EP2009955B1 - Dispositif auditif avec réduction du bruit passif dépendant du niveau d'entrée - Google Patents

Dispositif auditif avec réduction du bruit passif dépendant du niveau d'entrée Download PDF

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Publication number
EP2009955B1
EP2009955B1 EP08104366.3A EP08104366A EP2009955B1 EP 2009955 B1 EP2009955 B1 EP 2009955B1 EP 08104366 A EP08104366 A EP 08104366A EP 2009955 B1 EP2009955 B1 EP 2009955B1
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EP
European Patent Office
Prior art keywords
noise reduction
signal processing
level
signal
hearing
Prior art date
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Active
Application number
EP08104366.3A
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German (de)
English (en)
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EP2009955A3 (fr
EP2009955A2 (fr
Inventor
Sebastian Pape
Heike Dr. Heuermann
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
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Siemens Medical Instruments Pte Ltd
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Publication of EP2009955A2 publication Critical patent/EP2009955A2/fr
Publication of EP2009955A3 publication Critical patent/EP2009955A3/fr
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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
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2430/00—Signal processing covered by H04R, not provided for in its groups
    • H04R2430/03—Synergistic effects of band splitting and sub-band processing
    • 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 device with a signal processing channel, in which a noise reduction device is integrated. Moreover, the present invention also relates to a method for reducing noise in such hearing devices.
  • the term hearing device is understood here to mean a device that can be worn on 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) and in-the-ear hearing aids (ITO), e.g. Concha hearing aids or canal hearing aids (ITE, CIC).
  • BTE behind-the-ear hearing aids
  • ITO 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. This basic structure is in FIG. 1 shown using the example of a behind-the-ear hearing aid. In a hearing aid housing 1 for carrying behind the ear are one or more microphones 2 to Built-in sound recording from the environment.
  • 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 of the signal processing unit 3 is carried out by a likewise integrated into the hearing aid housing 1 battery. 5
  • Noise reduction algorithms are used to suppress disturbing noises or to reduce their level. Especially very quiet noises are then often lowered completely below the hearing threshold. This leads to an unnatural sound impression. For a natural listening experience, however, it is desirable, even if quiet sounds are not completely lost, d. H. not be lowered below the hearing threshold.
  • the US 2004/0252852 A1 describes a method by which the ratio of speech signal to background noise in hearing aids can be improved.
  • a weight function is determined as a function of the noise signals in the binaural signals.
  • a volume level is adjusted for the left and right ear.
  • the object of the present invention is therefore to propose a hearing device in which, although a noise reduction takes place, but still as natural a sound pattern is maintained.
  • a corresponding method for reducing noise in hearing devices should be provided.
  • this object is achieved by a hearing device with a first signal processing channel, in which a noise reduction device is integrated, comprising a second signal processing channel having the same input as the first signal processing channel and in which no noise reduction device, but a level limiting device is integrated, and an adder, with which the output signals of both signal processing channels are summable to a total output signal, wherein the noise reduction is passive and has no active level-dependent control with a decision threshold at which the noise reduction is to be turned off.
  • a method for reducing noise in hearing devices by processing an input signal in a first signal processing channel including noise reduction, processing the input signal in a second signal processing channel without noise reduction but with level limiting and adding the output signals of the two signal processing channels to a total output signal, wherein the noise reduction is passive and has no active level dependent control with a decision threshold at which the noise reduction is to be turned off.
  • the noise reduction is passive input level dependent. Even very quiet noises are then not lowered below the hearing threshold and are therefore not lost.
  • the two signal processing channels are realized on a single chip. This allows a reliable signal processing allow for the implementation of only little space is required.
  • Each of the two signal processing channels can be divided into several frequency channels. As a result, the level limitation and the noise reduction can be made frequency-dependent.
  • the level limiting device has an increasing compression characteristic over the entire effective range.
  • the natural hearing impression can be maintained even better, because louder noises are always presented louder than quiet noises.
  • FIG. 2 symbolically shows the structure of a signal processing unit of a hearing device according to the invention.
  • the signal of a processing unit 10 is supplied in a first channel K1 of a noise reduction unit 11 for noise reduction.
  • the output signal of the signal processing unit 10 is supplied to a level limiter 12 in a second channel K2. This limits the output levels to a predetermined level.
  • the level limiter 12 is provided with a characteristic to limit the high level to a fixed maximum level, it is also possible that the characteristic curve slightly rises after the kink, realizing not a hard limit but some compression. Also one Such compression should be understood here by the term "level limitation".
  • the output signals of the channels K1 and K2 are added in an adder 13 to form a total output signal SG.
  • the signal of the signal processing unit 10 is thus divided into two channels K1 and K2 before the noise reduction.
  • a noise reduction with the noise reduction unit 11 takes place in a conventional manner.
  • No noise reduction takes place in the second channel K2.
  • the signal is limited or compressed only in dynamics to a defined very low output level by the level limiter 12.
  • the noise-reduced signal and the level-limited signal are added again. This means that a noise signal with at least a reduced level is included in the output signal SG in any case. Quiet noises up to the characteristic bending point of the level limiter 12 are even accepted undamped into the output signal SG.
  • FIG. 2 Processing shown can be performed in parallel in multiple frequency channels. As a result, depending on the user's request, high-frequency and low-frequency noises or noise components can be attenuated individually.
  • the noise reduction is thus partially bypassed with a level-limited channel.
  • This makes it possible to realize a passive input-level-dependent noise reduction, since noises with a very low level are hardly reduced, whereas noises with a high level are correspondingly reduced.
  • This makes it possible that quiet signals can be heard again despite the noise reduction.
  • there is no need for active, level-dependent control with a decision threshold since the noise reduction in the two channels is passive.
  • the fact that no active decision-level control is necessary leads to the further advantage of completely calm, natural sound. The listener thus gets the chance to get used to soft sounds and, like the normal hearing, to hide them in the perception. For thresholded algorithms, this effect does not occur because the quiet sounds are not always present.
  • the addition of the signals from two channels does not lead to switching problems and thus to a natural sound.
  • the first channel K1 with the noise reduction masks the second channel K2 without noise reduction.
  • the second channel K2 is audible, the first channel K1, however, no longer.
  • Another advantage of this two-channel processing is that it may be possible to achieve a greater noise reduction, which in the first channel also suppresses loud noises below the threshold of hearing, without having to accept that this causes quieter details to disappear (in altogether quiet passages). In noisy environments, however, the noise reduction takes full effect and the second channel is masked.

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

Claims (7)

  1. Prothèse auditive comprenant :
    - un premier canal ( K1 ) de traitement du signal, dans lequel est intégré un dispositif ( 11 ) de réduction du bruit,
    - un deuxième canal ( K2 ) de traitement du signal, qui possède la même entrée que le premier canal ( K1 ) de traitement du signal et dans lequel il n'est pas intégré de dispositif de réduction du bruit, mais un dispositif ( 12 ) de limitation de niveau, et
    - un dispositif ( 13 ) d'addition, par lequel les signaux de sortie des deux canaux ( K1, K2 ) de traitement du signal peuvent être additionnés en un signal ( SG ) de sortie total, caractérisée en ce que
    - la réduction du bruit est passive et n'a pas de commande active qui dépend du niveau, avec un seuil de décision, auquel la réduction du bruit doit être débranchée.
  2. Prothèse auditive suivant la revendication 1, dans laquelle les deux canaux ( K1, K2 ) de traitement du signal sont réalisés sur une puce unique.
  3. Prothèse auditive suivant la revendication 1 ou 2, dans laquelle chacun des deux canaux ( K1, K2 ) de traitement du signal est subdivisé en plusieurs canaux de fréquence.
  4. Prothèse auditive suivant l'une des revendications précédentes, dans laquelle le dispositif ( 12 ) de limitation du niveau a, dans tout le domaine d'action, une courbe de caractéristique de compression croissante.
  5. Procédé de réduction de bruit parasite dans des prothèses auditives par
    - traitement d'un signal d'entrée dans un premier canal ( K1 ) de traitement du signal incluant une réduction du bruit,
    - traitement du signal d'entrée dans un deuxième canal ( K2 ) de traitement du signal sans réduction du bruit, mais avec limitation du niveau et
    - addition des signaux de sortie des deux canaux ( K1, K2 ) de
    traitement du signal en un signal ( SG ) de sortie total, caractérisé en ce que
    - la réduction du bruit est passive et n'a pas de commande active qui dépend du niveau, avec un seuil de décision, auquel la réduction du bruit doit être débranchée.
  6. Procédé suivant la revendication 5, dans lequel le traitement dans les deux canaux ( K1, K2 ) de traitement du signal s'effectue respectivement de manière divisée en plusieurs canaux de fréquence.
  7. Procédé suivant la revendication 5 ou 6, dans lequel la limitation du niveau s'effectue, dans tout le domaine d'action, par une courbe de caractéristique de compression croissante.
EP08104366.3A 2007-06-29 2008-06-11 Dispositif auditif avec réduction du bruit passif dépendant du niveau d'entrée Active EP2009955B1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102007030067A DE102007030067B4 (de) 2007-06-29 2007-06-29 Hörgerät mit passiver, eingangspegelabhängiger Geräuschreduktion und Verfahren

Publications (3)

Publication Number Publication Date
EP2009955A2 EP2009955A2 (fr) 2008-12-31
EP2009955A3 EP2009955A3 (fr) 2011-02-23
EP2009955B1 true EP2009955B1 (fr) 2014-03-05

Family

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EP08104366.3A Active EP2009955B1 (fr) 2007-06-29 2008-06-11 Dispositif auditif avec réduction du bruit passif dépendant du niveau d'entrée

Country Status (4)

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US (1) US8433086B2 (fr)
EP (1) EP2009955B1 (fr)
DE (1) DE102007030067B4 (fr)
DK (1) DK2009955T3 (fr)

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP2475423B1 (fr) 2009-09-11 2016-12-14 Advanced Bionics AG Réduction de bruit dynamique dans un système de prothèse auditive

Family Cites Families (14)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS55117712A (en) * 1979-02-28 1980-09-10 Matsushita Electric Ind Co Ltd Noise reduction circuit of video signal recording and reproducing device
JP2586687B2 (ja) * 1990-04-20 1997-03-05 松下電器産業株式会社 雑音除去回路
JPH09305908A (ja) * 1996-05-09 1997-11-28 Pioneer Electron Corp 雑音低減装置
US5903655A (en) * 1996-10-23 1999-05-11 Telex Communications, Inc. Compression systems for hearing aids
AU740951C (en) 1997-04-16 2004-01-22 Emma Mixed Signal C.V. Method for Noise Reduction, Particularly in Hearing Aids
AU4820099A (en) * 1998-06-30 2000-01-17 Resound Corporation System for reducing the effects of acoustically noisy environments on detected sound signals
US6157252A (en) * 1998-09-09 2000-12-05 The Engineering Consortium, Inc. Battery polarity insensitive integrated circuit amplifier
DE19957128C1 (de) * 1999-11-26 2001-08-16 Siemens Audiologische Technik Verfahren zur Pegelbegrenzung in einem digitalen Hörhilfegerät sowie digitales Hörhilfegerät
US7206421B1 (en) 2000-07-14 2007-04-17 Gn Resound North America Corporation Hearing system beamformer
DK1307072T3 (da) 2001-10-17 2008-04-14 Siemens Audiologische Technik Fremgangsmåde til et höreapparats drift samt höreapparat
US7369671B2 (en) * 2002-09-16 2008-05-06 Starkey, Laboratories, Inc. Switching structures for hearing aid
DK1453355T3 (da) * 2003-02-26 2013-02-11 Bernafon Ag Signalbearbejdning i et høreapparat
EP1883213B1 (fr) * 2006-07-24 2011-02-09 Harman Becker Automotive Systems GmbH Système et procédé pour calibrer un système mains-libres
US8041054B2 (en) * 2008-10-31 2011-10-18 Continental Automotive Systems, Inc. Systems and methods for selectively switching between multiple microphones

Also Published As

Publication number Publication date
DE102007030067B4 (de) 2011-08-25
EP2009955A3 (fr) 2011-02-23
US8433086B2 (en) 2013-04-30
DE102007030067A1 (de) 2009-01-08
DK2009955T3 (da) 2014-05-26
EP2009955A2 (fr) 2008-12-31
US20090003627A1 (en) 2009-01-01

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