EP2077059B1 - Procédé de fonctionnement d'une aide auditive et aide auditive - Google Patents

Procédé de fonctionnement d'une aide auditive et aide auditive Download PDF

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Publication number
EP2077059B1
EP2077059B1 EP07821025.9A EP07821025A EP2077059B1 EP 2077059 B1 EP2077059 B1 EP 2077059B1 EP 07821025 A EP07821025 A EP 07821025A EP 2077059 B1 EP2077059 B1 EP 2077059B1
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EP
European Patent Office
Prior art keywords
hearing aid
acoustic
source
signal processing
processing section
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German (de)
English (en)
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EP2077059A1 (fr
Inventor
Eghart Fischer
Matthias Fröhlich
Jens Hain
Henning Puder
André Steinbuß
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Sivantos GmbH
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Sivantos GmbH
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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
    • H04R25/40—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; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R3/00—Circuits for transducers
    • H04R3/005—Circuits for transducers for combining the signals of two or more microphones
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R2201/00—Details of transducers, loudspeakers or microphones covered by H04R1/00 but not provided for in any of its subgroups
    • H04R2201/40—Details of arrangements for obtaining desired directional characteristic by combining a number of identical transducers covered by H04R1/40 but not provided for in any of its subgroups
    • H04R2201/403—Linear arrays of transducers
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; ELECTRIC HEARING AIDS; 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

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 such as US2005 / 0265563A1 ).
  • 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 selection of the desired Nutzakustik provoke is inventively made such that the desired speaker or the desired acoustic source is always the one or the one whose distance from a microphone (system) of the hearing preferably the least of all distances of the detected speakers or acoustic sources is.
  • This also applies according to the invention to a plurality of speakers or acoustic sources, their distances from the microphone (system) being low in comparison with other speakers or acoustic sources.
  • a method for operating a hearing aid wherein for the tracking and selective amplification of an acoustic source, signal processing of the hearing aid for preferably all the electrical acoustic signals available to it determines a distance of the acoustic source to the hearing aid wearer and assigns it to the corresponding acoustic signal.
  • the acoustic source or the acoustic sources with small or the shortest distances with respect to the hearing aid wearer are tracked by the signal processing and particularly taken into account in an acoustic output signal of the hearing aid.
  • a hearing aid is provided according to the invention, wherein a distance of an acoustic source to the hearing aid wearer can be determined by an acoustic module (signal processing) of the hearing aid and then assigned to electrical acoustic signals.
  • the acoustic module selects at least one electrical acoustic signal, which represents a small spatial distance of the associated acoustic source to the hearing aid wearer. This electrical acoustic signal is particularly considered in an output sound of the hearing aid.
  • the electrical acoustic signals are analyzed by the hearing aid for features that - individually or in combination - can provide information about the distance of the acoustic source to the microphone (system) or the hearing aid wearer. This preferably takes place after application of a blind source separation algorithm.
  • 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 (speech) acoustic sources of ambient sound and to emphasize the output sound of the hearing aid. It is possible to adjust a volume of the acoustic source or the acoustic sources in the output sound of the hearing aid as desired.
  • 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 "near-source" operating mode in the hearing aid upon detection of a nearby acoustic source (near-acoustic-acoustic source). 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].
  • the hearing aid or the signal processing or the post-processor module leads a distance analysis of the electrical acoustic signals in that for each of the electrical acoustic signals simultaneously a distance of the corresponding acoustic source to the hearing aid is determined, and then by the signal processing or the post-processor module mainly the one or more electrical acoustic signals with a small source distance to a handset or the speaker Hearing aid are output, which converts the electrical acoustic signals into analog sound information.
  • Preferred acoustic sources are speech or speaker sources, whereby the selection of the speaker with the smallest horizontal distance to the ear of the hearing aid wearer - at least for many conversational situations - increases the probability that the "correct", ie. H. automatically select the voice or speaker source you want from the hearing aid user.
  • the electrical acoustic signals to be processed in the hearing aid are examined for information contained therein, which information can provide information about a distance of the acoustic source to the hearing aid wearer.
  • information can provide information about a distance of the acoustic source to the hearing aid wearer.
  • a distinction can be made between a horizontal distance and a vertical distance, wherein a too large vertical distance represents a non-preferred source.
  • the respective distance information obtained by a single electrical acoustic signal is processed individually or in a plurality or in their entirety in such a way that a spatial distance of the acoustic source represented thereby can be determined.
  • the corresponding electrical acoustic signal is examined as to whether it contains spoken speech.
  • it is a known speaker, ie a known hearing aid Speaker whose voice profile is stored within the hearing aid with corresponding parameters.
  • a BSS module which corresponds to a module for a blind source separation.
  • 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 acoustic signal by a hearing aid of a hearing aid wearer is mentioned. This is to be understood as meaning a selection of one or a plurality of electrical speech signals made by the hearing aid or a signal processing of the hearing aid or a post-processor module of the signal processing, which of the hearing aid is electrically or electronically be selected from other sources of acoustic ambient sound and which in a relation to the other acoustic sources of ambient sound amplified way, ie in a louder perceived for the hearing aid wearer, are reproduced.
  • a position of the hearing aid wearer in the room is preferably not taken into account by the hearing aid.
  • 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 are subject to a demixing process.
  • 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.
  • a post-processor module 330 According to specification of EP 1 017 253 A2 are steps 1 and 3, Thus, 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 demix module 320, hereinafter referred to as BSS module 320, is located, which is a post-processor module 330 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 is a speech source 102 arranged in relation to the hearing aid wearer, also referred to as a near acoustic source 102.
  • the other acoustic source 104 should also be a voice source 104 in this example, but further away from the hearing aid wearer than the voice source 102.
  • the voice source 102 should be selected and tracked by the hearing aid 1 or signal processor 300 and a primary acoustic component of the listener 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 deliver them either 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 in a single hearing aid 1 of the hearing aid 1 or distributed to both hearing aids 1 be. 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 carries out a distance analysis of the electrical acoustic signals 322, 324, wherein a spatial distance to the hearing aid 1 is determined for each of these electrical acoustic signals 322, 324. Subsequently, the post-processor module 330 selects the electrical acoustic signal 322 which has the smallest distance to the hearing aid 1 and outputs this electrical acoustic signal 322 in a manner amplified relative to the other electrical acoustic signal 324 as the output electrical acoustic signal 332 (substantially corresponds to the electrical acoustic signal 322) to the Speaker 400 off.
  • Fig. 3 shows the inventive method and the hearing aid 1 according to the invention in 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 respectively of three microphones, each of which outputs an electric 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) acoustic sources s 1 (t), s 2 (t), s n (t) separated and as electrical output signals s' 1 (t), s' 2 (t), s' n (t) to the post-processor module 330.
  • the two speech sources s 1 (t), s n (t) in the vicinity of the hearing aid wearer, so that the likelihood is high that the hearing aid wearer with these two speech sources s 1 (t), s n (t) in a Conversation situation is.
  • the voice range SR should correspond to a spherical shell around the head of the hearing aid wearer, within which usual call volumes prevail.
  • the corresponding volume level of a speech source s 2 (t) is too low to assume that this speech source s 2 (t) is in a conversation situation with the hearing aid wearer.
  • a front half of an equatorial layer of this sphere is preferred for a conversation situation, the equatorial layer being approximately 1.5 m high, preferably 0.8-1.2 m, particularly preferably 0.4-0.7 m, and particularly preferably of 0.2-0.4m possesses.
  • the equator in whose plane approximately the microphones of the hearing aid 1 are located, runs in the middle of the boundary of the equatorial layer.
  • the equator lies in an upper portion of the equatorial layer, so that an attention area of the hearing aid 1 is directed downwards rather than upwards.
  • This scenario is preferably suitable for a short-range area in which there is a maximum call range of 2m to 3m.
  • a cylinder whose longitudinal axis coincides with a longitudinal axis of the hearing aid wearer is suitable for defining the voice range SR.
  • An opening angle is 90 ° -120 °, preferably 60 ° -90 °, in particular 45 ° -60 ° and particularly preferably 30 ° -45 °. Such a scenario is preferably suitable for a more remote area.
  • the BSS module 320 In the electrical acoustic signals s' 1 (t), s' 2 (t), s' n (t) generated by the BSS module 320, which correspond to the speech or acoustic sources s 1 (t), s 2 (t), s n (t), distance information y 1 (t), y 2 (t), y n (t) are included, which can provide information about how far away the respective speech source s 1 (t), s 2 ( t), s n (t) of the hearing aid 1 and the hearing aid wearer is located.
  • the reading of this information in the form of a distance analysis takes place in the post-processor module 330, which includes a respective distance information y 1 (t), y 2 for each electrical speech signal s' 1 (t), s' 2 (t), s' n (t) (t), assigns y n (t) to the acoustic source s 1 (t), s 2 (t), s n (t) and then selects the one or more electrical acoustic signals s 1 (t), s n (t) which due to the distance information is probable that the hearing aid wearer is in a conversation situation with these speech sources s 1 (t), s n (t).
  • This is in the Fig. 3 with the speech source s 1 (t) facing the hearing aid wearer and the speech source s n (t) at approximately a 90 ° angle next to the hearing aid wearer Hearing aid carrier is located, both of which are within the language range SR.
  • the post-processor module 330 now outputs the two electrical acoustic signals s ' 1 (t), s' n (t) to the loudspeaker 400 in an amplified manner. Furthermore, it is conceivable that z. B. the acoustic source s 2 (t) is a source of noise and therefore ignored by the post-processor module 330, which can be determined by a corresponding module or a corresponding device in the post-processor module 330.
  • z. B a ratio of a direct sound component to a reverb content of the corresponding acoustic source 102, 104; s 1 (t), s 2 (t), s n (t) and the corresponding electrical signal 322, 324; s' 1 (t), s' 2 (t), s' n (t). Ie. in an individual case, the larger this ratio, the closer the acoustic source 102, 104; s 1 (t), s 2 (t), s n (t) on the hearing aid wearer.
  • a level criterion may indicate how far an acoustic source 102, 104; s 1 (t), s 2 (t), s n (t) is away from the hearing aid 1. Ie. the louder an acoustic source 102, 104; s 1 (t), s 2 (t), s n (t), the greater the likelihood that it is near the microphones 200, 210 of the hearing aid 1.
  • a "punctiformity" of the source also contains information about the distance. There are methods that allow conclusions about how “punctiform” (as opposed to “diffuse") the respective acoustic source 102, 104; s 1 (t), s 2 (t), s n (t). In general, the more punctiform an acoustic source is, the closer it is to the microphone (system) of the hearing aid 1.
  • conclusions about a distance of the respective acoustic source 102, 104 Determine s 1 (t), s 2 (t), s n (t) to the hearing aid 1. Ie. from the shape of the time signal, z. As a slope of edges of an envelope, conclusions about the distance of the corresponding acoustic source 102, 104; s 1 (t), s 2 (t), s n (t) are drawn.
  • s 1 (t), s 2 (t), s n (t) determine what z. B. can take place by triangulation.
  • the distance analysis in the post-processor module 330 can always run in the background of the hearing aid 1 and, upon the occurrence of a suitable electrical speech signal 322; s ' 1 (t), s' n (t) are initiated. It is also possible to call the distance analysis according to the invention by the hearing aid wearer. Ie. Establishing the operating mode "near source" of the hearing aid 1 is initiated by an input device that can be called or actuated by the hearing aid wearer. Here, the input device, an operating element on the hearing aid 1 and or a control on a remote control of the hearing aid 1, z. As a button or switch, be (not shown in the figures).
  • the input device as a voice control with an associated speaker recognition module, which is tuned to a voice of the hearing aid wearer, wherein the input device is at least partially formed in the hearing aid 1 and / or at least partially in a remote control of the hearing aid 1.
  • the hearing aid 1 which of the electrical voice 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) to the hearing aid 1, whereby certain angles of incidence are preferred, eg, the 0 ° to ⁇ 10 ° viewing direction (interlocutor sitting directly opposite) and / or a ⁇ 70 ° to ⁇ 100 ° Side direction (right / left interlocutor) and / or a ⁇ 20 ° to ⁇ 45 ° direction of view (interlocutor sitting diagonally opposite) of the hearing aid wearer may be preferred
  • the electrical voice signals 322; s ' 1 (t), s' n (t) to determine whether one
  • this other module of the hearing aid 1 is to be included in 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 distance analysis one or more speakers / acoustic sources 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 ) prefers the output signals z1, z2 respectively for the right (k) and left (k) of a second filter device of EP 1 655 998 A2 (please refer Fig. 2 and 3 ) for accentuation / amplification of the corresponding acoustic source downstream.
  • 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 the EP 1 655 998 A2 ).

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
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Claims (24)

  1. Procédé destiné à faire fonctionner une aide auditive (1), pour poursuivre et sélectionner une première source acoustique (102 ; s1(t), sn(t)) d'un son ambiant (100 ; 102, 104 ; s1(t), s2(t), ..., sn(t)) par un traitement de signaux (300) de l'aide auditive (1), un mode de fonctionnement « source proche » étant établi,
    par l'aide auditive (1), des signaux acoustiques électriques (202, 212 ; 312, 314 ; x1(t),x2(t), ..., xn(t)) étant créés à partir du son ambiant (100 ; 102, 104 ; s1(t), s2(t), ..., sn(t)),
    les signaux acoustiques électriques (202, 212 ; 312, 314 ; x1(t),x2(t), ..., xn(t)) étant dissociés en signaux de sortie électriques (322, 324; s'1(t), s'2(t), ..., s'n(t)),
    à partir des signaux de sortie électriques (322, 324 ; s'1(t), s'2(t), ..., s'n(t)) étant déterminée la première source acoustique (102 ; s1(t), sn(t)), laquelle
    par le traitement de signaux (300) est considérée sélectivement dans un son de sortie (402 ; s"(t) ; s"1(t)+s"n(t)) de l'aide auditive (1), de telle sorte que pour un porteur de l'aide auditive, la première source acoustique (102 ; s1(t), sn(t)) ressorte au moins acoustiquement, en comparaison d'une autre source acoustique (104 ; s2(t)) et soit mieux perçue de ce fait, pour un porteur de l'aide auditive, l'autre source acoustique (104 ; s2(t)) étant plus éloignée dans l'espace par rapport au porteur de l'aide auditive que la première source acoustique (102 ; s1(t), sn(t)), à cet effet, le traitement de signaux (300) comportant un module de dissociation (320) pour séparer les signaux acoustiques électriques (312, 314 ; x1(t),x2(t), ..., xn(t)) et un module post-processeur (330) par lequel le mode de fonctionnement « source proche » de l'aide auditive (1) est établi et par le traitement de signaux (300) étant réalisée une analyse de distance des signaux de sortie électriques (322, 324 ; s'1(t),s'2(t), ..., s'n(t) et pour les sources acoustiques (102, 104 ; s1(t), s2(t), ..., sn(t) chaque fois un écart (y1(t), y2(t), ..., yn(t)) par rapport au porteur de l'aide auditive étant déterminé.
  2. Procédé selon la revendication 1, la première source acoustique (102 ; s1(t), sn(t)) étant sélectionnée de telle sorte que par rapport au porteur de l'aide auditif, elle se trouve dans une portée de son vocaux (SR) d'un locuteur dans laquelle le langage parlé peut être compris.
  3. Procédé selon l'une quelconque des revendications précédentes, le traitement de signaux (300) de l'aide auditive (1) étant aménagé de sorte qu'une pluralité de sources acoustiques (102 ; s1(t), sn(t)) indépendantes les unes des autres soient poursuivies séparément les unes des autres.
  4. Procédé selon l'une quelconque des revendications précédentes, par le traitement de signaux (300) étant déterminée(s) la ou les sources acoustiques (102, 104 ; s1(t), s2(t), ..., sn(t)) dont les écarts (y1(t), y2(t), ..., yn(t)) par rapport au porteur de l'aide auditive sont les plus faibles et qui sont mises à disposition du porteur de l'aide auditive par le son de sortie (402 ; s"(t) ; s"1(t)+s"n(t)) de l'aide auditive (1).
  5. Procédé selon l'une quelconque des revendications précédentes, la première source acoustique (102 ; s1(t), sn(t)) ou le signal de sortie électrique (322 ; s'1(t), s'n(t)) étant identifié(e) ou sélectionné(e) par ailleurs sur la base
    • de son rapport d'un son direct à un niveau de réverbération ;
    • d'un critère de niveau ;
    • d'un effet d'ombre acoustique de la tête ;
    • d'une forme ponctuelle de la source concernée ;
    • d'une caractéristique dans le temps, notamment d'une forme d'un signal temporel ;
    • d'une mesure de l'éloignement basée sur un traitement multi-microphones ;
    • d'une absence d'interférence ;
    • d'un écart vertical par rapport à l'aide auditive (1) ou au porteur de l'aide auditive ; et/ou
    • du langage parlé qu'il contient.
  6. Procédé selon l'une quelconque des revendications précédentes, des sources acoustiques (104 ; s2(t)) qui ne contiennent aucune parole ou des sources acoustiques (104 ; s2(t)) qui sont trop fortement perturbées par des signaux parasites n'étant de préférence pas considérées par le traitement de signaux (300).
  7. Procédé selon l'une quelconque des revendications précédentes, le module de dissociation (320) étant conçu sous la forme d'un module de dissociation à source aveugle (320).
  8. Procédé selon l'une quelconque des revendications précédentes, par ailleurs dans le module post-processeur (330), une intensité sonore des signaux de sortie électriques (322, 324 ; s'1(t),s'2(t),) ..., s'n(t) étant réglée en accord avec un signal de sortie acoustique électrique (332) du traitement de signaux (300).
  9. Procédé selon l'une quelconque des revendications précédentes, le traitement de signaux (300) comportant un module préprocesseur (310), lequel prépare les signaux acoustiques électriques (202, 212 ; x1(t), x2(t), ..., xn(t) pour le module de dissociation (320).
  10. Procédé selon l'une quelconque des revendications précédentes, lors de l'établissement du mode de fonctionnement « source proche », la première source acoustique (102 ; S1(t), sn(t)) parvenant à partir d'une certaine direction par rapport au porteur de l'aide auditive, de préférence à partir d'une direction visuelle de 0° ou d'une direction latérale de 90° et étant poursuivie ensuite par le traitement de signaux (300).
  11. Procédé selon l'une quelconque des revendications précédentes, dans lequel dans le mode de fonctionnement « source proche » en tant que première source acoustique (102 ; S1(t), sn(t)), une première source acoustique (102 ; S1(t), sn(t)) prédominant dans le son ambiant (100 ; 102, 104 ; S1(t), s2(t), ..., sn(t)) est poursuivie.
  12. Procédé selon l'une quelconque des revendications précédentes, le mode de fonctionnement « source proche » étant aménagé de telle sorte que dans le son de sortie (402 ; s"(t) ; s"1(t)+s"n(t)) de l'aide auditive (1), le porteur de l'aide auditive ne perçoive sensiblement plus que la (les) première(s) source(s) acoustique (s) (102 ; S1(t), sn(t)) du son ambiant (100 ; 102, 104 ; S1(t), s2(t), ..., sn(t)).
  13. Aide auditive destinée à poursuivre et à sélectionner une première source acoustique (102 ; S1(t), sn(t)) d'un son ambiant (100 ; 102, 104 ; S1(t), s2(t), ..., sn(t)),
    l'aide auditive (1) créant à partir du son ambiant (100 ; 102, 104 ; S1(t), s2(t), ..., sn(t)) des signaux acoustiques électriques (202, 212 ; 312, 314 ; x1(t),x2(t), ..., xn(t)) et comportant un traitement de signaux (300) pour établir un mode de fonctionnement « source proche »,
    le traitement de signaux (300) comportant un module de dissociation (320) pour séparer les signaux acoustiques électriques (202, 212 ; 312, 314 ; x1(t),x2(t), ..., xn(t)) en des signaux de sortie électriques (322, 324 ; s'1(t), s'2(t), ..., s'n(t)),
    à partir des signaux de sortie électriques (322, 324 ; s"1(t), s'2(t), ..., s'n(t)) étant déterminée la première source acoustique (102 ; S1(t), sn(t)),
    au moyen du traitement de signaux (33) étant réalisée une analyse de distance de signaux de sortie électriques (322, 324 ; s'1(t), s'2(t), ..., s'n(t)), pour les sources acoustiques (102, 104 ; S1(t), s2(t), ..., sn(t)), un écart (y1(t), y2(t), ..., yn(t)) par rapport au porteur de l'aide auditive étant déterminé ,
    et un module post-processeur (330) du traitement de signaux (300) identifiant et sélectionnant la première source acoustique (102 ; S1(t), sn(t)), laquelle affiche un plus faible écart par rapport à un porteur de l'aide auditive, en comparaison d'une autre source acoustique (104 ; s2(t)),
    la première source acoustique (102 ; S1(t), sn(t)) pouvant être considérée de manière sélective dans un son de sortie (402 ; s"(t) ; s"1(t)+s"n(t)) de l'aide auditive (1), de sorte à ressortir au moins pour le porteur de l'aide auditive, en comparaison d'une autre source acoustique (104 ; s2(t)) et être de ce fait mieux perceptible acoustiquement.
  14. Aide auditive selon la revendication 13, le traitement de signaux (300) de l'aide auditive (1) étant aménagé de telle sorte qu'une pluralité de sources acoustiques (102 ; S1(t), sn(t)) indépendantes les unes des autres puissent être poursuivies séparément les unes des autres.
  15. Aide auditive selon l'une quelconque des revendications 13 ou 14, au moyen du traitement de signaux (300), la ou les sources acoustiques (102, 104 ; S1(t), s2(t), ..., sn(t) pouvant être déterminée(s) dont les écarts (y1(t), y2(t), ..., yn(t)) par rapport au porteur de l'aide auditive sont les plus faibles et qui peuvent être mises à la disposition du porteur de l'aide auditive par le son de sortie (402 ; s"(t) ; s"1(t)+s"n(t)) de l'aide auditive (1).
  16. Aide auditive selon l'une quelconque des revendications 13 à 15, la première source acoustique (102 ; S1(t), sn(t)) ou le signal de sortie électrique (322 ; s'1(t), s'n(t)) pouvant être identifié(e) et sélectionné(e) par ailleurs sur la base
    • de son rapport d'un son direct à un niveau de réverbération ;
    • d'un critère de niveau ;
    • d'un effet d'ombre acoustique de la tête ;
    • d'une forme ponctuelle de la source concernée ;
    • d'une caractéristique dans le temps, notamment d'une forme d'un signal temporel ;
    • d'une mesure de l'éloignement basée sur un traitement multi-microphones ;
    • d'une absence d'interférence ;
    • d'un écart vertical par rapport à l'aide auditive (1) ou au porteur de l'aide auditive ; et/ou
    • du langage parlé qu'il contient.
  17. Aide auditive selon l'une quelconque des revendications 13 à 16,
    des signaux de sortie électriques (324 ; s'2(t)) qui ne contiennent aucune parole ou des signaux de sortie électriques (324 ; s'2(t)) qui sont trop fortement perturbés par des signaux parasites n'étant de préférence pas considérés par le traitement de signaux (300).
  18. Aide auditive selon l'une quelconque des revendications 13 à 17,
    le module post-processeur (330) poursuivant et sélectionnant le ou les signaux de sortie électriques (322 ; s'1(t), s'n(t)) et générant un signal de sortie (332) électrique correspondant pour un haut-parleur (400) de l'aide auditive (1) qui délivre le son de sortie (402 ; s"(t) ; s"1(t)+s"n(t)) de l'aide auditive (1).
  19. Aide auditive selon l'une quelconque des revendications 13 à 18, deux appareils auditifs (1) de l'aide auditive (1) ou une aide auditive (1) individuelle comportant une pluralité de microphones (200, 210) au moyen desquels le son ambiant (100 ; 102, 104 ; S1(t), s2(t), ..., sn(t)) peut être enregistré qui contient la première source acoustique (102 ; S1(t), sn(t)) et au moyen des microphones (200, 210), chaque fois un signal acoustique électrique (202, 212 ; x1(t), x2(t), ..., xn(t)) pouvant être délivré à l'attention du traitement de signaux (300).
  20. Aide auditive selon l'une quelconque des revendications 13 à 19,
    le mode de fonctionnement « source proche » pouvant être établi par le module post-processeur (330) de l'aide auditive (1).
  21. Aide auditive selon l'une quelconque des revendications 13 à 20,
    le module de dissociation (320) étant conçu sous la forme d'un module de dissociation à source aveugle (320).
  22. Aide auditive selon l'une quelconque des revendications 13 à 21,
    par ailleurs dans le module post-processeur (330), une intensité de son des signaux de sortie électriques (322, 324 ; s'1(t), s'2(t),) ..., sn(t)) pouvant être réglée en accord avec le signal de sortie acoustique électrique (332) du traitement de signaux (300).
  23. Aide auditive selon l'une quelconque des revendications 13 à 22,
    le traitement de signaux (300) comportant un module préprocesseur (310), au moyen duquel les signaux acoustiques électriques (202, 212 ; x1(t), x2(t), ..., xn(t)) pour le module de dissociation (320) peuvent être préparés.
  24. Aide auditive selon l'une quelconque des revendications 13 à 23, l'aide auditive (1) comprenant un seul ou deux appareils auditifs (1).
EP07821025.9A 2006-10-10 2007-10-08 Procédé de fonctionnement d'une aide auditive et aide auditive Active EP2077059B1 (fr)

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PCT/EP2007/060652 WO2008043731A1 (fr) 2006-10-10 2007-10-08 Procédé de fonctionnement d'une aide auditive et aide auditive

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EP (1) EP2077059B1 (fr)
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WO (1) WO2008043731A1 (fr)

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US9031256B2 (en) 2010-10-25 2015-05-12 Qualcomm Incorporated Systems, methods, apparatus, and computer-readable media for orientation-sensitive recording control
JP2012205147A (ja) * 2011-03-25 2012-10-22 Kyocera Corp 携帯電子機器および音声制御システム
US10791404B1 (en) * 2018-08-13 2020-09-29 Michael B. Lasky Assisted hearing aid with synthetic substitution
CN114900771B (zh) * 2022-07-15 2022-09-23 深圳市沃特沃德信息有限公司 基于辅音耳机的音量调节优化方法、装置、设备及介质
US12424204B1 (en) 2022-08-23 2025-09-23 Gn Hearing A/S Speech recognition hearing device with multiple supportive detection inputs

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US8331591B2 (en) 2012-12-11
JP5295115B2 (ja) 2013-09-18
AU2007306432A1 (en) 2008-04-17
JP2010506525A (ja) 2010-02-25
DK2077059T3 (da) 2017-11-27
EP2077059A1 (fr) 2009-07-08
WO2008043731A1 (fr) 2008-04-17
US20100034406A1 (en) 2010-02-11
AU2007306432B2 (en) 2012-03-29

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