EP1542500B1 - Prothèse acoustique avec suppression de bruit et procédé correspondant pour la suppression du bruit - Google Patents

Prothèse acoustique avec suppression de bruit et procédé correspondant pour la suppression du bruit Download PDF

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Publication number
EP1542500B1
EP1542500B1 EP04026820A EP04026820A EP1542500B1 EP 1542500 B1 EP1542500 B1 EP 1542500B1 EP 04026820 A EP04026820 A EP 04026820A EP 04026820 A EP04026820 A EP 04026820A EP 1542500 B1 EP1542500 B1 EP 1542500B1
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EP
European Patent Office
Prior art keywords
signal
hearing aid
transfer function
output signal
usable
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.)
Active
Application number
EP04026820A
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German (de)
English (en)
Other versions
EP1542500A2 (fr
EP1542500A3 (fr
Inventor
Joachim Dr. Eggers
Volkmar Hamacher
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
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Publication date
Application filed by Siemens Audioligische Technik GmbH filed Critical Siemens Audioligische Technik GmbH
Publication of EP1542500A2 publication Critical patent/EP1542500A2/fr
Publication of EP1542500A3 publication Critical patent/EP1542500A3/fr
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Classifications

    • 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
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10L—SPEECH ANALYSIS TECHNIQUES OR SPEECH SYNTHESIS; SPEECH RECOGNITION; SPEECH OR VOICE PROCESSING TECHNIQUES; SPEECH OR AUDIO CODING OR DECODING
    • G10L21/00—Speech or voice signal processing techniques to produce another audible or non-audible signal, e.g. visual or tactile, in order to modify its quality or its intelligibility
    • G10L21/02—Speech enhancement, e.g. noise reduction or echo cancellation
    • G10L21/0208—Noise filtering
    • G10L21/0216—Noise filtering characterised by the method used for estimating noise
    • G10L2021/02161—Number of inputs available containing the signal or the noise to be suppressed
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/43—Signal processing in hearing aids to enhance the speech intelligibility
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2460/00—Details of hearing devices, i.e. of ear- or headphones covered by H04R1/10 or H04R5/033 but not provided for in any of their subgroups, or of hearing aids covered by H04R25/00 but not provided for in any of its subgroups
    • H04R2460/01—Hearing devices using active noise cancellation
    • 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
    • H04R25/43—Electronic input selection or mixing based on input signal analysis, e.g. mixing or selection between microphone and telecoil or between microphones with different directivity characteristics
    • 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
    • H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
    • H04R25/505—Customised settings for obtaining desired overall acoustical characteristics using digital signal processing

Definitions

  • the present invention relates to a hearing aid having an estimating device for estimating a useful signal from a disturbed input signal and a signal processing device for processing the useful signal into a useful output signal. Moreover, the present invention relates to a method for suppressing noise on a hearing aid.
  • Hearing impaired people often suffer from a reduced ability to communicate in noise.
  • the signal / noise ratio method for noise reduction have been used for some time.
  • the acoustic signal is recorded in hearing aids with the help of one or more microphones and electrically processed so that the signal / noise ratio is improved and then a suppressed signal can be output via a handset in the ear canal.
  • the acoustic signal but also directly, d. H. concurrently to an electrical processing path, enter the ear canal and so affect the desired influence of electrical signal processing.
  • Typical concurrent signal paths result, for example, in hearing aids with an open supply or in earmolds with vent holes.
  • concurrent signal paths can greatly affect noise suppression based on directional microphone techniques in the low frequency range up to about 1 kHz.
  • a generic hearing aid is for example from the document DE 198 13 512 A1 known. The noise reduction takes place here under the mentioned impairment.
  • EP 1 304 902 A1 a method for noise cancellation of a redundant acoustic signal, in which the intensity of a disturbance is estimated and an input signal component depending on the intensity of the interference is superimposed.
  • the publication WO-A2-01 / 47335 describes a method for suppressing noise components in an input signal of an auditory system and the application of the method in a hearing aid.
  • the method is based on principles of auditory scene analysis and increases speech intelligibility.
  • the object of the present invention is thus to propose a hearing aid with improved noise suppression. Likewise, an improved method for noise suppression in hearing aids should be provided.
  • this object is achieved by a hearing aid having an estimating device for estimating a useful signal from a disturbed input signal and a first signal processing device for processing the useful signal to a useful output signal, wherein the estimating device can also estimate an interference signal from the disturbed input signal. Furthermore, the hearing device has a second signal processing device, with which the transfer function of an acoustic path can be imitated, which is suitable for applying the disturbance signal with the transfer function to form a disturbance output signal. Subsequently, a linking device for linking the Nutzausgangssignals is required with the disturbance output signal.
  • the invention provides a method for suppressing noise on a hearing aid by estimating a useful signal from a disturbed input signal and processing the useful signal into a useful output signal, as well as estimating a disturbance signal from the disturbed input signal, applying the disturbance signal with a transfer function, with an acoustic path is simulated, forming a disturbance output signal and linking the Nutzausgangssignals with the disturbance output signal.
  • the acoustic Path will usually pass the hearing aid in an ear canal. This is a relatively short distance, so that it is essential to generate a compensating signal from the estimated interference signal as quickly as possible with the second signal processing device.
  • the sound reinforcement on the hearing aid over to the eardrum can be compensated as far as possible.
  • the replicated transfer function may be linear. This reduces the computing time and thus optimizes the interference signal compensation.
  • the transfer function can also be time-variant, so that, for example, the displacement of the hearing device in the ear canal can be taken into account.
  • the hearing device may have an acoustic sensor which is placeable or placed in the state of the hearing device at the end of the hearing device facing the eardrum so that its signal can be used for the dynamic variation of the simulated transfer function of the second signal processing device. This makes it possible to consider the acoustic condition in front of the eardrum to adapt the transfer function with the aid of a control loop.
  • the hearing device may further comprise a coupling device with which the useful output signal of the first signal processing device can be coupled to the second signal processing device for varying the simulated transfer function.
  • the coupling factor of the coupling device can be set or varied in the hearing aid operation. This is advantageous if the interference signal is strongly correlated with the useful signal, so that an excessive attenuation of the useful signal can be prevented.
  • FIG. 1 schematically illustrated hearing aid has as a central component to a signal processing device 1.
  • the noise suppression device 3 a useful signal N and an interference signal n are estimated from the input signal from the microphone 2 and from the plurality of microphones. While the estimated desired signal N is further processed in the signal processing device 1, the estimated disturbance signal n is supplied with an estimated system transfer function H.
  • the transfer function ⁇ results from a concurrent, acoustic signal path, which can be represented by a linear acoustic system 5 with a transfer function H.
  • the input of the concurrent signal path is the same acoustic signal X , which also accommodates the microphone 2.
  • d. H In the ear canal one obtains the acoustic signal xH due to the multiplication with the transfer function H of the linear acoustic system 5.
  • the fact that the concurrent signal path is a linear acoustic system is certainly a simplifying assumption which has the purpose of estimating resp . Simulating the concurrent signal path used signal processing device 4 as simple as possible.
  • the output signal n ⁇ of the signal processing device 4 with the transfer function ⁇ represents an estimate of the interference signal xH , which passes via the concurrent signal path into the ear canal.
  • This signal n ⁇ is subtracted from the output signal of the signal processing device 1 and thus fed through the receiver or loudspeaker 6 of the hearing aid in opposite phase in the ear canal.
  • the interference signal xH and the opposite-phase, estimated interference signal n ⁇ cancel each other in the ear canal and the concurrent signal path is compensated, as far as the transit time difference between the acoustic signal path and the electrical signal path allows.
  • the hearing aid of a second embodiment of the present invention is in FIG. 2 shown schematically.
  • the linear acoustic system 5 'of the concurrent acoustic signal path is time-varying or at least in the design of the hearing aid is not well known. Therefore, the transfer function ⁇ of the signal processing device 4 'is also made time-varying.
  • a microphone 7 or other sensor is used, which is to be inserted into the ear canal.
  • the signal obtained by the microphone is subtracted from the estimated signal n ⁇ to obtain an error signal for adaptively adjusting the system 4 'with the transfer function ⁇ .
  • the adaptive setting of the transfer function ⁇ can, for example, with an (N) LMS algorithm (Normalized Least Mean Square) as long as the estimated interference signal n is sufficiently uncorrelated with the useful signal at the hearing device output.
  • the estimated interference signal n is correlated with the useful signal at the hearing aid output to a certain extent, the influence of the useful signal on the adaptation of the filter or the signal processing device 4 'with the transfer function ⁇ can be reduced by the useful signal with a suitably selected system 8 is filtered with the coupling function G.
  • a suitably selected system 8 is filtered with the coupling function G.
  • FIG. 3 shown in a third embodiment.
  • the output signal of the signal processing device 1 is tapped from the coupling device 8 and multiplied by the coupling function G.
  • the resulting signal is subtracted from the microphone signal of the microphone 7 in the ear canal and the estimated interference signal n ⁇ already subtracted therefrom , so that an error signal of the active noise suppression is obtained.
  • This error signal is used to vary the transfer function ⁇ in the time-variant signal processing device 4 '.
  • the signal n.sub.o fed in out of phase into the ear canal compensates for the interference signal components x.sub.H of the acoustic signal X in the ear canal.
  • the interference suppression by directional microphone interconnections can also be made possible if concurrent Signal paths do not allow this in conventional approaches.

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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)
  • Soundproofing, Sound Blocking, And Sound Damping (AREA)
  • Circuit For Audible Band Transducer (AREA)

Claims (11)

  1. Appareil auditif comprenant
    - un dispositif d'estimation (3) pour estimer un signal utile (N̂) issu d'un signal d'entrée perturbé (X) et
    - un premier dispositif de traitement de signal (1) pour transformer le signal utile (N̂) en signal de sortie utile, caractérisée en ce que
    - le dispositif d'estimation (3) permet également d'estimer un signal perturbateur (n̂) issu du signal d'entrée perturbé (X) et en ce que l'appareil auditif comprend en outre
    - un second dispositif de traitement de signal (4, 4') permettant de reproduire la fonction de transfert (H) d'un chemin acoustique, pour appliquer au signal perturbateur (n̂) la fonction de transfert reproduite (Ĥ) en formant un signal de sortie perturbateur (n̂Ĥ) et
    - un dispositif de combinaison pour combiner le signal de sortie utile avec le signal de sortie perturbateur (n̂Ĥ).
  2. Appareil auditif selon la revendication 1, le chemin acoustique dans un canal auditif passant devant l'appareil auditif.
  3. Appareil auditif selon la revendication 1 ou 2, la fonction de transfert reproduite (Ĥ) étant linéaire.
  4. Appareil auditif selon l'une des revendications précédentes, la fonction de transfert reproduite (Ĥ) étant variable dans le temps.
  5. Appareil auditif selon l'une des revendications précédentes, laquelle présente un capteur acoustique (7) qui, lorsque la prothèse auditive est mise en place dans un canal auditif, peut être placé, ou est placé, à l'extrémité de l'appareil auditif tournée vers le tympan de sorte que son signal est utilisable pour la variation dynamique de la fonction de transfert reproduite (Ĥ) du second dispositif de traitement de signal (4, 4').
  6. Appareil auditif selon l'une des revendications précédentes, laquelle présente un dispositif de couplage (8) permettant de coupler le signal de sortie utile du premier dispositif de traitement de signal (1) au second dispositif de traitement de signal (4, 4') pour la variation de la fonction de transfert reproduite (Ĥ).
  7. Appareil auditif selon la revendication 6, un facteur de transfert (G) du dispositif de couplage (8) étant réglable lorsque l'appareil auditif est en fonctionnement.
  8. Procédé pour supprimer des bruits perturbateurs sur un appareil auditif par
    - estimation d'un signal utile (N̂) issu d'un signal d'entrée perturbé (X) et
    - transformation du signal utile (N̂) en signal de sortie utile,
    caractérisé par
    - estimation d'un signal perturbateur (n̂) issu du signal d'entrée perturbé (X),
    - application au signal perturbateur (n̂) d'une fonction de transfert (Ĥ) servant à reproduire un chemin acoustique, en formant un signal de sortie perturbateur (n̂Ĥ) et
    - combinaison du signal de sortie utile avec le signal de sortie perturbateur (n̂Ĥ).
  9. Procédé selon la revendication 8, un signal acoustique étant capté dans un canal auditif entre appareil auditif et tympan, qui est utilisé pour la variation dynamique de la fonction de transfert reproduite (Ĥ).
  10. Procédé selon la revendication 8 ou 9, le signal de sortie utile étant mis à contribution pour la variation de la fonction de transfert reproduite (Ĥ).
  11. Procédé selon la revendication 10, le couplage du signal de sortie utile pour la variation de la fonction de transfert reproduite (Ĥ) étant opéré avec un facteur de couplage (G) réglable.
EP04026820A 2003-12-10 2004-11-11 Prothèse acoustique avec suppression de bruit et procédé correspondant pour la suppression du bruit Active EP1542500B1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE10357800 2003-12-10
DE10357800A DE10357800B3 (de) 2003-12-10 2003-12-10 Hörgerät mit Störgeräuschunterdrückung und entsprechendes Störgeräuschunterdrückungsverfahren

Publications (3)

Publication Number Publication Date
EP1542500A2 EP1542500A2 (fr) 2005-06-15
EP1542500A3 EP1542500A3 (fr) 2009-11-11
EP1542500B1 true EP1542500B1 (fr) 2010-12-29

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ID=34485299

Family Applications (1)

Application Number Title Priority Date Filing Date
EP04026820A Active EP1542500B1 (fr) 2003-12-10 2004-11-11 Prothèse acoustique avec suppression de bruit et procédé correspondant pour la suppression du bruit

Country Status (6)

Country Link
US (1) US7574012B2 (fr)
EP (1) EP1542500B1 (fr)
AU (1) AU2004235586B9 (fr)
DE (2) DE10357800B3 (fr)
DK (1) DK1542500T3 (fr)
ES (1) ES2358797T3 (fr)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102019213810B3 (de) * 2019-09-11 2020-11-19 Sivantos Pte. Ltd. Verfahren zum Betrieb eines Hörgeräts und Hörgerät

Families Citing this family (13)

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Publication number Priority date Publication date Assignee Title
US7983433B2 (en) * 2005-11-08 2011-07-19 Think-A-Move, Ltd. Earset assembly
CA2647479C (fr) * 2006-03-31 2011-07-26 Widex A/S Appareil auditif et procede permettant d'estimer la limitation de gain dynamique dans un appareil auditif
US7502484B2 (en) * 2006-06-14 2009-03-10 Think-A-Move, Ltd. Ear sensor assembly for speech processing
US8867766B2 (en) 2007-07-17 2014-10-21 Phonak Ag Method for producing a signal which is audible by an individual
DE102007033484A1 (de) 2007-07-18 2009-01-22 Ruwisch, Dietmar, Dr. Hörgerät
DK2091266T3 (da) * 2008-02-13 2012-09-24 Oticon As Høreindretning og anvendelse af en høreapparatindretning
US8103029B2 (en) 2008-02-20 2012-01-24 Think-A-Move, Ltd. Earset assembly using acoustic waveguide
JP4355359B1 (ja) 2008-05-27 2009-10-28 パナソニック株式会社 マイクを外耳道開口部に設置する耳掛型補聴器
US8542856B2 (en) 2009-12-02 2013-09-24 Panasonic Corporation Hearing aid
US8983103B2 (en) 2010-12-23 2015-03-17 Think-A-Move Ltd. Earpiece with hollow elongated member having a nonlinear portion
US10751524B2 (en) 2017-06-15 2020-08-25 Cochlear Limited Interference suppression in tissue-stimulating prostheses
DE102020206367A1 (de) * 2020-05-20 2021-11-25 Sivantos Pte. Ltd. Verfahren zum Betrieb eines Hörgeräts und Hörgerät
CN114598981B (zh) * 2022-05-11 2022-07-29 武汉左点科技有限公司 助听器内部扰动抑制方法及设备

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US5402496A (en) * 1992-07-13 1995-03-28 Minnesota Mining And Manufacturing Company Auditory prosthesis, noise suppression apparatus and feedback suppression apparatus having focused adaptive filtering
JPH10501951A (ja) * 1995-04-03 1998-02-17 フィリップス エレクトロニクス ネムローゼ フェンノートシャップ 自動イコライザを有する信号増幅システム
DE19813512A1 (de) * 1998-03-26 1999-06-02 Siemens Audiologische Technik Hörgerät und Verfahren zur Störgeräuschunterdrückung mit Breitbandsignalanalyse
JP3916834B2 (ja) * 2000-03-06 2007-05-23 独立行政法人科学技術振興機構 雑音が付加された周期波形の基本周期あるいは基本周波数の抽出方法
US20020150264A1 (en) * 2001-04-11 2002-10-17 Silvia Allegro Method for eliminating spurious signal components in an input signal of an auditory system, application of the method, and a hearing aid
US6741707B2 (en) * 2001-06-22 2004-05-25 Trustees Of Dartmouth College Method for tuning an adaptive leaky LMS filter
EP1304902A1 (fr) * 2001-10-22 2003-04-23 Siemens Aktiengesellschaft Procédé et dispositif pour la suppression du bruit dans un signal acoustique redondant
US6829363B2 (en) * 2002-05-16 2004-12-07 Starkey Laboratories, Inc. Hearing aid with time-varying performance

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102019213810B3 (de) * 2019-09-11 2020-11-19 Sivantos Pte. Ltd. Verfahren zum Betrieb eines Hörgeräts und Hörgerät
EP3793217A1 (fr) 2019-09-11 2021-03-17 Sivantos Pte. Ltd. Appareil auditif avec annulation active du bruit et procédé de fonctionnement de lequel
US11190883B2 (en) 2019-09-11 2021-11-30 Sivantos Pte. Ltd. Method for operating a hearing device, and hearing device

Also Published As

Publication number Publication date
DE10357800B3 (de) 2005-05-25
DE502004012054D1 (de) 2011-02-10
US7574012B2 (en) 2009-08-11
AU2004235586A1 (en) 2005-06-30
EP1542500A2 (fr) 2005-06-15
AU2004235586B2 (en) 2006-05-04
US20050147266A1 (en) 2005-07-07
DK1542500T3 (da) 2011-04-18
ES2358797T3 (es) 2011-05-13
AU2004235586B9 (en) 2006-11-23
EP1542500A3 (fr) 2009-11-11

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