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WO2008107359A1 - Système d'aide auditive présentant une répartition du traitement des signaux, et procédé correspondant - Google Patents

Système d'aide auditive présentant une répartition du traitement des signaux, et procédé correspondant Download PDF

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Publication number
WO2008107359A1
WO2008107359A1 PCT/EP2008/052404 EP2008052404W WO2008107359A1 WO 2008107359 A1 WO2008107359 A1 WO 2008107359A1 EP 2008052404 W EP2008052404 W EP 2008052404W WO 2008107359 A1 WO2008107359 A1 WO 2008107359A1
Authority
WO
WIPO (PCT)
Prior art keywords
hearing
signal
input signal
devices
filtering
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.)
Ceased
Application number
PCT/EP2008/052404
Other languages
German (de)
English (en)
Inventor
Henning Puder
Andre Steinbuss
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 Audiologische Technik GmbH
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 Audiologische Technik GmbH filed Critical Siemens Audiologische Technik GmbH
Publication of WO2008107359A1 publication Critical patent/WO2008107359A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

Links

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
    • H04R25/55—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
    • 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
    • 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
    • H04R2460/03—Aspects of the reduction of energy consumption in hearing devices

Definitions

  • the present invention relates to a hearing system with a hearing device that is portable at one ear and a second device that has a separate housing relative to the hearing device, wherein the hearing device and the second device each have a signal processor and are coupled to each other by a data transmission device for data transmission , Moreover, the present invention relates to a corresponding method for carrying out a signal processing process for a corresponding hearing system.
  • a hearing device is understood to mean, in particular, 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. also Concha hearing aids or canal hearing aids (CIC), provided.
  • BTE behind-the-ear hearing aids
  • ITO in-the-ear hearing aids
  • CIC canal hearing aids
  • the exemplarily listed hearing aids 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 way integrated into a signal processing unit. This basic structure is shown in FIG. 1 using the example of a behind-the-ear hearing device. In 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 of the signal processing unit 3 is carried out by a likewise integrated into the hearing aid housing 1 battery. 5
  • Blind source separation enables statistical signal processing of at least two microphone signals to separate source signals without prior knowledge of the geometric arrangement of the sources. This procedure brings in the
  • N sources can be separated, i. Generate N output signals.
  • BSS blind source separation method
  • document WO 02/28143 A2 discloses a method for operating a hearing aid system with at least two hearing aid devices.
  • the hearing aid devices sound field characteristics are generated and transmitted to different hearing situations between the hearing aids to adapt the signal processing units. Both hearing aids are thus always operated in the same hearing program.
  • document WO 00/00001 discloses a synchronization method for a binaural hearing system.
  • the hearing system again comprises two hearing aids.
  • the hearing aids each of which is switchable in situ in at least two transmission modes from the respective microphone to the respective output transducer arrangement, to operate binaurally, the respectively active transmission modes of the hearing aids are synchronized via a wireless connection between the hearing aids.
  • DE 10 2004 053 790 A1 discloses a method for generating stereo signals for separate sources. For this purpose, a blind source separation of at least two microphone signals for the extraction of BSS filters is performed. After proper filtering, two stereo signals are obtained for each microphone signal.
  • a method for reducing interference power in a microphone is shown in the document DE 10 2004 052 912 A 1.
  • the microphone signals of several microphones are adaptively filtered as a function of at least one parameter.
  • the directivity of the directional microphone obtained in this case is adjusted by changing the at least one parameter such that the sum of noise power including microphone noise is reduced.
  • the object of the present invention is a
  • this object is achieved by a hearing system with a hearing device that is portable at one ear and a second device that has a separate housing relative to the hearing device, wherein the hearing device and the second device each have a signal processor and by a data transmission device with each other for data transmission are coupled, and wherein a signal processing process is divided into two signal processors, so that two sub-processes of the signal processing process on the two signal processors can run parallel in time, and an input signal for the signal processing process from the hearing to the second device or vice versa, the transferable Input signal there in the respective subprocess processed and the resulting output signal for further processing to the other device is retransmitted. It does not have to be a single input signal, but can be provided on both sides of several input signals.
  • the invention provides a method for carrying out a signal processing process for a hearing system, the at least one hearing device and a further device with separate housings and one each Signal processor, by transmitting an input signal from the hearing device to the other device or vice versa, by processing the input signal in a subprocess of the signal processing process, which runs in that of the two devices that had received the input signal by retransmitting one of the input signal Output signal to the device from which the input signal comes, and by further processing the output signal of those of the two devices, which had received the output signal from the other device.
  • the second device is also a hearing device. This makes it possible to divide the computational effort arising in the hearing system between the two hearing devices or hearing aids, from which both hearing devices profit.
  • the second device may also be a remote control with which the hearing device can be operated.
  • the remote control can also serve to operate a binaural hearing system, so that the computing capacity can be divided into three or more devices.
  • the hearing devices also each receive an input signal and exchange it via the data transmission devices.
  • all filter parameters are calculated for blind source separation filtering, and in the other hearing device the corresponding complete filtering is carried out after transmission of the filter parameters. In this case, the entire package of filter calculation and filtering is distributed to both hearing devices.
  • two equally compute-intensive algorithms are distributed to the individual processors in the hearing system.
  • one or more arbitrary algorithms can be distributed among the processors of the hearing system.
  • the data is wirelessly transmitted between the components of the hearing system.
  • the available processors of the hearing system can be used flexibly for complex calculations also spontaneously.
  • FIG. 1 shows the basic structure of a hearing aid and 2 shows a block diagram of a hearing aid system according to the invention.
  • the solution according to the invention to the problem of power consumption reduction is to distribute the computation of complex algorithms, such as BSS, over several signal processors.
  • signal processors in this case, both those of two hearing aids and another external signal processor, which is housed for example in a remote control conceivable.
  • the required computing power can be distributed to the processors, so that the entire computing capacity of the system can be reduced or used more meaningfully.
  • the calculation of filter values and the filtering itself are split between the two hearing aids 10, 20.
  • the two hearing aids 10, 20 separated by a dashed line. Even though they are physically separate, there is data communication between them.
  • the first hearing device 10 has at least one microphone 11 and likewise the second hearing device 20 has at least one microphone 21.
  • the two hearing aids first exchange the recorded signals, i. the microphone or input signals to each other.
  • the entire signal processing of each hearing aid 10, 20 is symbolized only by the filtering that is essential here.
  • the input signals in the hearing device 10 are fed to a filter unit 12, which is an individual BSS
  • the filter unit 12 in the present example has four filters Fl, F2, F3 and F4, which are to be fed with individual parameters.
  • the filtering on However, it is very compute-consuming. The calculation of the filter parameters themselves is likewise computation-intensive. Therefore, the calculation of the filter parameters is shifted here into the second hearing device 20.
  • an adaptation unit 22 calculates the filter parameters and delivers them via cable connection or wireless to the first hearing device 10 or its filter unit 12. After filtering, the BSS output signals are fed to a selection unit 13, with which the desired source is automatically selected, for example, by classification can be. The selected signal will now be for the binaural
  • a corresponding filtering or signal processing symbolized by the transfer functions Gl and G2, in processing units 14, 24 instead.
  • the two transfer functions G1 and G2 can be calculated, for example, from the filter coefficients F1, F2, F3 and F4 according to the document DE 10 1004 053 790 A1. Therefore, a control line 15 from the filter unit 12 to the processing unit 14 is provided in the first hearing device 10. Likewise, a control line 25 is provided between the adaptation unit 22 and the processing unit 24 in the second hearing device 20.
  • the output signals of the processing units 14, 24 are supplied to a respective loudspeaker 16, 26 in the respective hearing device 10, 20.
  • the entire BSS processing need not be carried out individually in each hearing device 10, 20. Rather, a part of the BSS algorithm is executed or calculated in the one hearing device and the remaining part in the other hearing device. The resulting filter signal is then made available to both hearing aids. Due to the fact that the BSS processing for the two hearing aids has to be carried out only once, computing capacity can be saved, whereby the power consumption of both hearing aids decreases.
  • the distribution of computationally intensive, complex algorithms on a plurality of signal processors is not limited to the example of FIG.
  • the division into the signal processors can also be carried out in such a way that, in the case of BSS processing, both the adaptation, ie the filtering parameter calculation and the filtering itself, each depend on the two hearing aids or the hearing aid and the remote control or the hearing aid and a separate external signal processor is divided.
  • the hearing aids or the devices involved in the division initially exchange the recorded signals with each other.
  • these signals are supplied to the individual BSS filters, wherein each device calculates only half of the filters and the necessary parameters to the other device for
  • the filter values Fl and F2 in the first hearing device and the filter values F3 and F4 in the second hearing device can be calculated.
  • Each hearing device carries out the corresponding filtering and one of the two hearing aids then transmits its filtered signals to the other hearing device for further processing, so that in the latter hearing device, for example, the summation can be carried out, which is indicated in FIG. 2 in the filter unit 12.
  • the further signal processing can then take place according to the example of FIG.
  • the BSS processing and a classification are divided into two hearing aids or devices.
  • the hearing aids initially exchange the recorded signals with one another, as in the other exemplary embodiments.
  • the first hearing aid processes these signals through the classification unit, while the second hearing aid calculates the BSS algorithm.
  • control signals for. B. for source selection, to be exchanged between two hearing aids.
  • the exchange of the final processed signals takes place again and classification data for further hearing aid signal processing.

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

Abstract

L'objectif de cette invention est de réduire la consommation électrique des dispositifs d'aide auditive d'un système d'aide auditive. A cet effet, des algorithmes complexes sont répartis dans les processeurs d'un dispositif d'aide auditive (10) et d'un dispositif (20) supplémentaire du système d'aide auditive. Par exemple, un signal d'entrée est transmis par le dispositif d'aide auditive au dispositif supplémentaire (20) ou inversement pour y être traité lors d'un processus partiel (22) du processus de traitement de signaux complet. Un résultat du processus partiel (22) est transmis (32) au dispositif d'aide auditive (10). Puis, un signal de sortie résultant du signal d'entrée est transmis en retour (33) au dispositif (20) dont provient le signal d'entrée. Enfin, le signal de sortie reçu est soumis à un traitement ultérieur (14, 16, 24, 26) dans les dispositifs respectifs (10, 20).
PCT/EP2008/052404 2007-03-05 2008-02-28 Système d'aide auditive présentant une répartition du traitement des signaux, et procédé correspondant Ceased WO2008107359A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE102007010601A DE102007010601A1 (de) 2007-03-05 2007-03-05 Hörsystem mit verteilter Signalverarbeitung und entsprechendes Verfahren
DE102007010601.9 2007-03-05

Publications (1)

Publication Number Publication Date
WO2008107359A1 true WO2008107359A1 (fr) 2008-09-12

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PCT/EP2008/052404 Ceased WO2008107359A1 (fr) 2007-03-05 2008-02-28 Système d'aide auditive présentant une répartition du traitement des signaux, et procédé correspondant

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DE (1) DE102007010601A1 (fr)
WO (1) WO2008107359A1 (fr)

Families Citing this family (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102020202725B4 (de) 2020-03-03 2022-11-17 Sivantos Pte. Ltd. Binaurales Hörsystem mit zwei im oder am Ohr des Nutzers getragenen Hörinstrumenten sowie Verfahren zum Betrieb eines solchen Hörsystems
DE102021103769B4 (de) 2021-02-17 2022-10-27 Clir Technologies Gmbh Verfahren zur Signalverarbeitung

Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5479522A (en) * 1993-09-17 1995-12-26 Audiologic, Inc. Binaural hearing aid
EP0941014A2 (fr) * 1998-03-03 1999-09-08 Siemens Audiologische Technik GmbH Système d'appareil auditif avec deux prothèses auditives et méthode de fonctionnement d'un tel système auditif
EP1017252A2 (fr) * 1998-12-31 2000-07-05 Resistance Technology, Inc. Système d'appareil auditif
WO2004028203A2 (fr) * 2002-09-18 2004-04-01 Stichting Voor De Technische Wetenschappen Combinaison aide auditive/lunettes
WO2004114722A1 (fr) * 2003-06-24 2004-12-29 Gn Resound A/S Systeme de prothese auditive binaural a traitement sonore coordonne
EP1643801A2 (fr) * 2004-09-30 2006-04-05 Siemens Audiologische Technik GmbH Utilisation d'un système de prothèse auditive avec au moins deux prothèses auditives
EP1858291A1 (fr) * 2006-05-16 2007-11-21 Phonak AG Système auditif et méthode de déterminer information sur un espace sonore

Family Cites Families (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1999004385A1 (fr) 1997-07-16 1999-01-28 Seiko Epson Corporation Dispositif a cristaux liquides, procede d'attaque de ce dispositif et ecran de projection et equipement electronique fabriques au moyen de ce dispositif
DE69838989T2 (de) * 1998-02-18 2008-05-29 Widex A/S Binaurales digitales hörhilfesystem
DK1221277T3 (da) 1999-10-15 2007-02-05 Phonak Ag Binaural synkronisering
DE10048354A1 (de) 2000-09-29 2002-05-08 Siemens Audiologische Technik Verfahren zum Betrieb eines Hörgerätesystems sowie Hörgerätesystem
DE10351509B4 (de) * 2003-11-05 2015-01-08 Siemens Audiologische Technik Gmbh Hörgerät und Verfahren zur Adaption eines Hörgeräts unter Berücksichtigung der Kopfposition
DE102004052912A1 (de) 2004-11-02 2006-05-11 Siemens Audiologische Technik Gmbh Verfahren zur Reduktion von Störleistungen bei einem Richtmikrophon und entsprechendes Akustiksystem
DE102004053790A1 (de) 2004-11-08 2006-05-18 Siemens Audiologische Technik Gmbh Verfahren zur Erzeugung von Stereosignalen für getrennte Quellen und entsprechendes Akustiksystem

Patent Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5479522A (en) * 1993-09-17 1995-12-26 Audiologic, Inc. Binaural hearing aid
EP0941014A2 (fr) * 1998-03-03 1999-09-08 Siemens Audiologische Technik GmbH Système d'appareil auditif avec deux prothèses auditives et méthode de fonctionnement d'un tel système auditif
EP1017252A2 (fr) * 1998-12-31 2000-07-05 Resistance Technology, Inc. Système d'appareil auditif
WO2004028203A2 (fr) * 2002-09-18 2004-04-01 Stichting Voor De Technische Wetenschappen Combinaison aide auditive/lunettes
WO2004114722A1 (fr) * 2003-06-24 2004-12-29 Gn Resound A/S Systeme de prothese auditive binaural a traitement sonore coordonne
EP1643801A2 (fr) * 2004-09-30 2006-04-05 Siemens Audiologische Technik GmbH Utilisation d'un système de prothèse auditive avec au moins deux prothèses auditives
EP1858291A1 (fr) * 2006-05-16 2007-11-21 Phonak AG Système auditif et méthode de déterminer information sur un espace sonore

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