EP2506603B1 - Système d'aide auditive avec système de microphone directif et procédé de fonctionnement dudit système d'aide auditive avec système de microphone directif - Google Patents

Système d'aide auditive avec système de microphone directif et procédé de fonctionnement dudit système d'aide auditive avec système de microphone directif Download PDF

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Publication number
EP2506603B1
EP2506603B1 EP12160523.2A EP12160523A EP2506603B1 EP 2506603 B1 EP2506603 B1 EP 2506603B1 EP 12160523 A EP12160523 A EP 12160523A EP 2506603 B1 EP2506603 B1 EP 2506603B1
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EP
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Prior art keywords
eff
time delay
hearing aid
microphone
res
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German (de)
English (en)
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EP2506603A2 (fr
EP2506603A3 (fr
Inventor
Dirk Junius
Jens Hain
Matthias Müller-Wehlau
Sebastian BEST
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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
    • H04R25/40—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
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R29/00—Monitoring arrangements; Testing arrangements
    • H04R29/004—Monitoring arrangements; Testing arrangements for microphones
    • H04R29/005—Microphone arrays
    • H04R29/006—Microphone matching
    • 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
    • H04R2225/39—Aspects relating to automatic logging of sound environment parameters and the performance of the hearing aid during use, e.g. histogram logging, or of user selected programs or settings in the hearing aid, e.g. usage logging
    • 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
    • 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

Definitions

  • the invention relates to a hearing aid device system comprising two hearing aid devices, each with a directional microphone system according to the preamble of claim 1. Furthermore, the invention relates to a method for operating such a hearing aid system according to the preamble of claim 8.
  • a hearing aid device is understood to mean any device which provides or helps to provide an output signal perceptible by a user as an audible signal, and which has means which help or compensate for an individual hearing loss of the user.
  • these are hearing aids which can be worn on the body or on the head, in particular on or in the ear, and which can be implanted in whole or in part.
  • such devices are also included, whose primary purpose is not to compensate for hearing loss, such as consumer electronics (TVs, hi-fi systems, MP3 players, etc.), or communication devices (mobile phones, PDAs, headsets etc), but over Have means to compensate for an individual hearing loss.
  • a hearing aid system consisting of two hearing aid devices that can be worn on or in the ear, in particular hearing aids, is generally used.
  • a hearing aid device system can also comprise at least one further device, for example an external processor unit that can be worn on the user's body.
  • the external processor unit can serve, for example, for the remote control of the hearing aid device or hearing aid device system, but also other functions, such as an analysis of the acoustic listening environment.
  • a hearing aid generally includes an input transducer for receiving an input signal.
  • the input transducer is designed for example as a microphone, which receives an acoustic signal and converts it into an electrical signal.
  • a hearing aid usually includes a signal processing unit for processing and frequency-dependent amplification of the electrical signal.
  • a preferably digital signal processor (DSP) is used, whose operation can be influenced by means of programs or parameters which can be transmitted to the hearing aid.
  • the mode of operation of the signal processing unit can be adapted both to the individual hearing loss of a hearing aid wearer and to the current hearing situation in which the hearing aid is currently being operated.
  • the thus changed electrical signal is finally fed to an output transducer.
  • This is usually designed as a handset, which converts the electrical output signal into an acoustic signal.
  • other embodiments are also possible here, e.g. an implantable output transducer that connects directly to an auditory ossicle and causes it to vibrate.
  • a hearing aid with a classifier which analyzes an incoming microphone signal in the hearing aid and automatically detects the hearing situation in which the hearing aid is currently located, is from the published patent application EP 0 064 042 A1 known. Depending on the detected hearing situation, the parameters relating to the signal processing in the hearing aid device are set automatically.
  • a modern hearing aid generally comprises a directional microphone system, by which in particular the speech intelligibility in various listening situations are improved can, for.
  • a directional microphone system comprises at least two microphones, the outputs of which are interconnected and whose output signals are linked together in order to obtain a directivity.
  • an internal signal delay between the two microphone signals different directional characteristics are adjustable.
  • the directivity usually serves the AI-DI (articulation index directivity index).
  • AI-DI articulation index directivity index
  • KEMAR measurements for a specific carrying position of the respective hearing aid device, wherein a reference signal is presented from the frontal direction.
  • the basic time delay is usually adjusted so that a sound signal incident from the front (with respect to the viewing direction) is optimally received and a sound signal incident from the opposite direction (from the rear) is maximally suppressed.
  • a hearing aid with a directional microphone system with two electrically interconnected microphones, in which different directional characteristics are adjustable as a function of a signal delay between the generated microphone signals for example, from the patent US 5,757,933 known.
  • the basic time delay is highly dependent on the effective distance of the two microphones with respect to a sound source, and secondly, the effective base time delay is also due to the frequency dependent diffraction and reflection of the sound frequency dependent.
  • the frequency-dependent base time delay is normally determined by KEMAR measurements, but is highly dependent on the reflection characteristics of the listening environment of the Hearing aid from.
  • the first problem is highly relevant for universally fitting (instant fit) hearing aids with fixed hose or cable lengths between the respective hearing aid and an associated earmold. Due to the given hose or cable lengths, the positions of the individually worn hearing aid devices vary more than in a conventional adaptation, because in the latter the acoustician can manually adjust the hose length to the individual ear of the respective user, thereby achieving the ideal position. The more an angle ⁇ between a connecting line of the microphone openings and the horizontal plane in a user-carried hearing aid device deviates from the angle ⁇ determined during the development process on the KEMAR for the optimum wearing position, the more ineffective the directivity of the directional microphone system, i. h., the AI-DI is sinking.
  • the second problem occurs regardless of the wearing position. Individual factors such as the hairstyle or shape of the head and pinna affect the frequency-dependent group delay, thereby impairing the performance of the directional microphone system.
  • the US 2002/0 041 696 A1 discloses a hearing aid with a directional microphone system and a method for operating such a hearing aid. According to US 2002/0 041 696 A1 the microphone signals of the directional microphone system are correlated with each other.
  • US Pat. No. 7,340,068 B2 discloses an apparatus and method for determining wind noise in which a first time dependent correlation signal consisting of values of a cross correlation function between a first and a second microphone signal and a second time dependent correlation signal are generated from values of an auto cross correlation function of either the first or the second second microphone signal.
  • Object of the present invention is to achieve a high performance of a directional microphone system in a hearing aid, regardless of the individual carrying position of the hearing aid.
  • the basic idea of the invention is to determine, by means of a cross-correlation analysis, the time delay with which an acoustic signal arrives at the microphones, in particular the microphone opening assigned to the respective microphone in the housing of the hearing aid.
  • the internal time delay in at least one microphone signal generated by one of the two microphones then takes place as a function of the external delay determined by means of the correlation analysis.
  • the invention makes it possible to adapt the internal delay to the individual, dependent on the wear position external delay.
  • an optimized with respect to the individual carrying position directivity can be adjusted. Even with a deviation of the individual wearing position from the ideal wearing position, a high performance of the respective directional microphone system, in particular a high AI-DI, is achieved.
  • the hearing aid according to the invention comprises a classifier for determining the hearing situation in which the hearing aid is currently located, wherein the adjustment of the time delay in dependence on the hearing situation.
  • the determination of the effective distance of the microphones of the respective directional microphone system is namely particularly then useful if the position of the acoustic sound source, from which an acoustic signal emanates and is detected by the microphones, is known in relation to the microphones. This can be assumed in certain listening situations. For example, it is assumed in the hearing situation “conversation at rest” that the hearing aid wearer faces the interlocutor. This is therefore an ideal time to determine the effective distance between the microphones. In addition to the listening situation “conversation in peace", however, this also applies to other listening situations, for example "television".
  • the determination of the time delay with which an acoustic signal arrives at the microphones takes place by means of a cross-correlation function.
  • This is commonly used in signal analysis to describe the correlation of two signals x (t) and y (t) at different time shifts ⁇ between the two signals. It shows, for example, maxima in the case of time shifts which correspond to the signal propagation time from the measuring location of the signal x (t) to the measuring location of the signal y (t). Also, runtime differences from one signal source to both measurement locations can be determined in this way.
  • the cross-correlation function of the microphone signals has a maximum at a time delay ⁇ which corresponds to the transit time of the acoustic signal between the two microphones (that is, between the two microphone openings in the housing of the hearing aid). This time delay is referred to as the effective time delay ⁇ eff .
  • the effective external transit time of an acoustic signal between the two microphones arriving from the user's point of view from the frontal direction into the hearing aid device carried in the individual position can be determined in a simple manner.
  • the internal time delay between the microphone signals does not become due to a single determination of the cross-correlation function of the two microphone signals and thus a one-time calculation of the effective time delay ⁇ eff set. Rather, it is advantageously carried out within a certain period of time a repeated determination of the cross-correlation function and thus the effective time delay ⁇ eff .
  • a resulting effective time delay ⁇ eff, res is determined therefrom. This results in stable results.
  • the time shift ⁇ is divided into specific time ranges and the frequency with which the effective time delay ⁇ eff falls within this time range is determined for each time range. From the time range in which the determined effective time delays ⁇ eff are most frequent, the resulting effective time delay ⁇ eff, res results.
  • a behind the ear portable hearing aid with a directional microphone system with a front and a rear microphone is advantageously the internal (base) time delay of the microphone signal generated by the rear microphone equal to the determined in the manner described above effective time delay ⁇ eff or resulting effective time delay ⁇ eff, res set.
  • This is the basic time delay, which largely extinguishes an acoustic signal coming from behind the hearing aid wearer (cardioid characteristic).
  • a time delay different from the base time delay may also be set.
  • a directional microphone system with two microphones for example, a super-cardioid, a hyper-cardioid or even an "eight" characteristic can be set.
  • a preferred embodiment of the invention provides to determine an also time-dependent internal time delay. This can be achieved in a simple manner in that the microphone signals emanating from the microphone signals are first each supplied to a filter bank. Done by this a splitting of the microphone signals into frequency bands. The internal time delay is then determined separately for the respective frequency band. As a result, the influence of diffraction and reflection phenomena can be largely suppressed.
  • the calculated effective time delay or possibly the resulting effective time delay is first subjected to a plausibility check before the internal time delay is adjusted.
  • erroneous values with regard to the effective time delay can be determined.
  • threshold values can be set for the calculated effective time delay, beyond which no adjustment of the internal time delay takes place.
  • FIG. 1 shows a simplified, schematic representation of the construction of a hearing aid, in particular a portable behind the ear hearing aid HA, according to the prior art.
  • Hearing aids comprise in principle as essential components at least one 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. B. miniature speaker or handset, or as an electromechanical transducer, z. B. bone conduction, realized.
  • the amplifier is usually integrated in a signal processing unit. In the embodiment according to FIG.
  • a signal processing unit SP which is also located in the housing of the hearing aid HA, processes the microphone signals and amplifies them.
  • the output of the signal processing unit SP is transmitted to a loudspeaker or listener R, which outputs an acoustic signal.
  • the sound is optionally transmitted via a sound tube (not shown), which is fixed with an earmold in the ear canal, to the eardrum of the user.
  • the power supply of the hearing aid device and in particular that of the signal processing unit SP is effected by a likewise arranged in the hearing aid HA voltage source VS, for example a battery.
  • a classifier K which can determine from an analysis of the microphone signals generated by the microphones F and B, the listening environment or the hearing situation in which the hearing aid HA is currently located.
  • auditory situations are, for example, “conversation at rest”, “conversation in noise”, “television” etc.
  • the signal processing in the signal processing unit parameters are adjusted automatically to adapt the signal processing to the detected hearing situation.
  • FIG. 2 is the usual structure of a directional microphone system used in hearing aids with two microphones F (front) and B (back) visible.
  • the microphones F and B usually have a distance between 5 mm and 15 mm and are equally sensitive in all directions (omnidirectional).
  • the Microphones F and B electrically interconnected and thereby linked together the microphone signals generated by them.
  • the microphone signal SB generated by the rear microphone B is delayed in a delay element T by an internal time delay T i and subtracted from the microphone signal SF, which is generated by the front microphone F.
  • the subtraction is usually realized by an inverter I in conjunction with a summation element S.
  • the microphone signal SB originating from the rear microphone B is inverted and added to the microphone signal SF originating from the front microphone F. This produces the directional microphone signal SD at the output of the summation element S.
  • the internal time delay T i is set to correspond to the propagation time of an acoustic signal between the two microphones F and B (base time delay)
  • the acoustic signal of a signal source on the line connecting the two microphones will be least attenuated when the signal source is located in front of the front microphone F, and maximally attenuated when the signal source is behind the rear microphone B.
  • the internal time delay T i By varying the internal time delay T i , the direction of the maximum attenuation can be pivoted in space in a known manner.
  • directional characteristics such as "cardioid characteristic”, “super cardioid characteristic”, “hyper cardioid characteristic”, “eight characteristic” etc can be set.
  • the invention is not limited to the shown conventional embodiment of a directional microphone system for a hearing aid. Rather, this analog is also applicable to other interconnections of microphones and directional microphone systems with more than two microphones.
  • FIG. 3 serves to explain the effects of a relation to an ideal position changed position of a worn on the head of a user hearing aid or its Directional microphone system.
  • a sound source in front of the front microphone F is on a straight line through the two microphones F and B.
  • the sound first hits the front microphone F and delays the propagation time, which the sound requires for the distance d between the two microphones F and B, at the rear microphone B.
  • the internal delay T i (cf. FIG. 2 ) is then set to correspond to the duration of the sound to overcome the distance d.
  • a time delay resulting from the effective distance d eff is automatically determined and set.
  • the microphones of the directional microphone system are not in a horizontal plane, but that even with the ideal carrying position a straight line through the microphones includes a predetermined angle ⁇ with the horizontal.
  • this does not change the procedure according to the invention, since in this case too the ideal carrying position can deviate from the actual individual carrying position and such a deviation is detected according to the invention and its effects are corrected accordingly.
  • FIG. 4 shows in a hearing aid device system with two hearing aids HA1 and HA2 required for determining an optimized internal time delay for the respective directional microphone system components.
  • the first hearing aid HA1 a front microphone F1 and a rear microphone B1 and the second hearing aid HA2 a front microphone F2 and a rear microphone B2.
  • the microphone signals SF1, SB1, SF2, SB2 emanating from the microphones are first fed to the filter banks FB11, FB12 or FB21, FB22, in which the microphone signals SF1, SB1, SF2, SB2 are each subdivided into a plurality of frequency bands.
  • the further signal processing then takes place in parallel in the respective frequency bands.
  • the calculation of the internal time delay will be described below for a particular frequency band. It is analogous to the other frequency bands.
  • the microphone signals SF3, SF4 of the relevant frequency band are first supplied to the hearing aid HA1 to a cross-correlation analysis unit K1.
  • the time dependent on a time delay ⁇ cross correlation function of the microphone signals has a maximum at a time delay ⁇ eff 1, which corresponds to the duration of the acoustic signal between the two microphones.
  • ⁇ eff a time delay ⁇ eff 1
  • several cross-correlation functions of the microphone signals SF3 and SF4 are determined as a function of the time delay ⁇ .
  • the statistical evaluation of the determined cross-correlation functions is then carried out in a histogram analysis unit H1, which is part of a control unit C1.
  • the relative frequency of the determined effective time delays ⁇ eff 1 as a function of the time delay ⁇ at which the respective cross-correlation function had its maximum is plotted for the considered period.
  • a time delay determination unit D1 a resulting effective time delay ⁇ eff, res 1 is then determined therefrom, at which the cross-correlation functions most often had their maximum.
  • This time delay is then called possible internal time delay used.
  • a plausibility check of the resulting effective time delay ⁇ eff, res 1 in a plausibility check unit P1 preferably takes place first.
  • a comparison of the determined, resulting effective time delay ⁇ eff, res 1 with a predefined setpoint range as well as a comparison with the resulting effective time delay ⁇ eff, res 2 determined in the second hearing aid HA2 in an analogous manner is preferable.
  • Strong deviations of the resulting effective time delays ⁇ eff, res 1 and ⁇ eff, res 2 found in both hearing aids HA1 and HA2 indicate unusable results.
  • the internal delay T i 1 is set in the hearing aid HA 1 and the internal delay T i 2 is set as a function of the respectively determined, resulting effective time delay ⁇ eff, res 1 or ⁇ eff, res 2 in the case of the hearing aid HA 2 ,
  • the internal time delay T i 1 or T i 2 is set equal to the resulting effective time delay ⁇ eff, res 1 or ⁇ eff, res 2 determined according to the invention.
  • control unit C2 which comprises a cross correlation analysis unit K2, a histogram analysis unit H2, a time delay determination unit D2 and a plausibility check P2 also for the second hearing aid HA2 of a hearing aid device.
  • HA1 and HA2 a linking of the microphone signals, for example analogously to the link according to FIG. 2 in which the determined internal time delays T i 1 and T i 2 are set in the respective delay units.

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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)
  • Signal Processing (AREA)
  • Neurosurgery (AREA)
  • Circuit For Audible Band Transducer (AREA)

Claims (14)

  1. Système d'appareils d'aide auditive comprenant un premier appareil d'aide auditive (HA1) pouvant être porté sur ou dans l'oreille gauche d'un utilisateur et comprenant un deuxième appareil d'aide auditive (HA2) pouvant être porté sur ou dans l'oreille droite d'un utilisateur, chacun des deux appareils d'aide auditive (HA1, HA2) possédant respectivement un système de microphone directionnel et le microphone directionnel respectif comprenant au moins
    - un premier microphone (F ; F1, F2) duquel émane un premier signal de microphone (SF ; SF1, SF2),
    - un deuxième microphone (B ; B1, B2) duquel émane un deuxième signal de microphone (SB ; SB1, SB2),
    - une unité de retard (T), en vue de générer un effet directionnel, le deuxième signal de microphone (SB ; SB1, SB2) ou un quatrième signal de microphone (SB3, SB4) qui résulte de celui-ci étant retardé au moyen de l'unité de retard (T) d'un retard dans le temps interne (Ti ; Ti1, Ti2) puis combiné avec le premier signal de microphone (SF ; SF1, SF2) ou un troisième signal de microphone (SF3, SF4) qui résulte de celui-ci en vue de générer un signal de microphone directionnel (SD),
    - une unité d'analyse de corrélation croisée (K1, K2), dans laquelle interviennent le premier (SF ; SF1, SF2) ou le troisième (SF3, SF4) signal de microphone ainsi que le deuxième (SB ; SB1, SB2) ou le quatrième (SB3, SB4) signal de microphone, destinée à déterminer une valeur d'une corrélation croisée entre les deux signaux de microphone (SF, SB ; SF1, SB1, SF3, SB3, SF2, SB2, SF4, SB4), une fonction de corrélation croisée des deux signaux de microphone (SF, SB ; SF3, SB3, SF4, SB4) pouvant être déterminée dans l'unité d'analyse de corrélation croisée (K1, K2) en fonction d'un retard dans le temps, et un retard dans le temps effectif (τeff1, τeff2) auquel la fonction de corrélation croisée possède un maximum pouvant être déterminé ;
    - une unité de contrôle de plausibilité (P1, P2) destinée à effectuer un contrôle de plausibilité du retard dans le temps effectif (τeff1, τeff2) déterminé ;
    - une unité de commande (C1, C2) destinée à régler le retard dans le temps interne (Ti; Ti1, Ti2) en fonction de la valeur de la corrélation croisée des deux signaux de microphone (SF, SB ; SF1, SB1, SF3, SB3, SF2, SB2, SF4, SB4), la valeur déterminée du retard dans le temps effectif (τeff1, τeff2) en fonction du résultat du contrôle de plausibilité pouvant être réglée en tant que retard dans le temps interne (Ti ; Ti1, Ti2) ;
    - un classificateur (K) destiné à déterminer une situation d'écoute dans laquelle l'appareil d'aide auditive (HA ; HA1, HA2) se trouve momentanément, le réglage du retard dans le temps interne (Ti ; Ti1, Ti2) s'effectuant dans des situations d'écoute données ;
    caractérisé en ce que
    le contrôle de plausibilité peut être réalisé à l'aide d'une comparaison des retards dans le temps effectifs (τeff1, τeff2) déterminés dans les deux appareils d'aide auditive (HA1, HA2).
  2. Système d'appareils d'aide auditive selon la revendication 1, le réglage du retard dans le temps interne (Ti ; Ti1, Ti2) s'effectuant dans une situation d'écoute « parole au repos ».
  3. Système d'appareils d'aide auditive selon la revendications 1 ou 2, une unité d'analyse d'histogramme (H1, H2) destinée à réaliser une analyse d'histogramme sur la base d'un nombre de retards dans le temps effectifs (τeff1, τeff2) déterminés au sein d'une période donnée étant présente et un retard dans le temps effectif résultant (τeff, rés1, τeff, rés2) pouvant être déterminé au moyen de l'analyse d'histogramme.
  4. Système d'appareils d'aide auditive selon la revendication 3, le retard dans le temps effectif résultant (τeff, rés1, τeff, rés2) pouvant être réglé en tant que retard dans le temps interne (Ti ; Ti1, Ti2).
  5. Système d'appareils d'aide auditive selon la revendication 3 ou 4, l'unité de contrôle de plausibilité (P1, P2) étant conçue pour réaliser un contrôle de plausibilité du retard dans le temps effectif résultant (τeff, rés1, τeff, rés2) déterminé et la valeur déterminée du retard dans le temps effectif résultant (τeff, rés1, τeff, rés2) pouvant être réglée en fonction du résultat du contrôle de plausibilité.
  6. Système d'appareils d'aide auditive selon l'une des revendications précédentes, une batterie de filtres (FB11, FB12, FB21, FB22) étant présente, servant à répartir les signaux de microphone (SF ; SF1, SB1, SF2, SB2) dans différentes bandes de fréquences et le réglage du retard dans le temps interne (Ti ; Ti1, Ti2) s'effectuant en fonction de la bande de fréquences respective.
  7. Système d'appareils d'aide auditive selon la revendication 5 ou 6, le contrôle de plausibilité pouvant être réalisé à l'aide d'une comparaison des retards dans le temps effectifs résultants (τeff, rés1, τeff, rés2) déterminés dans les deux appareils d'aide auditive (HA1, HA2).
  8. Procédé pour faire fonctionner un système d'appareils d'aide auditive comprenant un premier appareil d'aide auditive (HA1) pouvant être porté sur ou dans l'oreille gauche d'un utilisateur et comprenant un deuxième appareil d'aide auditive (HA2) pouvant être porté sur ou dans l'oreille droite d'un utilisateur, chacun des deux appareils d'aide auditive (HA1, HA2) comportant un système de microphone directionnel comprenant au moins un premier microphone (F ; F1, F2) duquel émane un premier signal de microphone (SF ; SF1, SF2), et un deuxième microphone (B ; B1, B2) duquel émane un deuxième signal de microphone (SB ; SB1, SB2), procédé selon lequel, dans l'appareil d'aide auditive (HA1, HA2) respectif
    - en vue de générer un effet directionnel, le deuxième signal de microphone (SB ; SB1, SB2) ou un quatrième signal de microphone (SB3, SB4) qui résulte de celui-ci est retardé au moyen d'une unité de retard (T) d'un retard dans le temps interne (Ti ; Ti1, Ti2) puis combiné avec le premier signal de microphone (SF ; SF1, SF2) ou un troisième signal de microphone (SF3, SF4) qui résulte de celui-ci,
    - une valeur d'une corrélation croisée des deux signaux de microphone (SF, SB ; SF1, SB1, SF3, SB3, SF2, SB2, SF4, SB4) est déterminée, une fonction de corrélation croisée des deux signaux de microphone (SF, SB ; SF1, SB1, SF3, SB3, SF2, SB2, SF4, SB4) étant déterminée en fonction d'un retard dans le temps,
    - un retard dans le temps effectif (τeff1, τeff2) est déterminé, auquel la fonction de corrélation croisée possède un maximum,
    - le retard dans le temps interne (Ti ; Ti1, Ti2) est réglé en fonction de la valeur de la corrélation croisée des deux signaux de microphone (SF, SB ; SF1, SB1, SF3, SB3, SF2, SB2, SF4, SB4), le retard dans le temps effectif (τeff1, τeff2) déterminée étant réglé en tant que retard dans le temps interne (Ti ; Ti1, Ti2),
    - une situation d'écoute dans laquelle l'appareil d'aide auditive (HA ; HA1, HA2) se trouve momentanément est déterminée,
    - le réglage du retard dans le temps interne (Ti ; Ti1, Ti2) est effectué dans des situations d'écoute données,
    - la valeur déterminée du retard dans le temps effectif (τeff1, τeff2) est soumise à un contrôle de plausibilité,
    caractérisé en ce que
    le contrôle de plausibilité est réalisé à l'aide d'une comparaison des retards dans le temps effectifs (τeff1, τeff2) déterminés dans l'appareil d'aide auditive (HA1, HA2) respectif.
  9. Procédé selon la revendication 8, le retard dans le temps interne (Ti ; Ti1, Ti2) étant réglé dans une situation d'écoute « parole au repos ».
  10. Procédé selon la revendication 8 ou 9, un retard dans le temps effectif résultant (τeff, rés1, τeff, rés2) étant déterminé au moyen d'une analyse d'histogramme sur la base d'un nombre de retards dans le temps effectifs (τeff1, τeff2) déterminés au sein d'une période donnée.
  11. Procédé selon la revendication 10, la valeur déterminée du retard dans le temps effectif résultant (τeff, rés1, τeff, rés2) étant soumise à un contrôle de plausibilité.
  12. Procédé selon la revendication 10 ou 11, le retard dans le temps effectif résultant (τeff, rés1, τeff, rés2) étant réglé en tant que retard dans le temps interne (Ti; Ti1, Ti2) .
  13. Procédé selon l'une des revendications 8 12, le retard dans le temps interne (Ti ; Ti1, Ti2) étant réglé en fonction de la fréquence d'un signal d'entrée acoustique qui pénètre dans l'appareil d'aide auditive.
  14. Procédé selon l'une des revendications 10 à 13, le contrôle de plausibilité étant réalisé à l'aide d'une comparaison du retard dans le temps effectif résultant (τeff, rés1, τeff, rés2) déterminé dans l'appareil d'aide auditive (HA1, HA2) respectif.
EP12160523.2A 2011-03-31 2012-03-21 Système d'aide auditive avec système de microphone directif et procédé de fonctionnement dudit système d'aide auditive avec système de microphone directif Active EP2506603B1 (fr)

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US8918197B2 (en) 2012-06-13 2014-12-23 Avraham Suhami Audio communication networks
EP2560412A1 (fr) 2012-10-08 2013-02-20 Oticon A/s Dispositif d'aide auditive avec un traitement audio dépendant des ondes cérébrales
EP2928210A1 (fr) * 2014-04-03 2015-10-07 Oticon A/s Système d'assistance auditive biauriculaire comprenant une réduction de bruit biauriculaire
EP2928211A1 (fr) * 2014-04-04 2015-10-07 Oticon A/s Auto-étalonnage de système de réduction de bruit à multiples microphones pour dispositifs d'assistance auditive utilisant un dispositif auxiliaire
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US20120250916A1 (en) 2012-10-04
DK2506603T3 (da) 2019-10-28
EP2506603A2 (fr) 2012-10-03
EP2506603A3 (fr) 2016-04-20
US9060232B2 (en) 2015-06-16
DE102011006471B4 (de) 2013-08-08
DE102011006471A1 (de) 2012-10-04

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