EP2362687A2 - Dispositif auditif avec réduction de contre-réaction par filtres actionnés parallèlement et procédé correspondant - Google Patents

Dispositif auditif avec réduction de contre-réaction par filtres actionnés parallèlement et procédé correspondant Download PDF

Info

Publication number
EP2362687A2
EP2362687A2 EP11150808A EP11150808A EP2362687A2 EP 2362687 A2 EP2362687 A2 EP 2362687A2 EP 11150808 A EP11150808 A EP 11150808A EP 11150808 A EP11150808 A EP 11150808A EP 2362687 A2 EP2362687 A2 EP 2362687A2
Authority
EP
European Patent Office
Prior art keywords
filter
feedback
filter coefficients
hearing
coefficients
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.)
Withdrawn
Application number
EP11150808A
Other languages
German (de)
English (en)
Other versions
EP2362687A3 (fr
Inventor
Sebastian Pape
Stefan Petrausch
Tobias Wurzbacher
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 Pte Ltd
Original Assignee
Siemens Medical Instruments Pte Ltd
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
Application filed by Siemens Medical Instruments Pte Ltd filed Critical Siemens Medical Instruments Pte Ltd
Publication of EP2362687A2 publication Critical patent/EP2362687A2/fr
Publication of EP2362687A3 publication Critical patent/EP2362687A3/fr
Withdrawn legal-status Critical Current

Links

Images

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 hearing device having a signal processing device for processing an input signal to an output signal and a feedback compensation device for compensating a feedback based on the input signal and the output signal. Moreover, the present invention relates to a corresponding method for compensating a feedback in a hearing device.
  • the term hearing device is understood here to mean any sound-emitting device which can be worn on or in the ear, 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.
  • FIG. 1 shown using the example of a behind-the-ear hearing aid.
  • 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
  • Hearing aids generally experience more or less strong feedback during operation. Feedback occurs both via acoustic paths and via electromagnetic paths. Acoustic feedback occurs, for example, when the sound is fed back from a hearing aid speaker to the microphone of the hearing aid. Electromagnetic feedback can be done, for example, from the speaker to another signal processing component by inductive means.
  • the feedback for the hearing aid wearer is imperceptible. However, if the gain in the hearing aid is set sufficiently high, then feedback can be quite disturbing. If the sound amplified by the hearing aid, as mentioned, a path back to the microphones of the hearing aid and is amplified again, this can lead to shrill-sounding and / or echoing artifacts.
  • Modern hearing systems are capable of estimating any feedback paths and producing corresponding filters to reduce or suppress the feedback signals. This results in the so-called feedback compensators (feedback cancler).
  • feedback cancler feedback cancler
  • estimating the feedback path i. H. adapting the particular filter within the hearing aid for some time during which typical feedback whistling or other artifacts occur, for example due to adaptation errors.
  • the adaptation of a filter is done step by step.
  • a so-called step size control is used to adjust the adaptation speed of the feedback compensation device.
  • the step size is increased for a certain period of time and then hardered to avoid disturbance of the useful signal by the feedback compensation means. In either case, however, a feedback whistle or other measurable artifact must occur before a targeted countermeasure can be taken.
  • From the publication DE 600 04 539 T2 is a hearing aid with a method for suppressing feedback known.
  • the hearing aid has two adaptive filters.
  • From the publication EP 0 930 801 B1 is a hearing aid with a two-filter circuit for suppressing feedback known.
  • the object of the present invention is thus to reduce or compensate for feedbacks in hearing devices as effectively and as quickly as possible.
  • the first filter is in FIR filter and the second filter is an IIR filter.
  • the coefficients obtained by an adaptive FIR filter must then be converted for an IIR filter.
  • An IIR filter usually requires much less computation time than a corresponding FIR filter.
  • all the filters of the feedback compensation device which can be operated in parallel may be FIR filters. This has the advantage that the coefficients of an adaptive FIR filter can be easily transferred to a parallel FIR filter.
  • the set of filter coefficients in the feedback compensation device is automatically rewritable with a new set of filter coefficients as soon as the new set of filter coefficients has been selected more frequently than the old one. This also implies an adaptation process with regard to changing feedback situations.
  • the feedback compensation device may also comprise a comparator with which the output signal of the one Filter is determined for the selection having the lowest feedback estimate signal strength. It is particularly advantageous if the feedback compensation device has a measuring unit for measuring the signal energy of the output signal of each filter, and the comparator, the signal energies are fed to the decision. In this way, it can be safely decided which filter or set of filter coefficients is the most effective one for the current feedback situation.
  • a plurality of sets of filter coefficients are storable in the feedback compensation means, and the second filter is operable based on one of the plurality of sets of filter coefficients.
  • a suitable set of filter coefficients can be selected for the second filter, for example based on a classification of the listening situation, or several second filters parallel to the first filter can be operated simultaneously with the different sets of filter coefficients to obtain the best filter or set to choose from filter coefficients.
  • the set of filter coefficients is preferably stored when the respective feedback situation is constant for at least a predetermined period of time. In this way it can be achieved that storage of feedback situations of short duration and thus rapid switching back and forth between several filters is avoided.
  • the set of filter coefficients is advantageously stored when the associated feedback situation occurs with a predetermined minimum frequency.
  • the respective sets filter coefficients are stored.
  • FIG. 2 a signal processing system of a hearing aid or a hearing device is shown schematically.
  • the hearing aid has a microphone 10 for providing an input signal and a handset or speaker 11 which converts an output signal into a corresponding output sound.
  • the input signal of the microphone 10 is processed by a signal processing device 12 to the output signal.
  • the output sound of the loudspeaker 11 reaches the microphone 10 of the hearing aid via an acoustic feedback path 13.
  • the feedback path 13 has the transfer function H.
  • the feedback is at least partially compensated in a known manner by an adaptive filter 14.
  • This adaptive filter 14 estimates the feedback transfer function H with a transfer function ⁇ 0 .
  • the adaptive filter 14 in the present context represents a first filter of the feedback compensation device. Its input is supplied by the output signal of the signal processing device 12. The output of the adaptive filter 14 is applied to a subtractor 15 which subtracts the output signal e 0 of the adaptive filter 14 from the input signal of the microphone 10. The output signal e 0 of the adaptive filter 14 thus represents an estimate of the fed back via the feedback path 13 signal and thus an estimate of the disturbance or error signal.
  • the adaptive filter 14 is operated after the subtractor 15, d. H. the feedback-adjusted useful signal, and adapted from the output signal of the signal processing device 12.
  • an adaptation unit 16 is provided, which calculates, for example, from the two signals mentioned the smallest mean square error.
  • another filter 17 is now provided parallel to the adaptive filter 14, and an additional filter 18 is also provided in parallel.
  • further parallel filters may be provided in the hearing device.
  • the filters 17 and 18, which process in parallel with the adaptive filter 14, each receive as input signal as well as the adaptive filter 14 the output signal of the signal processing device 12. Dashed arrows indicate in the FIG. 2 indicated that the filters 17 and 18 may receive sets of filter coefficients directly or after a corresponding conversion from the adaptive filter 14.
  • the output signals e 1 and e 2 are provided.
  • the output signals are also provided by other filters which are also parallel to the filters 14, 17 and 18 (in FIG FIG. 2 not shown).
  • the subtracter 15 uses the corresponding filter output e 0 , e 1 or e 2 (feedback estimation signals).
  • All filters 14, 17 and 18 are always operated in parallel. Ie. one of these filters is actually used for the feedback compensation, while the others run along only for the sake of comparison and therefore can be referred to as so-called shadow filters.
  • each estimation path has a memory in which a set of filter coefficients can be stored. Depending on the respective feedback situation, the corresponding path is then selected and applied. The remaining paths are then shadow paths or shadow filters.
  • the system must be in accordance with FIG. 2 go through an initialization phase.
  • the filling is similar to a so-called logbook, in which events are recorded continuously.
  • filter coefficients corresponding to the feedback situations that have occurred are recorded in the memories of the filters.
  • two possible options are presented according to which the coefficient memories can be filled. The two options can be realized individually or in combination with each other.
  • a set of relevant feedback paths is preferably measured in situ during a fitting process by an acoustician.
  • relevant feedback paths arise, for example, when telephoning when the phone is held in front of the ear, or when putting on the hat when the arm or hand is held in front of the ear.
  • the measured feedback paths, ie the filter coefficient sets determined for the relevant feedback paths are stored in an internal memory of the hearing aid, ie the feedback path log.
  • the hearing aid operates in a conventional feedback adaptation mode. If a stable, d. H.
  • the associated filter i.e., the set of filter coefficients
  • the feedback path is stable can be determined by different methods. For example, there is a stable feedback path when no feedback is detected over a period of time. However, it is also possible to speak of a stable feedback path if the same measured path or filter coefficient sets occur very frequently.
  • the logbook or the coefficient memories will have a certain number of entries.
  • the number of entries is naturally limited. In this case, entries can be overwritten if other entries or filters appear more relevant than already entered. For example, filters that are never or rarely used (filter coefficient sets) can be removed from the logbook and recorded more frequently. It is therefore a "dynamic logbook".
  • the initial phase is followed by the operating phase of the hearing device.
  • the hearing system uses the logbook entries. For example, there may be n logbook entries. Based on this, at least one and a maximum of n filters with the filter coefficients of the logbook will run as a shadow filter parallel to the currently used filter. This means that, in addition to the adaptive filter, at least one further filter is operated in parallel. Either this shadow filter is also an adaptive filter or not adaptive filter. However, only one of these put into operation filter contributes to the actual signal path of the hearing. This means that only the output signal of a single one of these filters 14, 17, 18 is subtracted from the input signal of the microphone 10.
  • a comparator 19 is used. At the comparator 19 outputs of all filters 14, 17, 18, 20 are connected, wherein the filter with the reference numeral 20 is an n-th filter of the hearing device.
  • the individual filters 17, 18 and 20 are equipped with the filter coefficients of the logbook.
  • a single, second filter may be provided, in which different filter coefficient sets, which are stored in the logbook, can be read.
  • the comparator 19 now checks which signal path (with the adaptive filter 14 or one with a shadow filter 17, 18, 20) has the lowest feedback signal strength. This can be done for example by measuring the output energy of the respective filter. Alternatively or additionally, the impulse responses of the filters or errors or deviations between the microphone signal and an output signal of one of the filters can also be evaluated. If a filter can be determined that is significantly better than the current one, this better filter is used for the signal path of the hearing aid.
  • the adaptive filter can always be the active filter.
  • the adaptive filter is usually a finite impulse response (FIR) filter which requires more filter coefficients than a comparable IIR filter.
  • the logbook contains an entry for both situations - the closed auditory canal and the slightly opened auditory canal - the feedback compensation can take place much more rapidly.
  • the feedback compensation system instead of triggering a new adaptation, the feedback compensation system only has to switch between the two filters. However, it remains open to adapt after switching to respond to small changes in the feedback path. However, this too is faster than performing a completely new adaptation.
  • the hearing device according to the invention thus optionally has a self-learning algorithm which generates a logbook with different feedback paths (dynamic logbook). This not only helps to speed up the adaptation time, but at best to compensate for the feedback in whole or in part before even a whistle is perceived.

Landscapes

  • 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)
  • Filters That Use Time-Delay Elements (AREA)
  • Circuit For Audible Band Transducer (AREA)
  • Soundproofing, Sound Blocking, And Sound Damping (AREA)
EP11150808.1A 2010-02-26 2011-01-13 Dispositif auditif avec réduction de contre-réaction par filtres actionnés parallèlement et procédé correspondant Withdrawn EP2362687A3 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102010009459A DE102010009459B4 (de) 2010-02-26 2010-02-26 Hörvorrichtung mit parallel betriebenen Rückkopplungsreduktionsfiltern und Verfahren

Publications (2)

Publication Number Publication Date
EP2362687A2 true EP2362687A2 (fr) 2011-08-31
EP2362687A3 EP2362687A3 (fr) 2015-11-11

Family

ID=44065021

Family Applications (1)

Application Number Title Priority Date Filing Date
EP11150808.1A Withdrawn EP2362687A3 (fr) 2010-02-26 2011-01-13 Dispositif auditif avec réduction de contre-réaction par filtres actionnés parallèlement et procédé correspondant

Country Status (3)

Country Link
US (1) US8737656B2 (fr)
EP (1) EP2362687A3 (fr)
DE (1) DE102010009459B4 (fr)

Families Citing this family (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP6285300B2 (ja) * 2014-07-07 2018-02-28 リオン株式会社 補聴器及びフィードバックキャンセラ
US11457304B1 (en) 2021-12-27 2022-09-27 Bose Corporation Headphone audio controller

Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE60004539T2 (de) 1999-09-20 2004-09-02 Sonic Innovations, Inc., Salt Lake City Teilband-unterdrückung einer akustischen rückkopplung in hörgeräten
EP0930801B1 (fr) 1998-01-14 2008-11-05 Bernafon AG Circuit et procédé pour la suppression adaptative de la réaction acoustique

Family Cites Families (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2005081584A2 (fr) * 2004-02-20 2005-09-01 Gn Resound A/S Prothese auditive a suppression de retroaction
CA2647462C (fr) * 2006-04-01 2014-05-20 Widex A/S Appareil auditif et procede permettant de commander la vitesse d'adaptation dans des systemes anti-retroaction pour appareils auditifs
CN105392099B (zh) * 2008-04-10 2019-06-07 Gn瑞声达A/S 具有反馈消除的助听器
DE102009031135A1 (de) * 2009-06-30 2011-01-27 Siemens Medical Instruments Pte. Ltd. Hörvorrichtung und Verfahren zur Unterdrückung von Rückkopplungen

Patent Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0930801B1 (fr) 1998-01-14 2008-11-05 Bernafon AG Circuit et procédé pour la suppression adaptative de la réaction acoustique
DE60004539T2 (de) 1999-09-20 2004-09-02 Sonic Innovations, Inc., Salt Lake City Teilband-unterdrückung einer akustischen rückkopplung in hörgeräten

Also Published As

Publication number Publication date
US20110211715A1 (en) 2011-09-01
US8737656B2 (en) 2014-05-27
DE102010009459B4 (de) 2012-01-19
DE102010009459A1 (de) 2011-09-01
EP2362687A3 (fr) 2015-11-11

Similar Documents

Publication Publication Date Title
EP2180726B2 (fr) Localisation du son avec des prothèses auditives binauriculaires
DE102008053457B3 (de) Verfahren zum Anpassen einer Hörvorrichtung und entsprechende Hörvorrichtung
EP2645743B1 (fr) Appareil auditif pour un traitement binaural et procédé destiné à préparer un traitement binaural
DE102007017761B4 (de) Verfahren zur Anpassung eines binauralen Hörgerätesystems
DE102011006129B4 (de) Hörvorrichtung mit Rückkopplungsunterdrückungseinrichtung und Verfahren zum Betreiben der Hörvorrichtung
EP2172062B1 (fr) Procédé d'adaptation d'un appareil de correction auditive à l'aide d'un modèle perceptif
EP2797344B1 (fr) Procédé de commande d'un pas d'adaptation et dispositif auditif
EP2988529A1 (fr) Frequence de division adaptative dans appareils d'aide auditive
EP2070384A1 (fr) Appareil de correction auditive commandé par un modèle perceptif et procédé correspondant
EP2200345B1 (fr) Procédé de sélection d'une direction préférentiel d'un microphone directionnel et dispositif auditif correspondant
EP2811762A1 (fr) Système binaural de formation de faisceau fondé sur la logique
EP2109329A2 (fr) Procédé d'évaluation en plusieurs étapes destiné à la réduction des bruits parasites et dispositif auditif
DE102014218672B3 (de) Verfahren und Vorrichtung zur Rückkopplungsunterdrückung
DE102010009459B4 (de) Hörvorrichtung mit parallel betriebenen Rückkopplungsreduktionsfiltern und Verfahren
EP3413588B1 (fr) Procédé de caractérisation d'une haut-parleur dans un dispositif auditif, dispositif auditif et dispositif d'essai pour un dispositif auditif
EP2822300B1 (fr) Reconnaissance de situations d'écoute à l'aide de différentes sources de signal
EP1962554A2 (fr) Appareil auditif doté d'une séparation de signal d'erreur et procédé correspondant
DE102009058415A1 (de) Verfahren zur Frequenztransposition bei einem Hörhilfegerät sowie Hörhilfegerät
EP2590437B1 (fr) Adaptation périodique d'un dispositif de suppression de l'effet Larsen
DE102009014053A1 (de) Verfahren zum Einstellen einer Richtcharakteristik und Hörvorrichtung
EP3048813B1 (fr) Procédé et dispositif de suppression du bruit basée sur l'inter-corrélation de bandes secondaires
WO2011000641A1 (fr) Procédé et dispositif auditif pour le réglage de la suppression de la réaction
DE102009018425A1 (de) Hörvorrichtung mit Entstörung am Signaleingang
DE102007011808A1 (de) Verfahren zur Reduzierung von Störgeräuschen mit trainierbaren Modellen
WO2011107545A2 (fr) Procédé pour régler un dispositif d'audition à effet directif

Legal Events

Date Code Title Description
PUAI Public reference made under article 153(3) epc to a published international application that has entered the european phase

Free format text: ORIGINAL CODE: 0009012

AK Designated contracting states

Kind code of ref document: A2

Designated state(s): AL AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HR HU IE IS IT LI LT LU LV MC MK MT NL NO PL PT RO RS SE SI SK SM TR

AX Request for extension of the european patent

Extension state: BA ME

PUAL Search report despatched

Free format text: ORIGINAL CODE: 0009013

AK Designated contracting states

Kind code of ref document: A3

Designated state(s): AL AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HR HU IE IS IT LI LT LU LV MC MK MT NL NO PL PT RO RS SE SI SK SM TR

AX Request for extension of the european patent

Extension state: BA ME

RAP1 Party data changed (applicant data changed or rights of an application transferred)

Owner name: SIVANTOS PTE. LTD.

RIC1 Information provided on ipc code assigned before grant

Ipc: H04R 25/00 20060101AFI20151008BHEP

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: THE APPLICATION IS DEEMED TO BE WITHDRAWN

18D Application deemed to be withdrawn

Effective date: 20160512