EP1401242A2 - 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

Info

Publication number: EP1401242A2
Authority: EP; European Patent Office
Prior art keywords: signal; feedback; component; compensation; input
Prior art date: 2002-09-23
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.): Granted

Application number

EP03021037A

Other languages

German (de)

English (en)

Other versions

EP1401242A3 (fr

EP1401242B1 (fr

Inventor

Torsten Dr. Niederdränk

Herve Schulz

Tom Weidner

Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)

Sivantos GmbH

Original Assignee

Siemens Audiologische Technik GmbH

Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)

2002-09-23

Filing date

2003-09-17

Publication date

2004-03-24

2003-09-17 Application filed by Siemens Audiologische Technik GmbH filed Critical Siemens Audiologische Technik GmbH

2004-03-24 Publication of EP1401242A2 publication Critical patent/EP1401242A2/fr

2008-02-20 Publication of EP1401242A3 publication Critical patent/EP1401242A3/fr

2008-12-03 Application granted granted Critical

2008-12-03 Publication of EP1401242B1 publication Critical patent/EP1401242B1/fr

2023-09-17 Anticipated expiration legal-status Critical

Status Expired - Lifetime 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; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
- H04R25/00—Electric hearing aids
- H04R25/45—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback
- H04R25/453—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback electronically

Definitions

the present invention relates to a device for feedback compensation in hearing aids with a signal input device for recording an input signal including a feedback signal, a feedback reducing device for adjustable reduction or Attenuation of the feedback signal and a signal output device to output an output signal with reduced Feedback signal.
a signal input device for recording an input signal including a feedback signal, a feedback reducing device for adjustable reduction or Attenuation of the feedback signal and a signal output device to output an output signal with reduced Feedback signal.
the present concerns Invention a corresponding method for feedback compensation.
Unwanted feedback is often found in hearing aids (Feedback) of the audio signal emitted by the listener to the Microphone of the hearing aid instead. This feedback takes place via different feedback paths (feedback paths).
Such one Path is e.g. the sound transmission in air if that Earpiece of a behind-the-ear hearing aid or an in-the-ear hearing aid is leaking.
Another feedback path may exist over the bones of the hearing aid wearer back to the hearing aid.
the hearing aid gain is greater than the feedback attenuation is the feedback by whistling the Hearing aid noticeable, which is very uncomfortable for the hearing aid wearer is.
the hearing aid reinforcement is less than the feedback attenuation is one Feedback compensation is not mandatory, one is feedback compensation carried out under certain circumstances could Lead artifacts.
Another problem is when the feedback signal e.g. relatively small and with a very dense earmold the useful signal is relatively large. Such a constellation often leads to an incorrect adaptation of the hearing aid to the feedback paths, which can also result in artifacts.
the object of the present invention is a powerful feedback compensation is available too the risk of artefact formation is reduced.
this object is achieved by a device for feedback compensation in hearing aids with a Signal input device (3) for receiving an input signal, that is affected by feedback, one Feedback reduction device (5, 12, 13, 14) for adjustable reduction, compensation or damping of the Feedback and a signal output device (1) for output an output signal with a reduced feedback component, and an estimation device (6 to 11), which between the signal input device (3) and the feedback reduction device (5, 12, 13, 14) is switched and with an estimated value of a system distance from the input signal, which by the distance of the loop gain of the feedback System to its specified stability limit is defined, can be determined so that parameters of the feedback reduction device (5, 12, 13, 14) using the Are taxable.
the above-mentioned object is also achieved according to the invention by a method for feedback compensation in hearing aids by picking up an input signal through a Feedback is influenced, adjustable reducing, compensating or attenuating the feedback and outputting one Output signal with a reduced feedback component, as well Estimate a system distance by the distance of the Circular gain of the feedback system to its given Stability limit is defined, and controlling the reduction, Compensating or damping the feedback based on of the estimate.
the invention is based on the idea that the amplification of a hearing device in each frequency range must be below a stability limit at which the coupling begins and the hearing device wearer or patient perceives a whistle.
the distance from the amplification of the hearing device (more precisely the product of the amplification of the hearing device with the amplification of the feedback) to a stability limit V stable is called the system distance.
the stability limit is usually the situation in which the product of feedback gain or loss and loop gain is equal to one.
the system distance is for the performance of an adaptive feedback compensation filter very important since it has the signal-to-noise ratios (S / N) for the adaptation.
the step size of an adaptive feedback compensator can for an improved adaptation behavior to the system distance or the stability reserve are adjusted. It makes a clear difference whether the feedback compensator adapt in the supercritical case or in the subcritical case should.
the system distance is advantageously estimated by detecting a first signal component and one second signal component of the input signal, forming one Estimation 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 second signal component.
a model-based Estimation of the system distance can be made and controlled the function of a feedback compensator or be adjusted. For example, becomes a very large one System distance recognized, so a very stable situation, in who has no feedback, for example the feedback compensator switched off or changed its parameters (e.g. extremely slow adaptation times). This can make unnecessary Artifacts avoided even with critical input signals become.
the function of the Feedback compensator e.g. to a significantly increased adaptation speed to be changed. That would be one faster adaptation and thus feedback suppression possible.
the system distance estimate can be based on a model, e.g. done for speech.
the input signal becomes a high frequency first signal component and a low-frequency second Disassembled signal portion. In the case of two-channel devices, these are Signal components before.
the low-frequency hearing aids Signal components are generally not affected by the feedback corresponding characteristics of the input signal such as amplitude, depth of modulation etc. from the low-frequency signal component can be determined without the influence of feedback is noticeable. With The high-frequency components can then be modeled of the input signal from the characteristics of the low frequency Estimate shares idealized without feedback. A comparison between the estimated high-frequency signal component and the actual high-frequency signal component leads to System distance with which the feedback compensation is variable can be carried out.
the exemplary embodiments described below represent preferred embodiments of the present invention.
1 shows the feedback signal curve in particular played.
the output signal of a The listener 1 of a hearing device is connected via a feedback path 2 coupled back to the microphone 3 of the hearing aid.
Next to the Feedback signal also becomes a useful signal, e.g. Language in which Microphone 3 fed.
Hearing aid signal processing 4 amplifies the microphone signal to the output to the listener respectively Speaker 1.
a feedback compensator 5 simulates the feedback path 2 and subtracts the result from the input signal of the microphone 3, which dampens feedback path 2.
the feedback compensator 5 is constantly active and can be used with hearing aids with small Feedback path, such as hearing aids with a cross connection or closed supply lead to artifacts.
An estimation unit is used for control used, which estimates the system distance, so the Feedback compensator 5 only with a very low or negative System distance is activated.
the estimation facility exists from a high pass filter 6 and a low pass filter 7. These are parallel to the usual signal path between microphone 3 and hearing aid signal processing 4 switched and disassemble that Output signal of the microphone 3, i.e. the input signal of the Hearing aids, in a high frequency and a low frequency Proportion of.
a feature extraction unit 8 or 9 switched.
the from the feature extraction unit 9 obtained characteristics are with model data of a model 10 linked and the resulting data are in one Evaluation unit 11 with the data of the feature extraction unit 8 compared.
the comparison result is a measure of the system distance with which the feedback compensator 5 is controlled becomes.
the function of the estimation unit can be described as follows
the input signal of the hearing aid is through the high pass filter 6 and the low pass filter 7 in a high frequency and disassembled a low frequency portion.
the threshold between High frequency and low frequency are chosen so that the couplings that usually occur in the high-frequency range are arranged. For example, the Threshold at 1.5 kHz.
the low-pass signal is in the feature extraction unit 9 examined for outstanding 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, i.e. from a feedback is not affected.
model 10 the for example the typical frequency response of a speech signal reproduces, the characteristics of the low-pass signal Characteristics of the associated high-pass signal estimated and on the evaluation unit or the comparator 11 is forwarded.
the actual characteristics of the high-pass signal in the feature extraction unit 8 determined and also passed to the comparator 11. There the actual characteristics of the high pass signal with the estimated features of the high-pass signal are compared. voices the characteristics of the actual and the estimated signal match, i.e.
the feedback compensator 5 can be switched off or in its Effects are minimized. Is that true? estimated signal does not match the actual signal, feedback can be assumed.
the corresponding Feedback signal can, for example, from the Difference between the two spectra of the estimated and the actual Signal can be obtained. If now through the feedback the system distance became too small or negative, the Feedback compensator 5 can be activated. In the event, however, that the system distance is still large enough, e.g. more than 3 dB, the feedback compensator 5 does not need here either to be activated.
this feedback compensator control Prerequisite for the functionality of this feedback compensator control is that for the current listening situation such as language at rest, music etc. suitable model 10 is stored. The right one Model should be determined in real time and for estimation be used.
FIG 3. Another embodiment of the feedback compensator control according to the invention is shown in FIG 3.
the hearing aid is already for multi-channel internal data processing designed. This means that the input signal, i.e. the Output signal of the microphone 3, through the filters 6 and 7 in Frequency bands is broken down. A feedback compensation takes place in the present case only in the high pass signal. Hearing aid signal processing is in each of the channels 41, 42 are provided. The signals are in front of the receiver 1 of the two channels added.
FIG. 1 Another embodiment of the present invention is reproduced in FIG.
the hearing aid not as in the case of FIG. 2 via a feedback compensator 5, but via a gain or compression control 12.
the reinforcement respectively the compression of the hearing aid can be varied.
the system distance is too small, be it due to the useful signal or the feedback signal, can amplify the hearing aid be reduced so far that it works again stably.
the necessary system distance is the same as in the previous ones Examples provided by the comparator 11.
the entire estimation unit 6 to 11 corresponds to that of the Embodiment according to FIG 2.
FIG. 5 shows an embodiment of the present invention shown, which is essentially a combination of the Embodiments of Figures 3 and 4 corresponds.
the intern Two-channel hearing aid is controlled by a gain control 12 in the high-frequency channel of feedback signals freed.
FIG. 6. Another embodiment is shown in FIG. 6. in the The construction of the hearing device essentially corresponds to that of FIG 2 or from FIG 4. However, the feedback is here in Input signal through a feedback or oscillation detector 13 detected.
a notch filter controller 14 evaluates the output signal of the oscillation detector 13 and controls a narrowband or notch filter 15. Because there is a hearing aid coupling due to an increase in resonance and makes the whistle noticeable, it can also are largely suppressed by a notch filter 15.
the Notch filter 15 is for this purpose between the hearing aid signal processing 4 and the handset 1 switched. Used as a control signal the notch filter controller 14 also the system distance from comparator 11.

Landscapes

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

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

Publications (3)

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

Family

ID=31896304

Family Applications (1)

Application Number	Title	Priority Date	Filing Date
EP03021037A Expired - Lifetime EP1401242B1 (fr)	2002-09-23	2003-09-17	Compensation de la rétroaction pour prothèses auditives avec système d'estimation de la distance

Country Status (5)

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

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number	Priority date	Publication date	Assignee	Title
EP1858289A1 (fr)	2006-05-19	2007-11-21	Siemens Audiologische Technik GmbH	Appareil auditif avec détection de rétroaction et procédé correspondant
US8280088B2 (en)	2006-05-19	2012-10-02	Siemens Audiologische Technik Gmbh	Hearing apparatus with feedback detection and corresponding method
EP2360945A3 (fr) *	2010-01-29	2013-07-10	Siemens Medical Instruments Pte. Ltd.	Appareil auditif avec décalage de fréquence et procédé correspondant
CN111629313A (zh) *	2019-02-27	2020-09-04	奥迪康有限公司	包括环路增益限制器的听力装置

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CA2357200C (fr) *	2001-09-07	2010-05-04	Dspfactory Ltd.	Dispositif d'ecoute
US6917471B2 (en) *	2003-01-24	2005-07-12	Sumitomo Electric Industries, Ltd.	Diffraction grating element
US7127076B2 (en) *	2003-03-03	2006-10-24	Phonak Ag	Method for manufacturing acoustical devices and for reducing especially wind disturbances
DE102004053776B4 (de) *	2004-11-08	2007-10-31	Siemens Audiologische Technik Gmbh	Verfahren zur Verstärkung eines Akustiksignals und entsprechendes Akustiksystem
DE102006020832B4 (de) †	2006-05-04	2016-10-27	Sivantos Gmbh	Verfahren zum Unterdrücken von Rückkopplungen bei Hörvorrichtungen
US7925307B2 (en) *	2006-10-31	2011-04-12	Palm, Inc.	Audio output using multiple speakers
DE102009012162A1 (de) *	2009-03-06	2010-09-09	Siemens Medical Instruments Pte. Ltd.	Verfahren zum Betrieb einer Hörvorrichtung und Hörvorrichtung mit einer Rückkopplungsunterdrückung
DE102009018812B4 (de) *	2009-04-24	2015-05-28	Siemens Medical Instruments Pte. Ltd.	Verfahren zum Betrieb einer Hörvorrichtung und Hörvorrichtung mit einer Frequenzweiche
WO2010040863A2 (fr)	2010-01-15	2010-04-15	Phonak Ag	Procédé d'utilisation d'un dispositif auditif et ce dispositif auditif lui-même
KR102007509B1 (ko) *	2013-05-06	2019-08-06	삼성전자주식회사	고막과 청각 장치간의 거리를 측정하는 청각 장치 및 방법
DE102014218672B3 (de) *	2014-09-17	2016-03-10	Sivantos Pte. Ltd.	Verfahren und Vorrichtung zur Rückkopplungsunterdrückung

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ATE69132T1 (de) *	1987-02-17	1991-11-15	Siemens Ag	Schaltungsanordnung zum erkennen von schwingungen.
FR2635680B1 (fr) *	1988-08-30	1997-12-26	Belone Electronics Corp	Prothese auditive
US5091952A (en) *	1988-11-10	1992-02-25	Wisconsin Alumni Research Foundation	Feedback suppression in digital signal processing hearing aids
DK169958B1 (da) *	1992-10-20	1995-04-10	Gn Danavox As	Høreapparat med kompensation for akustisk tilbagekobling
EP0585976A3 (en) *	1993-11-10	1994-06-01	Phonak Ag	Hearing aid with cancellation of acoustic feedback
US6072884A (en) *	1997-11-18	2000-06-06	Audiologic Hearing Systems Lp	Feedback cancellation apparatus and methods
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2002
- 2002-09-23 DE DE10244184A patent/DE10244184B3/de not_active Expired - Fee Related
2003
- 2003-09-17 EP EP03021037A patent/EP1401242B1/fr not_active Expired - Lifetime
- 2003-09-17 DE DE50310852T patent/DE50310852D1/de not_active Expired - Lifetime
- 2003-09-17 DK DK03021037T patent/DK1401242T3/da active
- 2003-09-17 AT AT03021037T patent/ATE416591T1/de not_active IP Right Cessation
- 2003-09-23 US US10/668,855 patent/US20040109578A1/en not_active Abandoned

Cited By (6)

* Cited by examiner, † Cited by third party
Publication number	Priority date	Publication date	Assignee	Title
EP1858289A1 (fr)	2006-05-19	2007-11-21	Siemens Audiologische Technik GmbH	Appareil auditif avec détection de rétroaction et procédé correspondant
US8280088B2 (en)	2006-05-19	2012-10-02	Siemens Audiologische Technik Gmbh	Hearing apparatus with feedback detection and corresponding method
EP2360945A3 (fr) *	2010-01-29	2013-07-10	Siemens Medical Instruments Pte. Ltd.	Appareil auditif avec décalage de fréquence et procédé correspondant
US8538053B2 (en)	2010-01-29	2013-09-17	Siemens Medical Instruments Pte. Ltd.	Hearing device with frequency shifting and associated method
CN111629313A (zh) *	2019-02-27	2020-09-04	奥迪康有限公司	包括环路增益限制器的听力装置
CN111629313B (zh) *	2019-02-27	2023-12-01	奥迪康有限公司	包括环路增益限制器的听力装置

Also Published As

Publication number	Publication date
US20040109578A1 (en)	2004-06-10
DK1401242T3 (da)	2009-04-06
EP1401242A3 (fr)	2008-02-20
EP1401242B1 (fr)	2008-12-03
ATE416591T1 (de)	2008-12-15
DE10244184B3 (de)	2004-04-15
DE50310852D1 (de)	2009-01-15

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