EP2360945B1 - Appareil auditif avec décalage de fréquence et procédé correspondant - Google Patents

Appareil auditif avec décalage de fréquence et procédé correspondant Download PDF

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Publication number
EP2360945B1
EP2360945B1 EP10187394.1A EP10187394A EP2360945B1 EP 2360945 B1 EP2360945 B1 EP 2360945B1 EP 10187394 A EP10187394 A EP 10187394A EP 2360945 B1 EP2360945 B1 EP 2360945B1
Authority
EP
European Patent Office
Prior art keywords
frequency
signal
low
pass filter
signal component
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.)
Revoked
Application number
EP10187394.1A
Other languages
German (de)
English (en)
Other versions
EP2360945A3 (fr
EP2360945A2 (fr
Inventor
Henning Puder
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
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Publication date
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Application filed by Siemens Medical Instruments Pte Ltd filed Critical Siemens Medical Instruments Pte Ltd
Publication of EP2360945A2 publication Critical patent/EP2360945A2/fr
Publication of EP2360945A3 publication Critical patent/EP2360945A3/fr
Application granted granted Critical
Publication of EP2360945B1 publication Critical patent/EP2360945B1/fr
Revoked 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; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Electric hearing aids
    • H04R25/35—Electric hearing aids using translation techniques
    • H04R25/353—Frequency, e.g. frequency shift or compression
    • 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 invention relates to a method for operating a hearing device and a hearing device with improved feedback suppression by the use of an optimized crossover network.
  • FIG. 1 shows the principle of acoustic feedback.
  • a hearing device 1 has a microphone 2, which receives an acoustic useful signal 10, converts it into an electrical microphone signal 11 and emits it to a signal processing unit 3.
  • the microphone signal 11 is, among other things, processed, amplified and delivered to a receiver 4 as an electrical receiver signal 12.
  • the electrical receiver signal 12 is again converted into an acoustic output signal 13 and delivered to the eardrum 7 of a hearing aid wearer.
  • the acoustic feedback path 14 is reproduced digitally in the hearing aid 1.
  • the replication takes place, for example, by means of an adaptive compensation filter 5, which is fed by the receiver signal 12.
  • a filtered compensation signal 15 is subtracted from the microphone signal 11.
  • the effect of the acoustic feedback path 14 is thereby canceled and there is a feedback-free input signal 16 for the signal processing unit.
  • the microphone signal 11 is evaluated with the aid of a detection unit 6 and examined for possible feedback.
  • artefacts can also be created, however, since additional signal components are generated or feedback whistling occurs in the case of an adaptive compensation filter which is not set optimally.
  • EP 1 033 063 B1 discloses a hearing aid with a feedback suppression, wherein two parallel adaptive compensation filters are used to improve the feedback suppression.
  • a high correlation between the useful signal 10 and the feedback signal 14 represents a major problem for optimal feedback suppression because the correlation also attacks input signal components and erroneous adaptions of the compensation filter occur.
  • a solution to this problem will be found in JASA Vol. 94, pt.6, 1993-Dec., 3248 ff. disclosed.
  • a useful signal is decorrelated by a feedback interference signal by the frequency of the output signal of a hearing aid and thus the frequency of the feedback signal is shifted relative to the frequency of the useful signal.
  • FIG. 2 is shown as an example of the frequency response of a crossover of a hearing aid of the type Butterworth 9th order with a cut-off frequency GF of 900 Hz.
  • the curves K1, K2 show the amplitude D in dB as a function of the frequency F in Hz in the range 0 to 1150 Hz.
  • the curve K1 shows a low-pass characteristic and the curve K2 a high-pass characteristic.
  • the cumulative curve K3 from the curves K1 and K2 gives a flat, constant frequency response.
  • the curve K4 shows one with respect to the curve K2 high-pass characteristic shifted by 25 Hz to higher frequencies.
  • the invention claims a hearing aid with an adaptive feedback suppression unit and a signal processing unit.
  • the hearing aid also comprises a low-pass filter characterized by a first cut-off frequency, which decouples a low-frequency signal component from an output signal of the signal processing unit, a high-pass filter characterized by a second cut-off frequency which decouples a high-frequency signal component from the output signal of the signal processing unit, and a frequency-shifting unit which determines the frequency of the high-frequency signal component high-frequency signal component shifts to higher frequencies.
  • There is a predeterminable distance or gap between the first and the second cutoff frequency Due to the different cutoff frequencies, signal distortions caused by a frequency shift are effectively suppressed. The reason is that this results in less overlapping shifted and unshifted signal components. Thus, feedback cancellation can operate continuously at higher frequencies. The suppression then takes place quickly.
  • the distance between 20 Hz and 50 Hz can be large. Experiments have shown that a distance of the cutoff frequencies in this size is sufficient.
  • the frequency shift of the high-frequency signal component is 10 Hz to 30 Hz. This optimizes acoustic feedback cancellation.
  • the hearing device comprises an adder, in which the low-frequency signal component and the frequency-shifted high-frequency signal component are summed, wherein an output signal of the hearing device is formed.
  • the low-pass filter and / or the high-pass filter may be formed as a Cauer filter (also referred to as an elliptic filter).
  • a Cauer filter also referred to as an elliptic filter.
  • the large slew rate of this type of filter effectively prevents signal distortion.
  • the distance of the cut-off frequencies between 20 Hz and 50 Hz can be selected.
  • the frequency of the high-frequency signal component can be shifted by 10 Hz to 30 Hz.
  • the method preferably also comprises an addition of the low-frequency signal component with the frequency-shifted high-frequency signal component, wherein an output signal of the hearing device is formed.
  • the low-pass filter and / or the high-pass filter can be executed as a Cauer filter.
  • FIG. 3 shows a hearing aid 1 with an acoustic input signal 101 receiving microphone 2 and with an acoustic output 13 donating handset 4. As described above, a portion of the output signal 13 is fed back via a feedback path 14 to the microphone 2 of the hearing aid 1, wherein it is with a User signal 10 superimposed on the input signal 101.
  • the microphone 2 converts the acoustic Input signal 101 into an electrical microphone signal 102 um.
  • Any occurring acoustic feedbacks are detected by means of a feedback suppression unit 17, simulated from an earphone input signal 108 and added as an inverted feedback suppression signal 109 to the microphone signal 102 in a second adder 22.
  • a feedback suppression unit 17 simulated from an earphone input signal 108 and added as an inverted feedback suppression signal 109 to the microphone signal 102 in a second adder 22.
  • this results in a feedback-suppressed microphone signal 107, which is supplied to a signal processing unit 3.
  • An output signal 103 of the signal processing unit 3 is supplied to the input of a crossover with a low-pass filter 18 and a high-pass filter 19.
  • a low-pass output signal 105 At the output of the low-pass filter 18 is a low-pass output signal 105 and at the output of the high-pass filter 19 is a high-pass output signal 104 is available.
  • the high-pass output signal 104 is shifted by means of a frequency shift unit 20 by about 10 Hz to 30 Hz to higher frequencies.
  • the frequency-shifted high-pass output signal 106 is added to the low-pass output signal 105 in a first adder 21.
  • a receiver input signal 108 is available, which is converted by the receiver 4 into the acoustic output signal 13.
  • the low-pass filter 18 and the high-pass filter 19 have different limit frequencies GF1, GF2, whereby almost no disturbing interference effects of original and shifted in frequency signal components can occur.
  • the two filters 18, 19 are elliptical filters, also called Cauer filters. They have a particularly steep edge, whereby an unwanted signal overlay in the filter overlap area can be extremely reduced in addition to the different choice of cutoff frequencies.
  • the invention can be used both for hearing aids with one and with several microphones.
  • several microphones there are also a plurality of feedback suppression units and a plurality of crossovers according to the invention, which are fed by different signal-processed microphone signals.
  • FIG. 4 Frequency responses K5, K6, K7, K8, K9, K10 corresponding Cauer filter used according to the invention are shown.
  • the two diagrams of FIG. 4 show the amplitude D in dB as a function of the frequency F in kHz for a frequency range from 650 Hz to 1150 Hz.
  • the upper diagram of the FIG. 4 shows the frequency responses K5, K6 first Cauer filter with a narrow and deep notch of the sum frequency response K7 due to a corresponding formation of the first Cauer filter.
  • the distance between the first limit frequency GF1 of the low pass (curve K5) and the second limit frequency GF2 of the high pass (curve K6) is chosen to be relatively small.
  • the first limit frequency GF1 is about 890 Hz
  • the second limit frequency GF2 is about 910 Hz.
  • the lower diagram of the FIG. 4 shows the frequency responses K8, K9 second Cauer filter with a wider and less deep notch of the sum frequency response K10 due to a corresponding formation of the second Cauer filter.
  • the gap between the first limit frequency GF1 of the low pass (curve K8) and the second limit frequency GF2 of the high pass (curve K9) is chosen larger.
  • the first limit frequency GF1 is about 880 Hz and the second limit frequency GF2 is about 920 Hz.

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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)
  • Amplifiers (AREA)

Claims (8)

  1. Appareil auditif (1) comprenant
    - une unité de suppression de rétroaction (17) et
    - une unité de traitement de signal (3),
    caractérisé par :
    - un filtre passe-bas (18) caractérisé par une première fréquence limite (GF1) et qui extrait d'un signal de sortie (103) de l'unité de traitement de signal (3) une composante de signal à basse fréquence (105),
    - un filtre passe-haut (19) caractérisé par une seconde fréquence limite (GF2) et qui extrait d'un signal de sortie (103) de l'unité de traitement de signal (3) une composante de signal à haute fréquence (104),
    - une unité de décalage de fréquence (20) qui décale la composante de signal à haute fréquence (104) vers des fréquences plus élevées, et
    - un premier additionneur (21) dans lequel la composante de signal à basse fréquence (105) et la composante de signal à haute fréquence (106) à fréquences décalées sont additionnées, permettant ainsi de former un signal de sortie (13) de l'appareil auditif (1),
    - la première et la seconde fréquence limite (GF1, GF2) étant différentes.
  2. Appareil auditif (1) selon la revendication 1,
    caractérisé en ce que
    l'écart entre la première et la seconde fréquence limite (GF1, GF2) est compris entre 20 Hz et 50 Hz.
  3. Appareil auditif (1) selon la revendication 1 ou 2,
    caractérisé en ce que
    le décalage de fréquence de la composante de signal à haute fréquence (104) est de 10 Hz à 30 Hz.
  4. Appareil auditif (1) selon l'une des revendications précédentes,
    caractérisé en ce que
    le filtre passe-bas (18) et/ou le filtre passe-haut (19) se présentent sous forme de filtres de type Cauer.
  5. Procédé de décalage de fréquence dans un appareil auditif (1),
    caractérisé par :
    - une extraction d'une composante de signal à basse fréquence (105) d'un signal de microphone (103) de traitement de signal par un filtre passe-bas (18) caractérisé par une première fréquence limite (GF1),
    - une extraction d'une composante de signal à haute fréquence (104) du signal de microphone (103) de traitement de signal par un filtre passe-haut (19) caractérisé par une seconde fréquence limite (GF2),
    - la première et la seconde fréquence limite (GF1, GF2) étant différentes,
    - un décalage de la composante de signal à haute fréquence (104) vers des fréquences plus élevées, et
    - une addition de la composante de signal à basse fréquence (105) et de la composante de signal à haute fréquence (106) à fréquences (F) décalées,
    - formant ainsi un signal de sortie (13) de l'appareil auditif (1).
  6. Procédé selon la revendication 5,
    caractérisé en ce que
    l'écart entre la première et la seconde fréquence limite (GF1, GF2) est choisi entre 20 Hz et 50 Hz.
  7. Procédé selon la revendication 5 ou 6,
    caractérisé en ce que
    les fréquences (F) de la composante de signal à haute fréquence (104) sont décalées de 10 Hz à 30 Hz.
  8. Procédé selon l'une des revendications 5 à 7,
    caractérisé en ce que
    le filtre passe-bas (18) et/ou le filtre passe-haut (19) sont réalisés sous forme de filtres de type Cauer.
EP10187394.1A 2010-01-29 2010-10-13 Appareil auditif avec décalage de fréquence et procédé correspondant Revoked EP2360945B1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US29937010P 2010-01-29 2010-01-29
DE102010006154A DE102010006154B4 (de) 2010-01-29 2010-01-29 Hörgerät mit Frequenzverschiebung und zugehöriges Verfahren

Publications (3)

Publication Number Publication Date
EP2360945A2 EP2360945A2 (fr) 2011-08-24
EP2360945A3 EP2360945A3 (fr) 2013-07-10
EP2360945B1 true EP2360945B1 (fr) 2014-09-10

Family

ID=43332772

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Application Number Title Priority Date Filing Date
EP10187394.1A Revoked EP2360945B1 (fr) 2010-01-29 2010-10-13 Appareil auditif avec décalage de fréquence et procédé correspondant

Country Status (4)

Country Link
US (1) US8538053B2 (fr)
EP (1) EP2360945B1 (fr)
DE (1) DE102010006154B4 (fr)
DK (1) DK2360945T3 (fr)

Families Citing this family (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102010025918B4 (de) 2010-07-02 2013-06-06 Siemens Medical Instruments Pte. Ltd. Verfahren zum Betrieb eines Hörgeräts und Hörgerät mit variabler Frequenzverschiebung
DK2590437T3 (da) 2011-11-03 2016-01-11 Sivantos Pte Ltd Periodisk adaptering af en tilbagekoblingsundertrykningsindretning
US9179222B2 (en) 2013-06-06 2015-11-03 Cochlear Limited Signal processing for hearing prostheses
US10499165B2 (en) 2016-05-16 2019-12-03 Intricon Corporation Feedback reduction for high frequencies
DE102017200320A1 (de) * 2017-01-11 2018-07-12 Sivantos Pte. Ltd. Verfahren zur Frequenzverzerrung eines Audiosignals
DE102024100300A1 (de) 2024-01-07 2025-07-10 Icebach Sound Solutions Gmbh Hörassistenzvorrichtung sowie zugehöriges Betriebsverfahren

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Publication number Priority date Publication date Assignee Title
US5121009A (en) * 1990-06-15 1992-06-09 Novatel Communications Ltd. Linear phase low pass filter
US6434246B1 (en) * 1995-10-10 2002-08-13 Gn Resound As Apparatus and methods for combining audio compression and feedback cancellation in a hearing aid
EP0855129A1 (fr) * 1995-10-10 1998-07-29 AudioLogic, Incorporated Prothese auditive a traitement de signaux numeriques et selection de strategie de traitement
US6097824A (en) * 1997-06-06 2000-08-01 Audiologic, Incorporated Continuous frequency dynamic range audio compressor
US6072884A (en) * 1997-11-18 2000-06-06 Audiologic Hearing Systems Lp Feedback cancellation apparatus and methods
US6498858B2 (en) * 1997-11-18 2002-12-24 Gn Resound A/S Feedback cancellation improvements
JP3381062B2 (ja) * 1999-06-22 2003-02-24 日本マランツ株式会社 ステレオ信号処理装置
US6831986B2 (en) * 2000-12-21 2004-12-14 Gn Resound A/S Feedback cancellation in a hearing aid with reduced sensitivity to low-frequency tonal inputs
WO2003034784A1 (fr) * 2001-10-17 2003-04-24 Oticon A/S Appareil de correction auditive ameliore
DE10244184B3 (de) * 2002-09-23 2004-04-15 Siemens Audiologische Technik Gmbh Feedbackkompensation für Hörgeräte mit Systemabstandsschätzung
US20040252853A1 (en) * 2003-05-27 2004-12-16 Blamey Peter J. Oscillation suppression
AU2003236382B2 (en) * 2003-08-20 2011-02-24 Phonak Ag Feedback suppression in sound signal processing using frequency transposition
DE102006020832B4 (de) * 2006-05-04 2016-10-27 Sivantos Gmbh Verfahren zum Unterdrücken von Rückkopplungen bei Hörvorrichtungen
DK2369859T3 (en) * 2008-05-30 2017-03-13 Sonova Ag Method of adapting sound in a hearing aid by frequency change and such a device / Method of adapting sound in a hearing aid device by frequency modification and such a device
DK2309776T3 (da) * 2009-09-14 2014-10-27 Gn Resound As Høreapparat med midler til adaptiv feedbackkompensation
US8564436B2 (en) * 2010-03-04 2013-10-22 Victoria A. Oleen Wallet

Also Published As

Publication number Publication date
DK2360945T3 (en) 2014-12-15
DE102010006154B4 (de) 2012-01-19
DE102010006154A1 (de) 2011-08-04
US8538053B2 (en) 2013-09-17
EP2360945A3 (fr) 2013-07-10
EP2360945A2 (fr) 2011-08-24
US20110194714A1 (en) 2011-08-11

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