EP2793488B1 - Adaptation de microphone binaurale au moyen de sa propre voix - Google Patents

Adaptation de microphone binaurale au moyen de sa propre voix Download PDF

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Publication number
EP2793488B1
EP2793488B1 EP14157214.9A EP14157214A EP2793488B1 EP 2793488 B1 EP2793488 B1 EP 2793488B1 EP 14157214 A EP14157214 A EP 14157214A EP 2793488 B1 EP2793488 B1 EP 2793488B1
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EP
European Patent Office
Prior art keywords
signal
voice
hearing aid
wearer
acousto
Prior art date
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Application number
EP14157214.9A
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German (de)
English (en)
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EP2793488A1 (fr
Inventor
Homayoun Kamkar Parsi
Marko Lugger
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Sivantos Pte Ltd
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Sivantos Pte Ltd
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Publication of EP2793488A1 publication Critical patent/EP2793488A1/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
    • H04R25/43—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
    • H04R25/40—Arrangements for obtaining a desired directivity characteristic
    • H04R25/407—Circuits for combining signals of a plurality of transducers
    • 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
    • H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
    • H04R25/552—Binaural
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R29/00—Monitoring arrangements; Testing arrangements
    • H04R29/004—Monitoring arrangements; Testing arrangements for microphones
    • H04R29/005—Microphone arrays
    • H04R29/006—Microphone matching

Definitions

  • the present invention relates to a hearing aid system, wherein the hearing aid system has a first and a second hearing aid.
  • the first hearing aid has a first acousto-electrical converter and the second hearing aid has a second acousto-electrical converter.
  • the transducers are designed to convert incoming acoustic signals into first and second electrical signals.
  • the hearing aid system has a signal processing device, wherein the signal processing device is in signal connection with the first and the second acousto-electrical converter.
  • 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 (ITE), e.g. Concha hearing aids or canal hearing aids (ITE, CIC).
  • BTE behind-the-ear hearing aids
  • RIC hearing aid with external receiver
  • ITE in-the-ear hearing aids
  • ITE in-the-ear hearing aids
  • ITE in-the-ear hearing aids
  • ITE concha hearing aids or 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 an acoustoelectric transducer, 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 device.
  • binaural hearing is an essential prerequisite for spatial hearing and sound wave localization. Because of the importance of binaural processes in analyzing hearing situations, it is understandable that hearing-impaired individuals benefit more from two hearing aids for binaural care than from a single hearing aid for monaural care.
  • the binaural signal processing is particularly sensitive to differences between the signals, since the natural differences in the signals from both sides of the head differ only slightly in amplitude, phase and / or frequency distribution. Therefore, it is particularly important that the signal processing in the hearing aids not artificially deviations are added.
  • the microphones are particularly susceptible because, because of their small dimensions, small mechanical manufacturing tolerances result in large deviations. For the same reason, the properties can also change during operation, for example due to contamination or material aging. Since this effect usually occurs asymmetrically, the effect is particularly severe.
  • the object of the present invention is therefore to provide a hearing aid system and a method for operating the hearing aid system, which allows a simple and reliable operation over a longer period of use.
  • the hearing aid system according to the invention has a first and a second hearing aid device.
  • the first hearing aid has a first acousto-electrical converter and the second hearing aid has a second acousto-electrical converter.
  • the transducers are designed to convert incoming acoustic signals into first and second electrical signals.
  • the hearing aid system has a signal processing device, wherein the signal processing device is in signal connection with the first and the second acousto-electrical converter.
  • the signal processing device is designed, signal deviations caused by the first and second acousto-electrical converter in the first and / or second electrical signals based on the first and second signals determine and compensate for the wearer's own voice.
  • the hearing aid system according to the invention utilizes in an advantageous manner that the wearer's own voice is distinguished by special features, in particular the symmetry with two hearing aid devices on the two ears of the wearer. It is thus particularly easy to identify deviations between the two electrical signals and then also to compensate them in the signal processing device.
  • the method of operating the hearing aid system shares its advantages.
  • the hearing aid system further comprises means for recognizing the wearer's own voice.
  • the means for recognizing one's own voice is in signal connection with the first and the second acousto-electrical converter and is designed to signal the signal processing device to detect a signal of the wearer's own voice.
  • Such a device for recognizing the wearer's own voice advantageously makes it possible for the signal processing device to determine and compensate the deviations of the first and second electrical signals even during ongoing operation without, for example, the wearer or another person starting an adaptation process.
  • the device for recognizing the wearer's own voice is designed to recognize a signal of his own voice based on a level of the first and / or the second electrical signal.
  • a recognition based on the level is particularly easy to implement.
  • the device for detecting the wearer's own voice is designed to detect a signal of one's own voice based on a phase relationship of the first and the second electrical signal relative to one another.
  • the phase position is particularly sensitive to the position and therefore a detection of your own voice in the middle between the hearing aids can be done very safe.
  • the device for detecting the wearer's own voice may be designed to recognize a signal of his own voice based on a frequency distribution of the first and / or the second electrical signal.
  • the own voice of the wearer Due to the influence of the head on the sound propagation, the own voice of the wearer has a special frequency characteristic which distinguishes the voice from the voices of other persons and facilitates a recognition. This applies in particular to frequency components that are transmitted as structure-borne sound.
  • Fig. 1 shows the basic structure of a hearing aid system 100 according to the invention.
  • the hearing aid system 100 has two hearing aids 110, 110 '.
  • a hearing aid housing 1, 1 ' for carrying behind the ear, one or more microphones 2, 2' for receiving the sound or acoustic signals from the environment are installed.
  • a signal processing device 3, 3 ' which is also integrated in the hearing aid housing 1, 1', processes the first audio signals.
  • the output signal of the signal processing device 3, 3 ' is transmitted to a loudspeaker or receiver 4, 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 that of the signal processing device 3, 3 ' is effected by a likewise integrated into the hearing aid housing 1, 1' battery 5, 5 '.
  • the hearing aid system 100 has a signal connection 6, which is designed to transmit a first electrical signal from the signal processing device 3 to the signal processing device 3 '. It is provided in the preferred embodiment that also signal processing device 3 'transmits a second electrical signal to the signal processing device 3 in the opposite direction.
  • the signal connection 6 can be galvanic. However, in a preferred embodiment, the first and second electrical signals are converted for transmission over the signal connection.
  • the signal connection can be made, for example, inductively, via Bluetooth, optically or another wireless transmission technology.
  • the hearing aid system 100 also includes means 7, 7 'for detecting a separate voice of the wearer having a signal connection with the signal processing unit 3, 3'.
  • the means 7, 7 'for recognizing one's own voice can, as in Fig. 1 represented, an integral part of the signal processing means 3, 3 'be. However, it is also conceivable for the device 7, 7 'to be able to recognize its own voice as a separate device in the hearing aid device 110, 110 ".
  • each hearing aid device its own signal processing means 3, 3 'and get the signals of both microphones 2, 2' supplied.
  • Each of the signal processing devices 2, 2 ' is then able to independently determine and compensate for the signal differences between the microphones 2, 2'.
  • only one of the hearing aid devices 110, 110 “has a signal processing device 3, 3 ', which performs the signal processing, determining and compensating and the resulting signal via the signal connection 6 to the other hearing aid 110, 110' to The same applies to the device 7, 7 'for detecting a separate voice of the wearer, which is either provided in each of the hearing aid devices 110, 110 "or even in one, jointly for both hearing aids 110, 110'.
  • Fig. 2 shows a schematic flow diagram of a method according to the invention in the signal processing device 3, 3 '.
  • the method comprises a step S10 of detecting a first and second acoustic signal of the own voice of the wearer of the hearing aid system with the first and second acousto-electrical converter 2, 2 '.
  • the acousto-electrical converters 2, 2 'or microphones 2, 2' convert the first and second acoustic signals into first and second electrical signals.
  • a signal processing means determines signal deviations caused by the first and second acousto-electric transducers. These deviations may exist between the first and second electrical signals in amplitude, phase and frequency response or any combination thereof.
  • the signal processing device 3, 3 compensates for the determined signal deviations.
  • this can be done, for example, by a frequency-dependent amplification of the relevant signal.
  • a phase deviation can be compensated by an equally frequency-dependent delay.
  • the compensation also takes place with the methods of digital signal processing.
  • the particular compensation parameters are preferably stored in the signal processing means 3, 3 'and used to process the first and second electrical signals until step 30 is re-executed.
  • the hearing aid system 100 detects a signal of a separate voice of the wearer in a step S20.
  • the voice of the wearer is characterized by various special features.
  • the source of voice with larynx and mouth is symmetrically interposed with hearing aids 110, 110 'worn on the ears arranged.
  • a high degree of symmetry of the signal is to be expected. Therefore, the sound waves at the first microphone 2 and the second microphone 2 'have a nearly identical phase and amplitude.
  • the means for detecting 7, 7 ' may therefore, for example, assign first and second electrical signals, which have almost identical amplitude and phase, to the wearer's own voice.
  • These signals also have their own frequency response and amplitude with respect to signals from voices of other people in front of the carrier, which are caused by the attenuation of the head and also by sound conduction in the head. It would also be conceivable that the microphones 2, 2 'are specially designed to also record structure-borne sound, or that, for example, other separate transducers are provided for this purpose and in this way the wearer's own voice is recognized.
  • the steps S10 to S40 can be performed once or repeated independently in response to a signal from the outside or at intervals.

Landscapes

  • Engineering & Computer Science (AREA)
  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Neurosurgery (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Circuit For Audible Band Transducer (AREA)

Claims (8)

  1. Système d'assistance auditive, le système d'assistance auditive (100) possédant :
    - un premier et un deuxième appareil d'assistance auditive (110, 110'), le premier appareil d'assistance auditive (110) possédant un premier convertisseur acousto-électrique (2) et le deuxième appareil d'assistance auditive possédant un deuxième convertisseur acousto-électrique (2') et les convertisseurs (2, 2') étant conçus pour convertir les signaux acoustiques entrants en premiers et deuxièmes signaux électriques ;
    - un dispositif de traitement de signal (3, 3'), le dispositif de traitement de signal (3, 3') se trouvant en liaison de signal avec le premier et le deuxième convertisseur acousto-électrique (2, 2'), au moins l'une des liaisons de signal avec le premier et le deuxième convertisseur acousto-électrique (2, 2') étant réalisée sans fil,
    le dispositif de traitement de signal (3, 3') étant conçu pour déterminer et pour compenser les variations de signal provoquées par le premier et le deuxième convertisseur acousto-électrique (2, 2') dans les premiers et/ou deuxièmes signaux électriques au moyen des premiers et deuxièmes signaux électriques d'une voix propre du porteur,
    et le système d'assistance auditive (100) possédant en outre un dispositif (7, 7') destiné à reconnaître la voix propre du porteur, le dispositif (7, 7') destiné à reconnaître la voix propre du porteur se trouvant en liaison de signal avec le premier et le deuxième convertisseur acousto-électrique (2, 2') et étant conçu pour signaler au dispositif de traitement de signal (3, 3') la reconnaissance d'un signal de la voix propre du porteur.
  2. Système d'assistance auditive selon la revendication 1, le dispositif (7, 7') destiné à reconnaître la voix propre du porteur étant conçu pour reconnaître un signal de la voix propre au moyen d'un niveau du premier et/ou du deuxième signal électrique.
  3. Système d'assistance auditive selon la revendication 1 ou 2, le dispositif (7, 7') destiné à reconnaître la voix propre du porteur étant conçu pour reconnaître un signal de la voix propre au moyen d'un déphasage entre le premier et le deuxième signal électrique.
  4. Système d'assistance auditive selon l'une des revendications 1 à 3, le dispositif (7, 7') destiné à reconnaître la voix propre du porteur étant conçu pour reconnaître un signal de la voix propre au moyen d'une distribution des fréquences du premier et/ou du deuxième signal électrique.
  5. Procédé pour adapter un système d'assistance auditive (100), le système d'assistance auditive (100) possédant :
    - un premier et un deuxième appareil d'assistance auditive (110, 110'), le premier appareil d'assistance auditive (110) possédant un premier convertisseur acousto-électrique (2) et le deuxième appareil d'assistance auditive (110') possédant un deuxième convertisseur acousto-électrique (2') ;
    - un dispositif de traitement de signal (3, 3'), le dispositif de traitement de signal se trouvant en liaison de signal avec le premier et le deuxième convertisseur acousto-électrique (2, 2'), au moins l'une des liaisons de signal avec le premier et le deuxième convertisseur acousto-électrique (2, 2') étant réalisée sans fil,
    le procédé comprenant les étapes suivantes :
    - détection d'un premier et d'un deuxième signal acoustique de la voix propre du porteur du système d'assistance auditive (100) avec les premier et deuxième convertisseurs acousto-électrique (2, 2') et conversion en un premier et un deuxième signal électrique ;
    - détermination de variations de signal provoquées par le premier et le deuxième convertisseur acousto-électrique (2, 2') dans les premiers et/ou deuxièmes signaux électriques au moyen des premiers et deuxièmes signaux électriques de la voix propre du porteur ;
    - compensation des variations de signal du premier et du deuxième signal électrique dans le dispositif de traitement de signal (3, 3'),
    et l'appareil possédant en outre un dispositif (7, 7') destiné à reconnaître la voix propre du porteur, le dispositif (7, 7') destiné à reconnaître la voix propre du porteur se trouvant en liaison de signal avec le premier et le deuxième convertisseur acousto-électrique (2, 2') et le procédé comprenant en outre l'étape dans laquelle le dispositif (7, 7') destiné à reconnaître la voix propre du porteur signale au dispositif de traitement de signal (3, 3') la reconnaissance d'un signal de la voix propre porteur.
  6. Procédé selon la revendication 5, le dispositif (7, 7') destiné à reconnaître la voix propre du porteur reconnaissant un signal de la voix propre au moyen d'un niveau du premier et/ou du deuxième signal électrique.
  7. Procédé selon la revendication 5 ou 6, le dispositif (7, 7') destiné à reconnaître la voix propre du porteur reconnaissant un signal de la voix propre au moyen d'un déphasage entre le premier et le deuxième signal électrique.
  8. Procédé selon l'une des revendications 5 à 7, le dispositif (7, 7') destiné à reconnaître la voix propre du porteur reconnaissant un signal de la voix propre au moyen d'une distribution des fréquences du premier et/ou du deuxième signal électrique.
EP14157214.9A 2013-04-19 2014-02-28 Adaptation de microphone binaurale au moyen de sa propre voix Active EP2793488B1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102013207080.2A DE102013207080B4 (de) 2013-04-19 2013-04-19 Binaurale Mikrofonanpassung mittels der eigenen Stimme

Publications (2)

Publication Number Publication Date
EP2793488A1 EP2793488A1 (fr) 2014-10-22
EP2793488B1 true EP2793488B1 (fr) 2017-11-08

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EP14157214.9A Active EP2793488B1 (fr) 2013-04-19 2014-02-28 Adaptation de microphone binaurale au moyen de sa propre voix

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US (1) US9565499B2 (fr)
EP (1) EP2793488B1 (fr)
DE (1) DE102013207080B4 (fr)
DK (1) DK2793488T3 (fr)

Families Citing this family (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DK3588983T3 (da) * 2018-06-25 2023-04-17 Oticon As Høreanordning tilpasset til at matche indgangstransducere ved anvendelse af stemmen af en bruger af høreanordningen
CN111464905A (zh) * 2020-04-09 2020-07-28 电子科技大学 基于智能穿戴设备的听力增强方法、系统和穿戴设备

Family Cites Families (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
ATE298968T1 (de) 2001-10-05 2005-07-15 Oticon As Verfahren zum programmieren einer kommunikationseinrichtung und programmierbare kommunikationseinrichtung
DE10228632B3 (de) * 2002-06-26 2004-01-15 Siemens Audiologische Technik Gmbh Richtungshören bei binauraler Hörgeräteversorgung
DK1599742T3 (da) 2003-02-25 2009-07-27 Oticon As Fremgangsmåde til detektering af en taleaktivitet i en kommunikationsanordning
US20070147635A1 (en) * 2005-12-23 2007-06-28 Phonak Ag System and method for separation of a user's voice from ambient sound
DE102007037659B4 (de) * 2007-08-09 2013-06-13 Siemens Audiologische Technik Gmbh Verfahren zum Betrieb eines Hörgerätesystems und Hörgerätesystem
US8031881B2 (en) * 2007-09-18 2011-10-04 Starkey Laboratories, Inc. Method and apparatus for microphone matching for wearable directional hearing device using wearer's own voice
US8588441B2 (en) 2010-01-29 2013-11-19 Phonak Ag Method for adaptively matching microphones of a hearing system as well as a hearing system
DE102010018877A1 (de) * 2010-04-30 2011-06-30 Siemens Medical Instruments Pte. Ltd. Verfahren und Anordnung zur Sprachsteuerung von Hörgeräten
EP2591615B1 (fr) * 2010-07-05 2014-03-05 Widex A/S Système et procédé de mesure et de validation de l'effet d'occlusion d'un utilisateur d'aide auditive

Also Published As

Publication number Publication date
DK2793488T3 (da) 2018-02-12
US9565499B2 (en) 2017-02-07
EP2793488A1 (fr) 2014-10-22
DE102013207080A1 (de) 2014-10-23
DE102013207080B4 (de) 2019-03-21
US20140314258A1 (en) 2014-10-23

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