EP1912474A1 - Procédé pour le fonctionnement d'une prothèse auditive et prothèse auditive - Google Patents

Procédé pour le fonctionnement d'une prothèse auditive et prothèse auditive Download PDF

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Publication number
EP1912474A1
EP1912474A1 EP20070117250 EP07117250A EP1912474A1 EP 1912474 A1 EP1912474 A1 EP 1912474A1 EP 20070117250 EP20070117250 EP 20070117250 EP 07117250 A EP07117250 A EP 07117250A EP 1912474 A1 EP1912474 A1 EP 1912474A1
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EP
European Patent Office
Prior art keywords
hearing aid
speaker
acoustic
electrical
signal processing
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.)
Granted
Application number
EP20070117250
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German (de)
English (en)
Other versions
EP1912474B1 (fr
Inventor
Eghart Fischer
Matthias Fröhlich
Jens Hain
Henning Puder
André Steinbuß
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Sivantos GmbH
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Siemens Audioligische Technik GmbH
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Publication date
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Publication of EP1912474A1 publication Critical patent/EP1912474A1/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
    • H04R25/40—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
    • H04R2225/41—Detection or adaptation of hearing aid parameters or programs to listening situation, e.g. pub, forest

Definitions

  • the invention relates to a method for operating a hearing aid consisting of a single or two hearing aids. Furthermore, the invention relates to a corresponding hearing aid or a corresponding hearing aid.
  • noise or unwanted acoustic signals that interfere with the voice of a counterpart or a wanted acoustic signal are omnipresent. People with a hearing loss are particularly susceptible to such noise. Conversations in the background, acoustic interference with digital devices (cell phones), car or other environmental noise can make it very difficult for a person with hearing loss to understand a desired speaker. Reducing the level of noise in an acoustic signal coupled with an automatic focus on a desired acoustic signal component can significantly improve the performance of an electronic speech processor as used in modern hearing aids.
  • Hearing aids with digital signal processing have been introduced in the recent past. They include one or more microphones, A / D converters, digital signal processors and speakers. Usually, the digital signal processors divide the incoming signals into a plurality of frequency bands. Within each band, signal amplification and processing may be individually adjusted in accordance with requirements for a particular hearing aid wearer to improve the intelligibility of a particular component. Furthermore, algorithms for feedback and noise minimization are available in digital signal processing, but have significant disadvantages. A disadvantage of the currently existing algorithms for noise minimization z. B. whose maximum achievable improvement in hearing aid acoustics when speech and background sounds are in the same frequency region and therefore unable to distinguish between spoken speech and background noise. (See also EP 1 017 253 A2 )
  • acoustic signal processing there are spatial (eg directional microphone, beamforming), statistical (eg blind source separation) or mixed methods, which are u. a. by means of algorithms from several simultaneously active sound sources can separate a single or a plurality thereof.
  • the blind source separation by means of statistical signal processing of at least two microphone signals allows to perform a separation of source signals without prior knowledge of their geometric arrangement.
  • This method has advantages over conventional directional microphone approaches when used in hearing aids.
  • BSS method Blind Source Separation
  • n microphones up to n sources can be separated, i. H. n Generate output signals.
  • the control of directional microphones in the sense of blind source separation is subject to ambiguity, as soon as several competing sources of use, eg. B. speaker, present simultaneously.
  • the blind source separation allows in principle the separation of the different sources, provided that they are spatially separated; the ambiguity, however, reduces the potential benefit of a directional microphone, although it is precisely in such scenarios that a directional microphone can be very useful for improving speech intelligibility.
  • the hearing aid or the mathematical algorithms for blind source separation are in principle faced with the problem of having to decide which of the signals generated by the blind source separation should be passed on most advantageously to the user of the algorithm, ie the hearing aid wearer.
  • the choice made by this algorithm must be so based on assumptions about the probable will of the listener.
  • a more flexible acoustic signal selection method can be formulated, which is not restricted by a geometric source distribution. It is therefore an object of the invention to provide an improved method for operating a hearing aid, as well as an improved hearing aid.
  • a selection of the speaker acoustic source to be reproduced is made in such a way that - if present - a preferred speaker or a speaker known to the hearing aid wearer is always reproduced by the hearing aid.
  • a database with profiles of a single or several such preferred speakers is created for this purpose. For the output signals of a source separation then acoustic profiles are determined or evaluated and compared with the entries in the database. In the event that one of the output signals of the source separation matches the or a database profile, then this electrical acoustic signal or this speaker is then explicitly selected and made available to the hearing aid wearer via the hearing aid. Such a decision may take precedence over other decisions that have lower decision-making power in such a case.
  • a method for operating a hearing aid wherein for tracking and selective amplification of a speaker acoustic source or an electrical speaker signal, by signal processing of the hearing aid for preferably all electrical acoustic signals available to it, comparison is made with voice profiles of desired or known speakers in which the voice profiles are stored in a database, which is preferably located in the hearing aid (s) of the hearing aid.
  • the speaker acoustic source or the speaker acoustic sources which largely coincide with the voice profiles of the database, are tracked by the signal processing and are particularly taken into account in an acoustic output signal of the hearing aid.
  • a hearing aid is provided, wherein by means of an acoustic module (signal processing) of the hearing aid electrical acoustic signals with voice profile entries of a database can be adjusted.
  • the acoustic module selects from the electrical acoustic signals at least an electrical speaker signal matching a voice profile of a desired or known speaker, wherein this electrical speaker signal can be particularly taken into account in an output signal of the hearing aid.
  • the hearing aid it is possible, depending on the number of existing microphones in the hearing aid to select a single or a plurality of speaker acoustic sources from the ambient sound and to emphasize the output sound of the hearing aid. In this case, it is possible to arbitrarily set a volume of the speaker acoustic source or the speaker acoustic sources in the output sound of the hearing aid.
  • the signal processing has a demixing module, which preferably operates as a device for blind source separation for separating the acoustic sources of ambient sound. Furthermore, the signal processing has a post-processor module, which establishes a corresponding operating mode "speaker" in the hearing aid when detecting an acoustic source with a high probability of speaker. Furthermore, the signal processing may comprise a preprocessor module - the electrical output signals of which are the electrical input signals of the demix module - which normalizes and processes electrical acoustic signals originating from microphones of the hearing aid. Regarding the preprocessor module and the demixing module (unmixer), please refer to the EP 1 017 253 A2 Refer to paragraphs [0008] to [0023].
  • a comparison of the speech profiles stored in the database with the acoustic profiles currently received by the hearing aid takes place, or a comparison of the profiles of the electrical acoustic signals currently generated by the signal processing with the speech profiles stored in the database takes place.
  • This preferably takes place by the signal processing or the post-processor module, wherein the database can be part of the signal processing or the post-processor module or part of the hearing aid.
  • the post-processor module tracks and selects the electrical speaker signal (s) and generates a corresponding electrical output acoustic signal for a speaker of the hearing aid.
  • the hearing aid has a data interface via which the hearing aid can communicate with a peripheral device.
  • a data interface via which the hearing aid can communicate with a peripheral device.
  • This is z. B. possible to exchange voice profiles of the desired or known speaker with other hearing aids. It is also possible to edit voice profiles in a computer and then transfer them to the hearing aid to update them.
  • the limited space within the hearing aid can be better utilized by the data interface, since this external processing and thus a "streamlining" the voice profiles is possible.
  • an external computer several databases with different language profiles, eg. As private and business, created and the hearing aid thus be configured for an upcoming situation accordingly.
  • the hearing aid or the signal processing can be trained on a speech characteristic of a new speaker. Furthermore, it is also possible to create additional voice profiles of the same speaker, which z. B. for different acoustic situations, eg. B. near / far, advantage.
  • the hearing aid or the signal processing on a device which meets a downstream corresponding acoustic source selection could e.g. B. look in such a way that, upon detection of (unknown) language in an electrical acoustic signal that speaker or those speakers are selected, which are in the direction of the hearing aid wearer. In addition, it is possible to make this subordinate decision as to which speaker is as close as possible to the hearing aid wearer or speaks loudest.
  • the hearing aid includes a remote control
  • the hearing aid can be made smaller overall and offer more storage space for voice profiles.
  • the remote control can communicate wireless or wired with the hearing aid.
  • the invention is not limited to such blind source separation, but rather is intended to broadly include source separation methods for acoustic signals. Therefore, this BSS module is also referred to as demixing module.
  • a "tracking" of an electrical speaker signal by a hearing aid of a hearing aid wearer is mentioned.
  • This is to be understood as one of the hearing aid or a signal processing of the hearing aid or a post-processor module of the signal processing selection of one or a plurality of electrical speaker signals which are selected by the hearing aid electrically or electronically from other sources of acoustic ambient sound and which in a relation to the other acoustic sources of ambient sound amplified way, d. H. in a way perceived as louder for the hearing aid wearer.
  • tracking the electrical speaker signal is a position of the hearing aid wearer in the room, in particular a position of the hearing aid in the room, d. H. a viewing direction of the hearing aid wearer, preferably not considered.
  • Fig. 1 shows the state of the art, as by the EP 1 017 253 A2 (see paragraph [0008] ff) is taught.
  • a hearing aid 1 has two microphones 200, 210, which together can form a directional microphone system, for generating two electrical acoustic signals 202, 212.
  • Such a microphone arrangement gives the two electrical output signals 202, 212 of the microphones 200, 210 an inherent directional characteristic.
  • Each of the microphones 200, 210 receives an ambient sound 100 that is a composite of unknown, acoustic signals from an unknown number of acoustic sources.
  • the electrical acoustic signals 202, 212 are processed primarily in three stages.
  • the electrical acoustic signals 202, 212 are preprocessed in a preprocessing module 310 to improve the directional characteristic, which begins with a normalization of the original signals (equalizing the signal strength).
  • a blind source separation takes place in a BSS module 320, wherein the output signals of the preprocessor module 310 a demixing subject.
  • the output signals of the BSS module 320 are post-processed in a post-processor module 330 to produce a desired electrical output signal 332 which serves as input to a handset 400 and loudspeaker 400 of the hearing aid 1, respectively, and a sound generated thereby to the hearing aid wearer leave.
  • steps 1 and 3 that is, preprocessor module 310 and postprocessor module 330, are optional.
  • FIG. 2 now shows a first embodiment of the invention, wherein in a signal processing 300 of the hearing aid 1 a demixing module 320, hereinafter referred to as BSS module 320, is located, to which a post-processor module 330 is connected downstream.
  • a preprocessor module 310 can be provided which appropriately prepares or prepares the input signals for the BSS module 320.
  • the signal processing 300 is preferably carried out in a DSP (Digital Signal Processor) or in an ASIC (Application Specific Integrated Circuit).
  • acoustic sources 102 are independent independent acoustic 102, 104 or signal sources 102, 104 exist in ambient sound 100, one of these acoustic sources 102 being a speaker source 102 of a speaker known to the hearing aid wearer and the other acoustic source 104 being a noise source 104.
  • the speaker acoustic source 102 is to be selected and tracked by the hearing aid 1 and the signal processor 300, respectively, and be a primary acoustic component of the handset 400 so that an output sound 402 of the speaker 400 mainly contains this signal (102).
  • the two microphones 200, 210 of the hearing aid 1 each receive a mixture of the two acoustic signals 102, 104 - illustrated by the dotted arrow (representing the preferred, acoustic signal 102) and the solid arrow (representing the non-preferred, acoustic signal 104). and either pass them to the preprocessor module 310 or equal to the BSS module 320 as electrical input signals.
  • the two microphones 200, 210 can be distributed as desired. They may be located in a single hearing aid 1 of the hearing aid 1 or distributed to both hearing aids 1. In addition, it is possible, for. B. one or both microphones 200, 210 outside the hearing aid 1, z. B.
  • the electrical input signals of the BSS module 320 need not necessarily originate from a single hearing device 1 of the hearing aid 1.
  • a hearing aid 1 consisting of two hearing aids 1 has a total of four or six microphones.
  • the preprocessor module 310 prepares the data for the BSS module 320, which in turn forms two separate output signals from its two mixed input signals, depending on the capability, each of which represents one of the two acoustic signals 102, 104.
  • the two separate output signals of the BSS module 320 are input signals for the post-processor module 330, in which it is now decided which of the two acoustic signals 102, 104 is output to the loudspeaker 400 as an electrical output signal 332.
  • the post-processor module 330 for the electrical acoustic signals 322, 324 simultaneously performs a comparison with acoustic signals / data of desired or known speakers whose acoustic signals / data are stored in a database 340. If the post-processor module 330 identifies a known speaker or acoustic source 102 in an electrical acoustic signal 322, 324, ie ambient sound 100, it selects this electrical speaker signal 322 and outputs it in an amplified manner relative to other acoustic signals 324 as output electrical acoustic signal 332 (essentially corresponds to the acoustic signal 322).
  • the database 340 in which speech profiles P of the speakers are stored is located in the post-processor module 330, the signal processor 300 or in the hearing aid 1.
  • a remote control 10 belongs to the hearing aid 1 or the hearing aid 1 is a remote control 10 (ie the remote control 10 is part of the hearing aid 1), it is also possible to accommodate the database 340 in the remote control 10. This is quite advantageous, since the remote control 10 is not subject to such great size restrictions as the part of the hearing aid 1 which is on or in the ear, so that more storage space for the database 340 can be available.
  • a communication with a peripheral device of the hearing aid 1, z. As a computer, since in such a case, a data interface necessary for communication can also be located within the remote control 10 (see also below).
  • FIG. 3 shows the method according to the invention and the hearing aid 1 according to the invention during the processing of three acoustic signal sources s 1 (t), s 2 (t), s n (t), which together form the ambient sound 100.
  • This ambient sound 100 is recorded in each case by three microphones, each of which outputs an electrical microphone signal x 1 (t), x 2 (t), x n (t) to the signal processor 300.
  • the signal processor 300 has no preprocessor module 310, but may preferably contain this. (This also applies analogously to the first embodiment of the invention).
  • the electrical microphone signals x 1 (t), x 2 (t), x n (t) are input signals to the BSS module 320, which in each case in the electrical microphone signals x 1 (t), x 2 (t), x n (t) contained acoustic signals by acoustic sources s 1 (t), s 2 (t), s n (t) s' 1 (t), s' 2 (t), s' n (t) outputs to the post-processor module 330 as electrical output signals.
  • the hearing aid 1 is at least sufficiently capable of delivering such an acoustic signal s ' 1 (t), s' n (t) to the hearing aid wearer in such a way that he or she can sufficiently correctly interpret the information contained therein, ie at least sufficiently understands the speaker information contained therein.
  • the third acoustic signal s' 2 (t) (in this embodiment largely corresponds to the acoustic source s 2 (t)) contains no or hardly usable speaker information.
  • the post-processor module 330 will now be the electric acoustic signals s' 1 (t), s' 2 (t), s' n (t) examined to determine whether it contains speech information of known speakers (speakers Information). These voice information of the known speakers are stored as voice profiles P in the database 340 of the hearing aid 1.
  • the database 340 can in turn be provided in the remote control 10, the hearing aid 1, the signal processing 300 or the post-processor module 330.
  • the post-processor module 330 compares the data stored in the database 340 speech profile P with the electric acoustic signals s '1 (t), s' 2 (t), s 'n (t) and identified in this example, while the relevant electrical speaker signals s' 1 (t) and s' n (t).
  • a profile derivation preferably takes place by the post-processor module 330, which compares all voice profiles P of the database 340 with the electrical acoustic signals s' 1 (t), s' 2 (t), s' n (t).
  • This is preferably done by the post-processor module 330 a profile evaluation of the electrical acoustic signals s' 1 (t), s' 2 (t), s' n (t) instead, the profile evaluation acoustic profiles P 1 (t), P 2 (t), P n (t) created and these acoustic profiles P 1 (t), P 2 (t), P n (t) can then be compared with the language profiles P of the database 340.
  • the post-processor module 330 identifies and outputs the corresponding electrical talker signal s ' 1 (t), s' n (t) this as an electrical acoustic signal 332 to the speaker 400 from.
  • the identification of the acoustic profiles P 1 (t), P 2 (t), P n (t) can take place in that the hearing aid 1 probabilities p 1 (t), p 2 (t), p n (t) for the respective Acoustic profile P 1 (t), P 2 (t), P n (t) with respect to the respective voice profiles P created. This preferably takes place during the profile adjustment, which is followed by a corresponding signal selection. Ie. it is possible by means of the profiles stored in the database 340 to give a respective acoustic profile P 1 (t), P 2 (t), P n (t) a probability p 1 (t), p 2 (t), p n (t ) for a respective speaker 1, 2, n. In the signal selection, it is then possible to select those electrical acoustic signals s' 1 (t), s' 2 (t), s' n (t) which correspond at least to a certain probability for a speaker 1, 2, ..., n.
  • the hearing aid 1 can be brought into a training mode in which the database 340 can be supplied with electrical acoustic signals of desired speakers.
  • the provision of the database 340 with new language profiles P from desired or known speakers can also take place via a data interface of the hearing aid 1. This makes it possible, the hearing aid 1 (also via its remote control 10) to connect to a peripheral device.
  • a dummy source separation method is preferably combined with a speaker classification algorithm. In this way it is ensured that the hearing aid wearer can always best or most clearly perceive the speaker preferred by him or the speaker preferred by him.
  • the hearing aid 1 which of the electrical speaker signals 322; s ' 1 (t), s' n (t) can preferably be reproduced on the hearing aid wearer as the output sound 402, s "(t) .
  • This can be an angle of incidence of the corresponding acoustic source 102, 104; s 1 (t), s 2 (t ), s n (t) may be on the hearing aid 1, with certain angles of incidence being preferred, for example the 0 ° viewing direction or a 90 ° lateral direction of the hearing aid wearer may be preferred s ' 1 (t), s' n (t) - even apart from their different probabilities p 1 (t), p 2 (t), p n (t) for speaker information contained therein (this of course also applies to all Embodiments of the invention) - to weight whether one of the electrical speaker signals 322; s ' 1 (t), s' n (t) is a predominant or
  • this other module of the hearing aid 1 is intended to be incorporated into the post-processor module 330, ie, in such an embodiment, the post-processor module 330 comprises this other module.
  • the present document relates inter alia to a post-processor module 20 of the EP 1 017 253 A2 (Reference numeral after the EP 1 017 253 A2 ), in which by means of a profile evaluation one or more known speakers for an electrical output signal of the post-processor module 20 are selected and reproduced therein at least amplified. See also paragraph [0025] of EP 1 017 253 A2 . Further, in the invention, the preprocessor module and the BSS module such as the preprocessor 16 and the unmixer 18 of the EP 1 017 253 A2 be constructed. See in particular paragraphs [0008] to [0024] of EP 1 017 253 A2 ,
  • the invention ties in with the EP 1 655 998 A2 to provide for a hearing aid wearer stereo voice signals or to enable a binaural acoustic care with speech.
  • the invention (notation according to the EP 1 655 998 A2 ) the output signals z1, z2 respectively for the right (k) and left (k) of a second filter device of EP 1 655 998 A2 (see Figs. 2 and 3) for accentuation / amplification of the corresponding acoustic source downstream.
  • it is possible to use the invention in the EP 1 655 998 A2 apply to the effect that it intervenes according to the teached there blind source separation and even before the second filter device. Ie. According to the invention, a selection of a signal y1 (k), y2 (k) takes place (see FIG. 3 of FIG EP 1 655 998 A2 ).

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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)
  • Soundproofing, Sound Blocking, And Sound Damping (AREA)
EP07117250.6A 2006-10-10 2007-09-26 Procédé pour le fonctionnement d'une prothèse auditive et prothèse auditive Not-in-force EP1912474B1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102006047982A DE102006047982A1 (de) 2006-10-10 2006-10-10 Verfahren zum Betreiben einer Hörfilfe, sowie Hörhilfe

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EP1912474A1 true EP1912474A1 (fr) 2008-04-16
EP1912474B1 EP1912474B1 (fr) 2015-11-11

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US (1) US8194900B2 (fr)
EP (1) EP1912474B1 (fr)
CN (1) CN101163354B (fr)
DE (1) DE102006047982A1 (fr)
DK (1) DK1912474T3 (fr)

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EP2445230A4 (fr) * 2009-06-17 2016-05-18 Panasonic Ip Corp America Appareil auditif
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EP1912474B1 (fr) 2015-11-11
US8194900B2 (en) 2012-06-05
CN101163354B (zh) 2013-01-02
CN101163354A (zh) 2008-04-16
DK1912474T3 (da) 2016-02-22
US20080107297A1 (en) 2008-05-08

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