EP1052881A2 - Prothèse acoustique avec détecteur d'oscillations et méthode de detection d'oscillations dans une prothése acoustique - Google Patents

Prothèse acoustique avec détecteur d'oscillations et méthode de detection d'oscillations dans une prothése acoustique Download PDF

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Publication number
EP1052881A2
EP1052881A2 EP00109229A EP00109229A EP1052881A2 EP 1052881 A2 EP1052881 A2 EP 1052881A2 EP 00109229 A EP00109229 A EP 00109229A EP 00109229 A EP00109229 A EP 00109229A EP 1052881 A2 EP1052881 A2 EP 1052881A2
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EP
European Patent Office
Prior art keywords
hearing aid
oscillation
feedback
microphone
determining
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.)
Granted
Application number
EP00109229A
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German (de)
English (en)
Other versions
EP1052881A3 (fr
EP1052881B1 (fr
Inventor
Volkmar Dipl.-Ing. Hamacher
Georg-Erwin Dipl.-Ing. Arndt
Tom Dipl.-Ing. Weidner (FH)
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 Audioligische 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.)
Filing date
Publication date
Priority claimed from DE1999122133 external-priority patent/DE19922133C2/de
Application filed by Siemens Audioligische Technik GmbH filed Critical Siemens Audioligische Technik GmbH
Publication of EP1052881A2 publication Critical patent/EP1052881A2/fr
Publication of EP1052881A3 publication Critical patent/EP1052881A3/fr
Application granted granted Critical
Publication of EP1052881B1 publication Critical patent/EP1052881B1/fr
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

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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 hearing aid with an oscillation detector and a method for the detection of oscillation in a hearing aid.
  • a feedback suppression is known from WO 96/35314 A1 known in a hearing aid in which the occurrence of feedback is determined. If feedback is found the gain is in at least one frequency band reduced and unchanged in all other frequency bands calmly. To finally set the hearing aid, finally a set of corresponding parameters is generated and saved.
  • a disadvantage of this feedback suppression is that the occurrence of feedback only during the fitting of the hearing aid is recognized and feedback not recognized during normal operation of the hearing aid and be eliminated.
  • DE 37 33 983 A1 describes a method for damping Disturbing sound against speech in hearing aids which also reduces the tendency to feedback.
  • the procedure is the spectral distribution of recorded sound signals using Fourier analysis in a plurality of frequency windows determined and compared with predetermined limit values.
  • the feedback suppression is based on a frequency transposition of the microphone signal, so that feedback not arise at all.
  • this procedure leads to a falsification of the input signal and thus affects the sound of the hearing aid.
  • the invention has for its object a hearing aid with an oscillation detector and a method for detection of oscillations to offer, which with low circuitry complexity realized in a hearing aid can be.
  • the task is for the hearing aid through the features of characterizing part of claim 1 in conjunction with solved the features of the generic term.
  • Advantageous embodiments of the hearing aid are in the further claims 2-13.
  • the task by the features of the characterizing part of the claim 14 in connection with the features of the preamble solved.
  • Advantageous process variants can be found in the further patent claims 15-23.
  • the hearing aid is both a separate one below Hearing aid, e.g. BTE or ITE device, or an implantable Understood hearing aid.
  • the hearing aid according to the invention is characterized by a particularly simply constructed oscillation detector, which takes up little space and requires little circuitry can be realized.
  • the oscillation detector of the hearing aid comprises a period measuring element for determining the respective Number of digitized samples of consecutive periods an input signal of the microphone of the hearing aid.
  • the input signal is digitized by an A / D converter, which upstream of the oscillation detector or can be integrated into this.
  • the output values of the period measuring element pass through subordinate ones Averaging elements around a long term mean and a short term mean, each on a longer and are related to a shorter period.
  • the averaging elements of the invention Hearing aid devices are designed as low-pass filters.
  • low-pass filters of the first order used with a low-pass filter with a longer time constant to determine the long-term mean and another Low pass filter with a shorter time constant for determination of the short-term mean value.
  • the oscillation detector has a magnitude element by one Sign correction of the difference between long-term and Bring about short-term mean so that all assessment values with a positive sign. This can a comparison is made with a likewise positive threshold value, without a threshold range with both negative as well as positive values must be monitored.
  • the oscillation detector has another one Averaging element, e.g. another low pass to the in Comparative element found difference between long-term and Averaging and smoothing the short-term mean again.
  • the predicate of Oscillation detector advantageously an adjustable Threshold value around the sensitivity of the oscillation detector to be able to regulate.
  • the threshold value can be set manually can be set or automatically dependent of detected ambient or noise situations by itself to adjust.
  • a goal of the method according to the invention for oscillation detection consists of essentially sinusoidal input signals of the microphone to be detected since such Signals usually from oscillation and thus present Feedback is assumed.
  • the number of digitized samples in successive periods of the input signal of the microphone is determined. It is now a matter of determining whether the number of sampled values determined changes in successive periods or is essentially identical. For this purpose, a long-term mean value N L and a short-term mean value N K of the number of determined sample values are formed.
  • the method according to the invention enables using a small number that are easy to implement in terms of circuitry Procedural steps the presence of essentially sinusoidal signals and thus of oscillation too detect.
  • a filter element is placed on the appropriate blocking frequency set and activated to frequency-specific (narrowband) to reduce the gain and suppress the feedback effect.
  • frequency-specific narrowband
  • the interference suppression is also concentrated due to the activated filter element only that frequency or that frequency range in which the feedback actually occurs.
  • the remaining Frequency ranges of the signal to be processed are in their Gain not reduced.
  • the oscillation detector creates feedback effects detected, which are characterized by sinusoidal signals are.
  • Hearing aid also enables time-fluctuating feedback effects to recognize and the respective for suppression determine suitable frequency and via activation of the filter element. It can also be used for changing Feedback situations are recorded and remedied.
  • the hearing aid have several filter elements (blocking filter, e.g. notch filter). If when activating a first filter element it is determined that the feedback effects persist, additional filter elements can be activated to a gain reduction at the respective other frequencies to reach.
  • blocking filter e.g. notch filter
  • a general adjustability of the filter characteristics of the filter elements makes it possible, after the respective feedback effect has been determined by the oscillation detector, not only the frequency range of the gain reduction, but also other suitable countermeasures (e.g. Width "and With a particularly detailed typing of the feedback effects, countermeasures adapted precisely to this can be taken by corresponding generation of the filter elements, whereby a particularly targeted and adapted feedback suppression is achieved without this being perceived by the user of the hearing aid device, since only individual frequency ranges of the microphone signal to be processed are affected.
  • suitable countermeasures e.g. Width "and With a particularly detailed typing of the feedback effects, countermeasures adapted precisely to this can be taken by corresponding generation of the filter elements, whereby a particularly targeted and adapted feedback suppression is achieved without this being perceived by the user of the hearing aid device, since only individual frequency ranges of the microphone signal to be processed are affected.
  • the reliability of the oscillation detector is increased if the level of the output signal via a level measuring unit is determined and feedback is only then detected is exceeded if an adjustable level threshold is exceeded becomes.
  • the oscillation detector, the Filter elements and / or level measuring unit connected, controlled and be activated. So can be achieved by the control unit be that upon detection of feedback conditions activation of the filter element by the oscillation detector only takes place when a via the level measuring unit detected and above an adjustable threshold Signal level is present.
  • the control unit can also be designed to be programmable and other functions of the signal analysis of the processed Take over signals so that e.g. based on the signal analysis a suitable threshold value is set in the level measuring unit and this is changed if necessary.
  • the filter elements are therefore advantageous only activated for an adjustable period of time and then again switched off. Then the oscillation detector it is determined whether the initially determined Feedback is still present and, if necessary, a new one Filter activation take place. Through a time-limited filter activation it is avoided that the filters are switched on remain, although due to changing environmental conditions The causes of the feedback effect have been eliminated.
  • a timed activation of the filter elements can be done via a time switch element, which is also in the control element can be integrated.
  • a method for operating a hearing aid is first determined for feedback detection, whether there is an oscillating microphone signal and then - if this is the case - a corresponding frequency-specific Gain reduction of the processed Microphone signal set. Feedback effects that occur are suppressed frequency-specifically and narrowband, without that other frequency ranges of the microphone signal to be processed be touched.
  • the method according to the invention enables a targeted and particularly comfortable for the user Feedback suppression, as in all unaffected Frequency ranges get the usual gain potential remains.
  • the process is continuous determined whether feedback occurs and will then appropriate measures for frequency-specific Gain reduction taken, which is temporal continuously also changes in the feedback effects found to adjust.
  • appropriate dynamic reinforcement reduction measures are reacted to, so that always exactly the feedback determined is suppressed and changes as well as a loss of the feedback effects Find attention.
  • the respective level threshold is not exceeded can also be a sinusoidal largely monofrequency Input signal are present without a feedback situation consists.
  • the respective measure to suppress feedback optimized be adjusted and by activating a suitable one Filter characteristics an adaptation of e.g. the location and the Size of the cutoff frequency range and the degree of gain reduction a further improved feedback suppression can be achieved.
  • the gain reduction only for a certain period of time and then cancel itself to respond to changes in the Sound situation and a loss of the originally detected Feedback effect also the originally applicable set gain reductions and switch off.
  • filter measures again can be set to reduce the gain.
  • the mode of operation of the oscillation detector 4 can be seen from the basic circuit diagram according to FIG. 1.
  • An input signal 11 from the microphone 1 (see FIG. 2) is first digitized in the A / D converter 10 at a sampling rate f S.
  • the A / D converter 10 can be integrated in the oscillation detector 4 or be connected upstream of it.
  • the digitized samples of the A / D converter 10 are fed to the period measuring element 5 in order to determine the number of samples in the respective successive periods of the input signal 11.
  • the period measuring element 5 could thus determine that the successive periods contain, for example, 4-6 samples.
  • Such a period measurement in the period measuring element 5 can e.g. by establishing and analyzing the zero crossings of the digitized samples. Thus, a change of sign and also the direction of the sign change (from + to - or vice versa). Overall, can thus the beginning and end of a period of the input signal 11 (period) can be determined and the number the digital samples between period start and - be determined at the end.
  • the long-term mean value N L and the short-term mean value N K of the number of samples determined by the period measuring element in the respective signal periods of the input signal 11 are determined via the period measuring element 5, namely the low-pass filters 6, 7.
  • x represents the input value (that is, the number of sampled values determined per period) and y the respective output value (that is, N L or N K ) of the processing instruction, in each case provided with the indices t for the respective sampling time interval.
  • a difference between N L and N K is formed in the difference element 12, which is advantageously corrected in the magnitude element 13, so that only positive values occur.
  • a further smoothing is carried out by means of a further averaging element, here, for example, also a first order low-pass filter 14.
  • the size of the difference between N L and N K is then assessed in comparison element 8. If this is below a certain adjustable threshold value, it is assumed that an essentially sinusoidal input signal 11 is present and it can therefore be assumed that oscillation is present.
  • the oscillation frequency 16 (f OSZ ) is now determined in the frequency determiner 15, specifically as the product of the sampling rate f S with the reciprocal of the long-term mean value N L.
  • oscillation frequency f OSZ 4 kHz is present.
  • This oscillation frequency f OSZ can be passed on from the oscillation detector 4 to a control element 20, so that suitable filter elements 17, 18, 19 can be activated, for example to prevent the detected oscillation by means of filters with notch effect (see FIG. 2).
  • a hearing aid device is derived from the basic circuit diagram according to FIG. 2 with at least one microphone 1, a signal processing device 2 with means for signal processing and one Handset 3 emerges, in the signal processing path between Microphone 1 and receiver 3 filter elements 17, 18, 19 for frequency-specific Gain reduction are provided.
  • the filter elements 17, 18, 19 mentioned are determined on a Blocking frequency set and activated, if by the oscillation detector 4 determines oscillating signals and thus a feedback is analyzed as present.
  • the oscillation detector does so 4 reported to the control element 20 and it takes place Adjustment (setting of the blocking frequency) at least one the filter elements 17, 18 or 19. If necessary also several filter elements 17, 18, 19 activated. Basically can be any number of filter elements 17, 18, 19 can be provided to a required extensive feedback suppression to reach.
  • the control element 20 receives the level via the level measurement unit 21 of the output signal communicated. Through the control 20 a feedback is only determined if from Oscillation detector 4 the presence of an oscillating Signal is registered and at the same time a certain Threshold of the level measuring element 21 level exceeding the output signal, i.e. the processed microphone signal, is determined by the level measuring element 21.
  • the filter elements 17, 18 and 19 not only activated, but also in terms of their Filter characteristics (e.g. position and size of the blocking frequency range, Degree of gain reduction) set accordingly.
  • the control element can be programmable for this and e.g. At first the usual basic parameters of filter characteristics set to - if the feedback is not is sufficiently suppressed - an appropriate adjustment the filter characteristics according to a specified or make self-learning program flow.
  • An analysis or typing can also be carried out via the control element 20 the feedback determined by the oscillation detector 4 take place and in the generation of the filter characteristic of the filter elements 17, 18 and 19 flow or this determine.

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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)
  • Measurement Of Mechanical Vibrations Or Ultrasonic Waves (AREA)
  • Control Of Amplification And Gain Control (AREA)
EP00109229A 1999-05-12 2000-04-28 Prothèse acoustique avec détecteur d'oscillations et méthode de détection d'oscillations dans une prothèse acoustique Expired - Lifetime EP1052881B1 (fr)

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
DE19922133 1999-05-12
DE19922132 1999-05-12
DE1999122133 DE19922133C2 (de) 1999-05-12 1999-05-12 Hörhilfsgerät mit Oszillationsdetektor sowie Verfahren zur Feststellung von Oszillationen in einem Hörhilfsgerät
DE19922132 1999-05-12

Publications (3)

Publication Number Publication Date
EP1052881A2 true EP1052881A2 (fr) 2000-11-15
EP1052881A3 EP1052881A3 (fr) 2008-04-23
EP1052881B1 EP1052881B1 (fr) 2010-10-20

Family

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Application Number Title Priority Date Filing Date
EP00109229A Expired - Lifetime EP1052881B1 (fr) 1999-05-12 2000-04-28 Prothèse acoustique avec détecteur d'oscillations et méthode de détection d'oscillations dans une prothèse acoustique

Country Status (4)

Country Link
US (1) US7024011B1 (fr)
EP (1) EP1052881B1 (fr)
DE (1) DE50016012D1 (fr)
DK (1) DK1052881T3 (fr)

Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102004050304B3 (de) * 2004-10-14 2006-06-14 Siemens Audiologische Technik Gmbh Verfahren zur Reduktion von Rückkopplungen bei einem Akustiksystem und Signalverarbeitungsvorrichtung
EP1851994A2 (fr) * 2005-01-11 2007-11-07 Otologics, LLC Attenuation active des vibrations pour microphone implantable
DE102009016845B3 (de) * 2009-04-08 2010-08-05 Siemens Medical Instruments Pte. Ltd. Anordnung und Verfahren zur Erkennung von Rückkopplungen bei Hörvorrichtungen
US8096937B2 (en) 2005-01-11 2012-01-17 Otologics, Llc Adaptive cancellation system for implantable hearing instruments
DE102011001793A1 (de) * 2011-04-05 2012-10-11 Burmester Audiosysteme Gmbh Hörgerät und Verfahren zum Einstellen und Betreiben eines Hörgeräts
US20160345107A1 (en) 2015-05-21 2016-11-24 Cochlear Limited Advanced management of an implantable sound management system

Families Citing this family (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9008319B2 (en) * 2004-12-30 2015-04-14 Plantronics, Inc. Sound pressure level limiter with anti-startle feature
GB2445984B (en) * 2007-01-25 2011-12-07 Sonaptic Ltd Ambient noise reduction
US8045738B2 (en) * 2008-10-31 2011-10-25 Zounds Hearing, Inc. System for managing feedback
DK200970303A (en) * 2009-12-29 2011-06-30 Gn Resound As A method for the detection of whistling in an audio system and a hearing aid executing the method
US8630437B2 (en) * 2010-02-23 2014-01-14 University Of Utah Research Foundation Offending frequency suppression in hearing aids

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE3733983A1 (de) * 1987-10-08 1989-04-20 Bosch Gmbh Robert Verfahren zum daempfen von stoerschall in von hoergeraeten uebertragenen schallsignalen
DE3802903A1 (de) * 1988-02-01 1989-08-10 Siemens Ag Einrichtung zur uebertragung von sprache
DE3927765A1 (de) * 1988-08-30 1990-03-29 Beltone Electronics Corp Hoergeraet
WO1996035314A1 (fr) * 1995-05-02 1996-11-07 Tøpholm & Westermann APS Procede permettant de commander une prothese auditive programmable ou geree par programme pour le reglage de ladite prothese in situ

Family Cites Families (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4596902A (en) * 1985-07-16 1986-06-24 Samuel Gilman Processor controlled ear responsive hearing aid and method
US5170434A (en) 1988-08-30 1992-12-08 Beltone Electronics Corporation Hearing aid with improved noise discrimination
US5396560A (en) * 1993-03-31 1995-03-07 Trw Inc. Hearing aid incorporating a novelty filter
JP2947093B2 (ja) * 1994-11-02 1999-09-13 日本電気株式会社 適応フィルタによるシステム同定の方法および装置
US6359992B1 (en) * 1997-02-06 2002-03-19 Micro Ear Technology Acoustics conditioner

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE3733983A1 (de) * 1987-10-08 1989-04-20 Bosch Gmbh Robert Verfahren zum daempfen von stoerschall in von hoergeraeten uebertragenen schallsignalen
DE3802903A1 (de) * 1988-02-01 1989-08-10 Siemens Ag Einrichtung zur uebertragung von sprache
DE3927765A1 (de) * 1988-08-30 1990-03-29 Beltone Electronics Corp Hoergeraet
WO1996035314A1 (fr) * 1995-05-02 1996-11-07 Tøpholm & Westermann APS Procede permettant de commander une prothese auditive programmable ou geree par programme pour le reglage de ladite prothese in situ

Cited By (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102004050304B3 (de) * 2004-10-14 2006-06-14 Siemens Audiologische Technik Gmbh Verfahren zur Reduktion von Rückkopplungen bei einem Akustiksystem und Signalverarbeitungsvorrichtung
EP1851994A2 (fr) * 2005-01-11 2007-11-07 Otologics, LLC Attenuation active des vibrations pour microphone implantable
EP1851994A4 (fr) * 2005-01-11 2010-06-30 Otologics Llc Attenuation active des vibrations pour microphone implantable
US8096937B2 (en) 2005-01-11 2012-01-17 Otologics, Llc Adaptive cancellation system for implantable hearing instruments
US8840540B2 (en) 2005-01-11 2014-09-23 Cochlear Limited Adaptive cancellation system for implantable hearing instruments
DE102009016845B3 (de) * 2009-04-08 2010-08-05 Siemens Medical Instruments Pte. Ltd. Anordnung und Verfahren zur Erkennung von Rückkopplungen bei Hörvorrichtungen
US8259974B2 (en) 2009-04-08 2012-09-04 Siemens Medical Instruments Pte. Ltd Configuration and method for detecting feedback in hearing devices
DE102011001793A1 (de) * 2011-04-05 2012-10-11 Burmester Audiosysteme Gmbh Hörgerät und Verfahren zum Einstellen und Betreiben eines Hörgeräts
US20160345107A1 (en) 2015-05-21 2016-11-24 Cochlear Limited Advanced management of an implantable sound management system
US10284968B2 (en) 2015-05-21 2019-05-07 Cochlear Limited Advanced management of an implantable sound management system

Also Published As

Publication number Publication date
EP1052881A3 (fr) 2008-04-23
DK1052881T3 (da) 2011-02-14
DE50016012D1 (de) 2010-12-02
US7024011B1 (en) 2006-04-04
EP1052881B1 (fr) 2010-10-20

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