EP2811762B1 - Système binaural de formation de faisceau fondé sur la logique - Google Patents

Système binaural de formation de faisceau fondé sur la logique Download PDF

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Publication number
EP2811762B1
EP2811762B1 EP14166949.9A EP14166949A EP2811762B1 EP 2811762 B1 EP2811762 B1 EP 2811762B1 EP 14166949 A EP14166949 A EP 14166949A EP 2811762 B1 EP2811762 B1 EP 2811762B1
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EP
European Patent Office
Prior art keywords
hearing aid
signal
aid system
linear combinations
linear combination
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EP14166949.9A
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German (de)
English (en)
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EP2811762A1 (fr
Inventor
Eghart Fischer
Homayoun Dr. Kamkar Parsi
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Sivantos Pte Ltd
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Sivantos Pte Ltd
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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
    • H04R25/55—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
    • H04R25/405—Arrangements for obtaining a desired directivity characteristic by combining 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
    • H04R25/40—Arrangements for obtaining a desired directivity characteristic
    • H04R25/407—Circuits for combining signals of a plurality of transducers
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10L—SPEECH ANALYSIS TECHNIQUES OR SPEECH SYNTHESIS; SPEECH RECOGNITION; SPEECH OR VOICE PROCESSING TECHNIQUES; SPEECH OR AUDIO CODING OR DECODING
    • G10L21/00—Speech or voice signal processing techniques to produce another audible or non-audible signal, e.g. visual or tactile, in order to modify its quality or its intelligibility
    • G10L21/02—Speech enhancement, e.g. noise reduction or echo cancellation
    • G10L21/0208—Noise filtering
    • G10L21/0216—Noise filtering characterised by the method used for estimating noise
    • G10L2021/02161—Number of inputs available containing the signal or the noise to be suppressed
    • G10L2021/02166—Microphone arrays; Beamforming

Definitions

  • the present invention relates to a hearing aid system, wherein the hearing aid system has a left and a right hearing aid.
  • the left hearing aid has a left akusto-electrical converter and the right hearing aid on a right akusto-electrical converter.
  • the transducers are designed to convert incoming acoustic signals into left and right electrical signals.
  • the hearing aid system has a signal processing device, wherein the signal processing device is in signal connection with the left and the right 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 also used to hide noise.
  • Wiener filters are used to hide uncorrelated noise.
  • a formation of a static directional characteristic by means of a static beam shaping (beam: beam, Richtkeule) of binaural signals is not able to independently respond to changing acoustic environments, so that the wearer of the hearing aid itself must respond by adjusting the device.
  • beam beam, Richtkeule
  • adaptive filters are based on certain conditions for the useful and interfering signals, so that in certain listening situations that do not meet these requirements, the intelligibility for the wearer can even be worsened by the adaptive filters and he must again manually correct them.
  • this object is achieved by a method for operating a hearing aid system according to claim 1 and a hearing aid system according to claim 6.
  • the method according to the invention relates to a method for beam shaping for hearing aid systems.
  • the hearing aid system includes a left and a right hearing aid for placement on a head of a wearer. Usually, the hearing aids are worn on or in the left or right ear.
  • the left hearing aid has a left acousto-electric transducer, which converts sound waves arriving at the left hearing aid into a left input signal.
  • the right hearing aid has a right acousto-electric transducer, which converts sound waves arriving at the right hearing aid into a right input signal.
  • the hearing aid system has a signal processing device which is in signal communication with the left and the right acousto-electric converter stands and receives the left and the right input signal.
  • a linear combination is selected as a beam signal depending on the rating.
  • the linear combinations are easy to calculate and therefore require little processor power. Furthermore, the linear combinations are undistorted signals without artificial frequency components and provide a natural listening experience available. By evaluating the linear combinations and selecting one as the beam signal, the type of evaluation can be used to predict the output of the beam shaping in a deterministic manner and no undesirable effects are to be expected.
  • the device of claim 6 for carrying out the method according to the invention shares its advantages.
  • the input signals are weighted with weighting factors, wherein the sum of the weighting factors of a linear combination is equal to 1 in each case.
  • the left and the right input signal are equally strong in the heads worn hearing aids Therefore, in an advantageous manner for all linear combinations for the source in front of the carrier an equally strong sum signal.
  • the evaluation of the linear combinations is done by determining a signal level of the linear combinations.
  • Selecting a linear combination is done by selecting the linear combination with the lowest signal level.
  • the signal with the lowest energy content is selected.
  • the advantageous effect is that in this way the signal with the lowest level of noise from directions unequal in direction is chosen in front of the carrier.
  • an estimated value for the spectral power density of a useful signal and a noise signal is determined from the left and the right input signal, and depending on this, the beam signal is amplified or attenuated.
  • the steps of the method are carried out separately for a plurality of frequency ranges.
  • the selection of a linear combination is effected by switching or blending the beam signal between two linear combinations.
  • this is done automatically for the user switching to the signal with the least amount of noise.
  • the transition for the wearer is barely noticeable.
  • 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.
  • the microphones 2, 2 ' are acousto-electrical converters 2, 2' for converting the sound into first audio signals.
  • 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 left input signal from the signal processing device 3 to the signal processing device 3 '. Conversely, it is provided that also the signal processing device 3 'transmits a right input 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 so for example inductively, via Bluetooth, optical or other wireless transmission technology.
  • the signal processing device 3, 3 ' is designed to form a plurality of linear combinations from the left and the right input signal, to evaluate the linear combinations and to select one of the linear combinations as a beam signal on the basis of the evaluation. For details, see the description of the process steps Fig. 2 see below.
  • the hearing aid system 100 also includes means 7, 7 'for adjusting the gain of the beam signal.
  • the signal processing means 3, 3 'and the means 7, 7' for adjusting the gain of the beam signal can, as in Fig. 1 represented, an integral part of the signal processing means 3, 3 'be.
  • 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 3, 3 ' 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 Forwarding the issue.
  • the device 7, 7 'for Adjusting the gain of the beam signal which is provided either in each of the hearing aids 110, 110 'or even in one, together 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 includes a step S10 of providing a plurality of different linear combinations of the left input signal and the right input signal.
  • This step includes inter alia converting an acoustic signal at the microphones 2, 2 'into a left input signal LS and a right input signal RS, as well as its transmission to the signal processing device 3, 3'.
  • the signal processing device 3, 3 ' provides a plurality of linear combinations LKi from the input signals LS and RS.
  • each of the hearing aids two microphones 2, 2 'have, so that a linear combination of 4 signals is formed.
  • the boundary condition remains that the sum of the coefficients, in this case four coefficients, is equal to 1 in each case. Also conceivable are three or more input signals and coefficients per page.
  • a step S20 the linear combinations are evaluated from the step S10. This is preferably also done by the signal processing device 3, 3 '.
  • One possible evaluation of the linear combination is a determination of an instantaneous signal level by means of a fast level meter. This can be done, for example, by a short-term average of the amount of the linear combination, wherein the short-term averaging could each comprise a few periods of the signal. However, it is also conceivable to use in each case the maximum of the magnitude of the amplitude of the signal in a signal period for determining the level.
  • one of the linear combinations is selected on the basis of the evaluation as a beam signal.
  • the linear combination is selected in which the signal level determined as the evaluation criterion is the lowest.
  • the energy density of the signal is correlated with the square of the signal level.
  • the linear combination with the lowest signal level and the corresponding lowest energy density is also the linear combination, which has the least amount of noise.
  • FIG. 3 illustrates a flowchart of a further method according to the invention. The method is identical in steps S10 to S30 with that in FIG Fig. 2 illustrated method.
  • the procedure of Fig. 3 also has a step S40.
  • step S40 an estimation of the spectral energy density of the useful signal is carried out.
  • step S50 an estimation of the spectral energy density of the noise is performed in the same manner.
  • the amplification of the beam signal is set as a function of the estimated energy densities of the useful and the interference signals. If it is estimated that the energy density of the useful signal is low, ie no useful signal arrives from a source in the plane of symmetry, then the amplification of the beam signal is reduced and thus also the interference signals. Conversely, if it is estimated that the energy density of the useful signal is large and thus a useful signal is present, the gain of the beam signal can be increased.
  • the selection of the linear combination is performed in step S60 by switching or blending the beam signal between the previously selected one Linear combination and the linear combination selected from the switching time.
  • the signal connection between the beam signal output and the linear combination is changed from the previous linear combination to newly selected.
  • this is done, for example, by the signal processing device 3, 3 'passing on the result of the selected linear combination to the beam signal output starting at this point in time.
  • the sum of the previous and the selected linear combination can be passed on to the cross-fading, the previous linear combination being weighted with a factor falling to zero over time and the selected linear combination being weighted with a factor increasing to one.
  • Steps S10 to S30 or S10 to S60 are therefore also carried out separately for individual frequency ranges or frequency bands of the input signals in a possible embodiment, so that the beam signal with the lowest noise component can be selected in each frequency range.
  • Fig. 4 shows the course of the Fig. 2 shown in function blocks.
  • the linear combinations LK1, LK2 and LK 3 are evaluated in accordance with step S20.
  • the comparator 24 decides on the basis of the criterion of the minimum level which is to be selected and passes this information on to the switch 25. This selects in step S30 from the linear combinations LK1, LK2, LK3 that which is to be passed as a beam signal.
  • Fig. 5 the sequence of steps S40 to S60 is shown in function blocks.
  • the estimation block 35 executes an estimate of the spectral energy density of the desired signal in accordance with step S40 with the prefiltered signals.
  • estimation block 36 an estimation of the spectral energy density of the interfering signal is carried out in the same way as in step S50.
  • the gain for the prefiltered beam signal BS is adjusted according to step S60.

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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)

Claims (10)

  1. Procédé de formation de faisceau pour système d'aide auditive (100), dans lequel le système d'aide auditive (100) comprend un appareil d'aide auditive gauche (110) et un appareil d'aide auditive droit (110') qui sont disposés à des fins d'utilisation sur la tête d'un utilisateur, dans lequel l'appareil d'aide auditive gauche (110) comprend un convertisseur acousto-électrique gauche (2) qui convertit des ondes acoustiques incidentes sur l'appareil appareil d'aide auditive gauche (110) en un signal d'entrée gauche et l'appareil d'aide auditive droit (110') comprend un convertisseur acousto-électrique droit (2') qui convertit des ondes acoustiques incidentes sur l'appareil appareil d'aide auditive droit (110') en un signal d'entrée droit,
    dans lequel le système d'aide auditive gauche (110) comprend un dispositif de traitement de signaux (3, 3') qui est en communication de signal avec les convertisseurs acousto-électriques gauche et droit (2, 2') et qui reçoit les signaux d'entrée gauche et droit, dans lequel le procédé comprend les étapes consistant à, et le dispositif de traitement de signaux (3, 3') est conçu pour :
    fournir une pluralité de combinaisons linéaires différentes du signal d'entrée gauche et du signal d'entrée droit ;
    évaluer les combinaisons linéaires conformément à un critère de signal prédéterminé, dans lequel l'évaluation des combinaisons linéaires comprend la détermination d'un niveau de signal des combinaisons linéaires ;
    sélectionner une combinaison linéaire en fonction de l'évaluation en tant que signal de faisceau, dans lequel la sélection d'une combinaison linéaire est effectuée par sélection de la combinaison linéaire ayant le niveau de signal le plus faible.
  2. Procédé selon la revendication 1, dans lequel, lors de la fourniture des combinaisons linéaires, les signaux d'entrée sont pondérés par des facteurs de pondération et la somme des facteurs de pondération d'une combinaison linéaire est respectivement égale à 1.
  3. Procédé selon l'une quelconque des revendications précédentes, dans lequel une estimation de la densité de puissance spectrale d'un signal utile et d'un signal de bruit de perturbation est déterminée à partir des signaux d'entrée gauche et droit et est amplifiée ou atténuée en fonction du signal de faisceau.
  4. Procédé selon l'une quelconque des revendications précédentes, dans lequel les étapes du procédé sont respectivement exécutées séparément pour une pluralité de domaines de fréquences.
  5. Procédé selon l'une quelconque des revendications précédentes, dans lequel la sélection d'une combinaison linéaire consiste à permuter ou à effectuer une transition du signal de faisceau entre deux combinaisons linéaires.
  6. Système d'aide auditive, dans lequel le système d'aide auditive (100) comprend un appareil d'aide auditive gauche (110) et un appareil d'aide auditive droit (110') destinés à être disposés à des fins d'utilisation sur la tête d'un utilisateur,
    dans lequel l'appareil d'aide auditive gauche (110) comprend un convertisseur acousto-électrique gauche (2) qui convertit des ondes acoustiques incidentes sur l'appareil appareil d'aide auditive gauche (110) en un signal d'entrée gauche et l'appareil d'aide auditive droit (110') comprend un convertisseur acousto-électrique droit (2) qui convertit des ondes acoustiques incidentes sur l'appareil d'aide auditive droit (110') en un signal d'entrée droit,
    dans lequel le système d'aide auditive (100) comprend un dispositif de traitement de signaux (3, 3') qui est en communication de signal avec les convertisseurs acousto-électriques gauche et droit (2, 2') et qui reçoit les signaux d'entrée gauche et droit, caractérisé en ce que le dispositif de traitement de signaux (3, 3') est conçu pour :
    - fournir une pluralité de combinaisons linéaires différentes du signal d'entrée gauche et du signal d'entrée droit et pour évaluer les combinaisons linéaires conformément à un critère de signal prédéterminé,
    - sélectionner une combinaison linéaire en fonction de l'évaluation en tant que signal de faisceau,
    - déterminer un niveau de signal des combinaisons linéaires, et
    - sélectionner une combinaison linéaire ayant le niveau de signal le plus faible.
  7. Système d'aide auditive selon la revendication 6, dans lequel le système d'aide auditive (100) est conçu pour pondérer les signaux d'entrée des combinaisons linéaires avec des facteurs de pondération, dans lequel la somme des facteurs de pondération d'une combinaison linéaire est respectivement égale à 1.
  8. Système d'aide auditive selon l'une quelconque des revendications précédentes, dans lequel le système d'aide auditive (100) est conçu pour déterminer à partir des signaux d'entrée gauche et droit une estimation de la densité de puissance spectrale d'un signal utile et d'un signal de bruit de perturbation et pour les amplifier ou les atténuer en fonction du signal de faisceau.
  9. Système d'aide auditive selon l'une quelconque des revendications précédentes, dans lequel le système d'aide auditive (100) est conçu pour exécuter respectivement les étapes du procédé pour une pluralité de domaines de fréquences.
  10. Système d'aide auditive selon l'une quelconque des revendications précédentes, dans lequel le système d'aide auditive (100) est conçu pour effectuer la sélection d'une combinaison linéaire par permutation ou transition du signal de faisceau entre deux combinaisons linéaires.
EP14166949.9A 2013-05-16 2014-05-05 Système binaural de formation de faisceau fondé sur la logique Active EP2811762B1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102013209062.5A DE102013209062A1 (de) 2013-05-16 2013-05-16 Logik-basiertes binaurales Beam-Formungssystem

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EP2811762A1 EP2811762A1 (fr) 2014-12-10
EP2811762B1 true EP2811762B1 (fr) 2016-03-09

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US (1) US9473860B2 (fr)
EP (1) EP2811762B1 (fr)
DE (1) DE102013209062A1 (fr)
DK (1) DK2811762T3 (fr)

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US9510222B2 (en) * 2013-08-23 2016-11-29 Qualcomm Incorporated Detection of bursty WiFi interference in LTE/LTE-A communications in an unlicensed spectrum
JP6464280B2 (ja) 2015-03-13 2019-02-06 シバントス ピーティーイー リミテッド 両耳補聴器システム
US10182299B1 (en) * 2017-12-05 2019-01-15 Gn Hearing A/S Hearing device and method with flexible control of beamforming
EP3606100B1 (fr) 2018-07-31 2021-02-17 Starkey Laboratories, Inc. Commande automatique de fonctions binaurales dans des dispositifs portables à l'oreille
US11049509B2 (en) * 2019-03-06 2021-06-29 Plantronics, Inc. Voice signal enhancement for head-worn audio devices
DE102021210098A1 (de) * 2021-09-13 2023-03-16 Sivantos Pte. Ltd. Verfahren zum Betrieb eines Hörgeräts

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WO2001097558A2 (fr) 2000-06-13 2001-12-20 Gn Resound Corporation Directionnalite adaptative basee sur un modele polaire fixe
EP1326478B1 (fr) * 2003-03-07 2014-11-05 Phonak Ag Procédé de génération des signaux de commande et système d'appareil auditif binaural
US7330556B2 (en) 2003-04-03 2008-02-12 Gn Resound A/S Binaural signal enhancement system
CA2621940C (fr) * 2005-09-09 2014-07-29 Mcmaster University Procede et dispositif d'amelioration d'un signal binaural
DE102007033877B3 (de) 2007-07-20 2009-02-05 Siemens Audiologische Technik Gmbh Verfahren zur Signalverarbeitung in einer Hörhilfe
EP2394270A1 (fr) 2009-02-03 2011-12-14 University Of Ottawa Procédé et système de réduction de bruit à multiples microphones
DK2262285T3 (en) * 2009-06-02 2017-02-27 Oticon As Listening device providing improved location ready signals, its use and method

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EP2811762A1 (fr) 2014-12-10
DK2811762T3 (da) 2016-06-13
US20140341407A1 (en) 2014-11-20
US9473860B2 (en) 2016-10-18
DE102013209062A1 (de) 2014-11-20

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