessary system spacing is provided by the comparator 11 as in the previous examples. Incidentally, the entire estimation unit 6 to 11 corresponds to that of the embodiment according to FIG. 2 ,
  • FIG. 5 an embodiment of the present invention is shown, which is essentially a combination of the embodiments of the Figures 3 and 4 equivalent.
  • the internally dual-channel hearing aid is freed of feedback signals by a gain control 12 in the high frequency channel.
  • FIG. 6 Another embodiment is in FIG. 6 shown.
  • the structure of the hearing aid corresponds to that of FIG. 2 or from FIG. 4 ,
  • the feedback is detected here in the input signal by a feedback or oscillation detector 13.
  • a notch filter control 14 utilizes the output signal of the oscillation detector 13 and thus controls a narrowband or notch filter 15. Since a hearing aid coupling becomes noticeable due to a resonance peaking and corresponding whistling, it can also be largely suppressed by a notch filter 15.
  • the notch filter 15 is connected between the hearing aid signal processing 4 and the handset 1 for this purpose.
  • the notch filter control 14 also uses the system distance from the comparator 11.

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  • Acoustics & Sound (AREA)
  • Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • General Health & Medical Sciences (AREA)
  • Signal Processing (AREA)
  • Amplifiers (AREA)
  • Measurement Of Velocity Or Position Using Acoustic Or Ultrasonic Waves (AREA)
  • Radar Systems Or Details Thereof (AREA)
  • Length Measuring Devices Characterised By Use Of Acoustic Means (AREA)
  • Circuit For Audible Band Transducer (AREA)
  • Tone Control, Compression And Expansion, Limiting Amplitude (AREA)

Claims (14)

  1. Dispositif pour la compensation de la rétroaction pour prothèses auditives comprenant
    un dispositif d'entrée de signal (3) pour la réception d'un signal d'entrée qui est influencé par une rétroaction,
    un dispositif de réduction de rétroaction (5, 12, 13, 14) pour la réduction, la compensation ou l'amortissement réglable de la rétroaction et
    un dispositif de sortie de signal (1) pour la délivrance d'un signal de sortie avec fraction de rétroaction réduite,
    caractérisé par
    un dispositif d'estimation (6 à 11), qui est monté entre le dispositif d'entrée de signal (3) et le dispositif de réduction de rétroaction (5, 12, 13, 14) et avec lequel, à partir du signal d'entrée, on peut déterminer une valeur estimative d'un espacement de système, qui est définie par la distance de l'amplification de circuit du système à rétroaction à sa limite de stabilité prédéfinie, de sorte que des paramètres du dispositif de réduction de rétroaction (5, 12, 13, 14) peuvent être commandés à l'aide de la valeur estimative.
  2. Dispositif selon la revendication 1, une première fraction de signal et une seconde fraction de signal pouvant être saisies avec le dispositif d'estimation (6 à 11) à partir du signal d'entrée, un signal d'estimation pour la seconde fraction de signal pouvant être élaboré en particulier au moyen d'un modèle à partir de la première fraction de signal et la valeur estimative pouvant être déterminée à partir de la différence du signal d'estimation et de la seconde fraction de signal.
  3. Dispositif selon la revendication 2, la première fraction de signal correspondant à une fraction à haute fréquence du signal d'entrée et la seconde fraction de signal à une fraction à basse fréquence du signal d'entrée.
  4. Dispositif selon la revendication 2 ou 3, des caractéristiques pouvant être extraites des fractions de signal pour le traitement ultérieur.
  5. Dispositif selon l'une quelconque des revendications 1 à 4, le dispositif de réduction de rétroaction (5, 12, 13, 14) comprenant un compensateur d'asservissement (5).
  6. Dispositif selon l'une quelconque des revendications 1 à 5, le dispositif de réduction de rétroaction (5, 12, 13, 14) comprenant une commande d'amplification/compression (12) pour une prothèse auditive.
  7. Dispositif selon l'une quelconque des revendications 1 à 6, le dispositif de réduction de rétroaction (5, 12, 13, 14) comprenant au moins un détecteur d'oscillation (13) et au moins un dispositif de filtre à bande étroite (14) pour la suppression des vibrations sur la base de la valeur estimative.
  8. Procédé pour la compensation de la rétroaction pour prothèses auditives par
    réception d'un signal d'entrée qui est influencé par une rétroaction,
    réduction, compensation ou amortissement réglable de la rétroaction et
    sortie d'un signal de sortie avec une fraction de rétroaction réduite,
    caractérisé par
    l'estimation d'une distance de système qui est définie par la distance de l'amplification de circuit du système à rétroaction à sa limite de stabilité prédéfinie et
    la commande de la réduction, de la compensation ou de l'amortissement de la rétroaction à l'aide de la valeur estimative.
  9. Procédé selon la revendication 8, l'estimation s'effectuant par les étapes de la saisie d'une première fraction de signal et d'une seconde fraction de signal du signal d'entrée, de la formation d'un signal de prévision pour la seconde fraction de signal à partir de la première fraction de signal en particulier au moyen d'un modèle et de la détermination de la valeur estimative à partir de la différence du signal de prévision et de la seconde fraction de signal.
  10. Procédé selon la revendication 9, la première fraction de signal correspondant à une fraction à haute fréquence du signal d'entrée et la seconde fraction de signal à une fraction à basse fréquence du signal d'entrée.
  11. Procédé selon la revendication 9 ou 10, une extraction de caractéristiques du signal à partir des fractions de signal pour le traitement ultérieur ayant lieu après la saisie de la première et de la seconde fractions de signal.
  12. Procédé selon l'une quelconque des revendications 8 à 11, la réduction ou l'amortissement du signal de rétroaction s'effectuant par une compensation adaptative d'asservissement.
  13. Procédé selon l'une quelconque des revendications 8 à 11, la réduction ou l'amortissement du signal de rétroaction s'effectuant par la commande de l'amplification/compression d'une prothèse auditive.
  14. Procédé selon l'une quelconque des revendications 8 à 11, la réduction ou l'amortissement du signal de rétroaction s'effectuant par la détection d'une vibration et l'extraction par filtration à bande étroite de cette vibration.
EP03021037A 2002-09-23 2003-09-17 Compensation de la rétroaction pour prothèses auditives avec système d'estimation de la distance Expired - Lifetime EP1401242B1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE10244184A DE10244184B3 (de) 2002-09-23 2002-09-23 Feedbackkompensation für Hörgeräte mit Systemabstandsschätzung
DE10244184 2002-09-23

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EP1401242A2 EP1401242A2 (fr) 2004-03-24
EP1401242A3 EP1401242A3 (fr) 2008-02-20
EP1401242B1 true EP1401242B1 (fr) 2008-12-03

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US (1) US20040109578A1 (fr)
EP (1) EP1401242B1 (fr)
AT (1) ATE416591T1 (fr)
DE (2) DE10244184B3 (fr)
DK (1) DK1401242T3 (fr)

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Publication number Publication date
EP1401242A3 (fr) 2008-02-20
DE10244184B3 (de) 2004-04-15
DE50310852D1 (de) 2009-01-15
EP1401242A2 (fr) 2004-03-24
DK1401242T3 (da) 2009-04-06
ATE416591T1 (de) 2008-12-15
US20040109578A1 (en) 2004-06-10

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