EP1771038B1 - Procédé d'utilisation d'un système de prothèse auditive pour le traitement binaural d'un utilisateur - Google Patents

Procédé d'utilisation d'un système de prothèse auditive pour le traitement binaural d'un utilisateur Download PDF

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Publication number
EP1771038B1
EP1771038B1 EP06121022A EP06121022A EP1771038B1 EP 1771038 B1 EP1771038 B1 EP 1771038B1 EP 06121022 A EP06121022 A EP 06121022A EP 06121022 A EP06121022 A EP 06121022A EP 1771038 B1 EP1771038 B1 EP 1771038B1
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EP
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Prior art keywords
hearing aid
aid device
signal
audio signal
microphone
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Not-in-force
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EP06121022A
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German (de)
English (en)
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EP1771038A3 (fr
EP1771038B2 (fr
EP1771038A2 (fr
Inventor
Gerhard Sporer
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Sivantos GmbH
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Siemens Audioligische Technik GmbH
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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
    • H04R25/45—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback
    • H04R25/453—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback electronically
    • 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
    • H04R2430/00—Signal processing covered by H04R, not provided for in its groups
    • H04R2430/03—Synergistic effects of band splitting and sub-band processing

Definitions

  • the invention relates to a method for operating a hearing aid system with a first hearing aid device which can be worn on or in the left ear of a user and a second hearing aid device which can be worn on or in the right ear of the user, the hearing aid devices each having at least one microphone for receiving an acoustic input signal and converting it into a An audio signal, a signal processing device for processing an audio signal and an output transducer for converting a processed audio signal in a perceptible by the user as an acoustic signal and means for transmitting an audio signal from a respective hearing aid to the respective other hearing aid, at least for a certain frequency range of the microphone of the first hearing aid device, a first audio signal is generated and this first audio signal or a resulting audio signal is transmitted to the second hearing aid and after a sig Nal kau is output from the handset of the second hearing aid and at the same time from the microphone of the second hearing aid, a second audio signal is generated and this second audio signal or a resulting audio signal is transmitted to the first hearing
  • an input signal is recorded by means of an input transducer and converted into an electrical input signal.
  • an input transducer usually serves as an input transducer at least one microphone which receives an acoustic input signal.
  • Modern hearing aids often comprise a microphone system with a plurality of microphones in order to achieve a direction dependent on the direction of arrival of acoustic signals reception, a directional characteristic.
  • the input transducers may also include a telecoil or an antenna for Recording of electromagnetic input signals.
  • the input signals converted by the input converter into electrical input signals (audio signals) are fed to a signal processing unit for further processing and amplification.
  • the further processing and amplification takes place to compensate for the individual hearing loss of a hearing aid wearer, as a rule, as a function of the signal frequency.
  • the signal processing unit generates an electrical output signal, which is fed via an output transducer to the hearing of the hearing aid wearer, so that the latter perceives the output signal as an acoustic signal.
  • output transducers usually listeners are used, which generate an acoustic output signal.
  • output transducers for generating mechanical vibrations are also known, which directly excite certain parts of the ear, such as the ossicles, to vibrate.
  • output transducers are known which directly stimulate neurons of the ear.
  • the microphone and the earpiece of a hearing aid device usually have only a small distance from one another. This promotes unwanted sound transmission directly from the listener to the microphone, often resulting in annoying feedback whistling (feedback).
  • feedback whistling feedback whistling
  • none of these measures has so far reliably and completely eliminated the occurrence of feedback whistling.
  • the hearing aids include means for wireless transmission of control signals and audio signals between the hearing aids. This makes it possible to process the audio signals obtained by means of the microphones in both hearing aids at least partially only in one of the two hearing aids. Signal processing resources therefore need not be equally provided in both hearing aids.
  • a method for operating a hearing aid device system with two hearing aids for binaural care of a user is known in which the direction of incidence of an acoustic signal is determined in the hearing aid system. Depending on the determined direction of incidence the parameters relating to the signal processing in the hearing aid system are set.
  • the object of the present invention is therefore to largely avoid feedback in a hearing aid device system for the binaural supply of a user.
  • the basic idea of the invention is to separate the signal paths of the hearing aid devices, which lead from a microphone via a signal processing unit to a receiver, in a hearing aid device system with two hearing aid devices for the binaural supply of a hearing impaired person.
  • An audio signal emitted by the microphone of the hearing aid worn on the left ear is transmitted to the hearing aid worn on the right ear and output by the listener of the hearing aid worn on the right ear.
  • an audio signal emitted by the microphone of the hearing aid worn on the right ear is transmitted to the left hearing aid and output by the listener of the left hearing aid.
  • the distance between a microphone and a listener, with a feedback path between them, has been significantly increased.
  • the head of the user determines the feedback path.
  • the distance between a handset and a microphone, between which a feedback path is formed in the range of millimeters to a maximum of a few centimeters, so this distance increases in a hearing aid device system according to the invention to several decimeters.
  • the invention is advantageous in the case of a severe hearing loss, as it increasingly causes feedback due to the required high amplification. Furthermore, it is to be expected that in the case of the hearing aid system according to the invention, the severely hearing impaired, habituation takes place after a short time, so that the direction of an incoming sound signal is correctly interpreted again.
  • the human brain seems to be adaptive in this regard. Namely, it is known that when seeing, the eyes caught Images are projected mirror-inverted onto the respective retina. Therefore, we would actually have to see all things "upside down”. If one equips test persons with special glasses, which produce a mirror-inverted representation, then these subjects actually see first of all "upside down". Surprisingly, this impression disappears after a few days, so that everything is seen "normal” again. After prolonged wearing then occur when discontinuing the corresponding glasses again the same problems as at the beginning when wearing the glasses.
  • the locations in the signal paths of the hearing aid devices, at which the separation of the signal paths for signal transmission between the hearing aid devices takes place, can in principle be chosen almost arbitrarily.
  • a "microfonn" separation can take place in which the audio signals emitted by the microphones are not or hardly further processed before they are transmitted crosswise between the hearing aids.
  • "separation close to the listener” can take place, in which the further processing of the audio signals generated by the microphones has already taken place, at least substantially. This is well possible especially in digital hearing aid systems in which only numbers rows are transmitted between the hearing aids anyway and therefore the energy required for the signal transmission is almost independent of the degree of amplification of the audio signals.
  • signal processing may need to be adapted to the hearing loss of the right ear and vice versa.
  • the separation of the signal paths can in principle also take place at any point between the two extremes mentioned.
  • An asymmetrical separation of the signal paths is possible, so that in a hearing aid, a signal at one point of the signal path is sent and sent to the other hearing aid when the signal processing is already substantially completed and the same hearing aid, the almost unprocessed audio signal of the other hearing aid for further processing receives.
  • the signal processing is mainly concentrated on one of the two hearing aids of the hearing aid system.
  • the signal transmission between the hearing aids worn on the right and on the left ear preferably takes place wirelessly. This increases the wearing comfort of the hearing aid system according to the invention. However, a less convenient but less expensive wired audio signal transmission may be provided. Furthermore, the signal transmission is preferably carried out directly between the two worn on or in the ear hearing aids. However, signal transmission may also be via another device, e.g. an external processor unit carried on the body.
  • the microphone signals emanating from the microphones are transmitted completely crosswise to the respective other hearing aid.
  • an over-cross transmission of audio signals between a hearing aid worn on or in the left ear and on or in the right ear of a user only occurs when the occurrence of feedback has to be expected with high probability. This is especially the case when an acoustic input signal experiences a high gain. Furthermore, feedback often occurs when a high sound pressure level is generated by the listener of the hearing aid in question.
  • the set gain or the generated sound pressure level is monitored, so that when certain threshold values are exceeded, an over-cross transmission according to the invention can take place automatically.
  • the threshold values are advantageously adjustable by programming the hearing aid devices.
  • monitoring and cross-over transmission are preferably carried out in each case for specific frequency ranges or channels.
  • the crosswise transmission of audio signals is limited to one or more specific listening programs.
  • the cross-over transmission thus takes place only in the hearing programs for which this transmission is also explicitly, e.g. by programming the hearing aids, was provided.
  • the invention can thus be used particularly advantageously in the listening situations “television” and “music”, in which feedback occurs particularly frequently because of the large dynamic range of the acoustic input signals.
  • the hearing aids each comprise a plurality of microphones for the formation of directional microphones with directional characteristics of different order.
  • audio signals can be processed, which emerge from the directional microphones of different order.
  • a complete separation of the signal path between the microphone and the receiver preferably takes place at least for a certain frequency range. This means that no audio signal obtained from the microphone signal of the same hearing aid device is supplied to the listener of this hearing aid device for this frequency range.
  • an audio signal from the signal path of the first hearing aid is also tapped and transmitted to the second hearing aid of the hearing aid system, in parallel there is also a signal processing of the present at the tap audio signal in the first hearing aid and a signal output of the processed signal through the Handset of the first hearing aid.
  • the signal processing is carried out in the context of the invention, however, such that feedback by this signal in the first hearing aid are likely to be excluded.
  • the signal in question is therefore usually delivered by the second hearing aid device with a higher sound pressure level than from the first, when in both ears in about the same hearing loss is present.
  • Feedback can be excluded with high probability, if the so-called loop gain for a particular Hearing aid continuous signal even in the worst case, for example, even in a poorly fitting Otoplasik, always less than one.
  • a threshold which is an upper limit for the gain, is set accordingly.
  • FIG. 1 shows a hearing aid system 1, 1 'according to the invention with a left and a right hearing aid 1 and 1'.
  • Each of the hearing aids 1 or 1 ' comprises a microphone 2 or 2', a first signal processing unit 3 or 3 ', a second signal processing unit 4 or 4' and a receiver 5 or 5 '.
  • the first signal processing units 3 and 3 ' are each connected to a transmitting coil 6 or 6' and the second signal processing units 4 and 4 'are each connected to a receiving coil 7 or 7'.
  • a single coil or antenna may be present, which is suitable both for transmitting and for receiving signals.
  • the hearing aid system according to FIG. 2 has two identically constructed hearing aids 10 and 10 '.
  • the audio signal emanating from the omnidirectional microphone 11 is fed directly to a filter bank 14 and, on the other hand, it is electrically connected to the omnidirectional microphone 12 to form a first-order directional microphone system.
  • the audio signal originating from the omnidirectional microphone 12 is first delayed in a delay unit 13 and subtracted from the audio signal of the microphone 11.
  • the audio signal M2 of the first-order directional microphone thus formed is first supplied to the filter bank 15, in which the audio signals are split into a plurality of frequency bands.
  • the parallel signal processing takes place in the signal processing blocks 16 and 17 of the signal processing unit 19.
  • the same cutoff frequencies are selected for the different frequency bands in both hearing aid devices.
  • the signal path between the signal processing blocks 16 and 17 is interrupted.
  • the listener 18 thus no signal component of the frequency band FBn of the audio signals M1 and M2 is supplied. Instead, this signal component is transmitted via the transmitting coil 21 and the receiving coil 22 'to the hearing aid device 10' and emitted by the hearing aid device 10 'via the earpiece 18'.
  • this signal component is transmitted via the transmitting coil 21 and the receiving coil 22 'to the hearing aid device 10' and emitted by the hearing aid device 10 'via the earpiece 18'.
  • there is preferably still a signal processing in the signal processing block 17 ' eg a gain.
  • the audio signal in the frequency band FBn 'from the hearing aid 10' via the transmitting coil 21 'and the receiving coil 22 is transmitted to the hearing aid 10 and supplied to the listener 18 after signal processing in the signal processing block 17.
  • the crosswise signal transmission described in this way can be carried out for one or more frequency bands that are particularly critical with regard to the feedback tendency.
  • the respective frequency bands are selectable, for example by programming the hearing aids.
  • the signal paths of the hearing aid devices 10 and 10 'for the frequency bands FBn or FBn' are interrupted by the opened switches 23 and 23 'between the signal processing blocks 16 and 17 or 16' and 17 '.
  • the output signal output by the receiver 18 thus contains no signal component originating from the microphone signals M1 and M2 in the frequency band FBn and the output signal output by the receiver 18 'does not contain any signal component in the frequency band FBn' originating from the microphone signals M1 'and M2'.
  • the switches are missing 23 or 23 ', or they remain closed, at least in certain applications, even if an over-cross transmission of audio signals for the critical frequency bands FBn or FBn'.
  • the gain is adjusted so that feedback is excluded.
  • the ear is supplied with an output signal which comprises the entire transmittable bandwidth of an input signal detected by the microphones, however, in view of the gain required to compensate for the individual hearing loss of the hearing aid wearer for these frequency bands only in an attenuated form.
  • the other ear receives the transmitted signal in the volume required for that other ear.
  • the two microphone signals M1 and M2 originating from directional microphone systems of different order are treated differently with regard to the signal transmission according to the invention.
  • the microphone signals M1 and M1 'emanating from the two omnidirectional microphones 11 and 11' are advantageously transmitted crosswise to the respective other hearing aid device and the microphone signals M2 or M2 'which are less critical with respect to the feedback tendency are not transmitted to the respective other hearing aid device. This procedure has the advantage that the amount of data to be transmitted is reduced.
  • the signal processing in both hearing aid devices 10 and 10 ' preferably takes place as a function of the hearing situation in which the hearing aid devices are located instantaneously.
  • an automatic adjustment can take place, which is based, for example, on an analysis of the audio signals in the signal processing blocks 16 or 16 '.
  • the hearing aid devices 10 and 10 ' according to the exemplary embodiment, it is possible to manually switch between different hearing programs by means of the program selection buttons 20 or 20'.
  • the selection of the audio signals e.g. M1, M1 'or M2, M2' or the selection of the one or more transmitted frequency bands as a function of the current hearing situation or the current hearing program.
  • the required Amplification of an existing audio signal or the sound pressure level of the output signal from the handset automatically estimated. If one of these values exceeds a predetermined threshold value, an over-cross transmission according to the invention automatically takes place; otherwise this will be omitted. This ensures that cross-transmission of audio only occurs when it appears necessary to avoid feedback.

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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)
  • Stereophonic System (AREA)
  • Details Of Audible-Bandwidth Transducers (AREA)

Claims (13)

  1. Procédé pour faire fonctionner un système de prothèse auditive ayant une première prothèse ( 1, 10 ) auditive pouvant être portée à l'oreille gauche d'un utilisateur ou dans celle-ci et une deuxième prothèse ( 1', 10' ) auditive pouvant être portée à l'oreille droite de l'utilisateur ou dans celle-ci, dans lequel les prothèses ( 1, 1', 10, 10' ) ont respectivement au moins un microphone ( 2, 2', 11, 11', 12, 12' ) de réception d'un signal acoustique d'entrée de transformation en un signal audio, un dispositif ( 3, 4, 3', 4', 16, 17, 16', 17' ) de traitement du signal pour traiter un signal audio et un transducteur ( 5, 5', 18, 18' ) de sortie pour la transformation d'un signal audio traité en un signal perceptible par l'utilisateur comme signal acoustique ainsi que des moyens ( 6, 7, 6', 7', 21, 22, 21', 22' ) de transmission d'un signal audio de respectivement l'une des prothèses ( 1, 1', 10, 10' ) auditives à respectivement l'autre prothèse ( 1, 1', 10, 10' ) auditive, dans lequel, au moins pour une certaine plage de fréquences, il est produit par le microphone ( 2, 2', 11, 11', 12, 12' ) de la première prothèse ( 1, 10) auditive un premier signal audio et ce premier signal audio ou un signal audio qui en provient est transmis à la deuxième prothèse ( 1', 10' ) auditive et après un traitement du signal par l'écouteur ( 5', 18' ) de la deuxième prothèse ( 1', 10' ) auditive est émis comme signal acoustique de sortie et il est produit en même temps par le microphone ( 2, 2', 11, 11', 12, 12' ) de la deuxième prothèse ( 1', 10' ) auditive un deuxième signal audio, et ce deuxième signal audio ou un signal audio qui en provient est transmis à la première prothèse ( 1, 10 ) auditive et après un traitement d'un signal par l'écouteur ( 5, 18 ) de la première prothèse ( 1, 10 ) auditive est émis en tant que signal acoustique de sortie, caractérisé en ce qu'au moins pour la plage de fréquences déterminée le signal acoustique de sortie et émis par l'écouteur ( 5', 18' ) de la deuxième prothèse ( 1', 10' ) auditive provient exclusivement du premier signal audio et le signal acoustique de sortie émis par l'écouteur ( 5', 18' ) de la première prothèse ( 1, 10 ) auditive provient exclusivement du deuxième signal audio.
  2. Procédé pour faire fonctionner un système de prothèse auditive suivant la revendication 1, dans lequel on interrompt le trajet du signal entre le microphone ( 2, 11, 12 ) et l'écouteur ( 5', 18' ) de la première prothèse ( 1, 10 ) auditive pour ce qui concerne le premier signal audio.
  3. Procédé pour faire fonctionner un système de prothèse auditive suivant la revendication 1 ou 2, dans lequel on interrompt le trajet du signal entre le microphone ( 2', 11', 12' ) et l'écouteur ( 5', 18' ) de la deuxième prothèse ( 1', 10' ) auditive pour ce qui concerne le deuxième signal audio.
  4. Procédé pour faire fonctionner un système de prothèse auditive ayant une première prothèse ( 1, 10 ) auditive pouvant être portée à l'oreille gauche d'un utilisateur ou dans celle-ci et une deuxième prothèse ( 1', 10' ) auditive pouvant être portée à l'oreille droite de l'utilisateur ou dans celle-ci, dans lequel les prothèses ( 1, 1', 10, 10' ) ont respectivement au moins un microphone ( 2, 2', 11, 11', 12, 12' ) de réception d'un signal acoustique d'entrée de transformation en un signal audio, un dispositif ( 3, 4, 3', 4', 16, 17, 16', 17' ) de traitement du signal pour traiter un signal audio et un transducteur ( 5, 5', 18, 18' ) de sortie pour la transformation d'un signal audio traité en un signal perceptible par l'utilisateur comme signal acoustique ainsi que des moyens ( 6, 7, 6', 7', 21, 22, 21', 22' ) de transmission d'un signal audio de respectivement l'une des prothèses ( 1, 1', 10, 10' ) auditives à respectivement l'autre prothèse ( 1, 1', 10, 10' ) auditive, dans lequel, au moins pour une certaine plage de fréquences, il est produit par le microphone ( 2, 2', 11, 11', 12, 12' ) de la première prothèse ( 1, 10 ) auditive un premier signal audio et ce premier signal audio ou un signal audio qui en provient est transmis à la deuxième prothèse ( 1', 10' ) auditive et après un traitement du signal par l'écouteur ( 5', 18' ) de la deuxième prothèse ( 1', 10' ) auditive est émis comme signal acoustique de sortie et il est produit en même temps par le microphone ( 2, 2', 11, 11', 12, 12' ) de la deuxième prothèse ( 1', 10' ) auditive un deuxième signal audio, et ce deuxième signal audio ou un signal audio qui en provient est transmis à la première prothèse ( 1, 10 ) auditive et après un traitement d'un signal par l'écouteur ( 5, 18 ) de la première prothèse ( 1, 10 ) auditive est émis en tant que signal acoustique de sortie, caractérisé en ce qu'au moins pour la plage de fréquences déterminée le signal acoustique de sortie et émis par l'écouteur ( 5', 18' ) de la deuxième prothèse ( 1', 10' ) auditive provient du premier et du deuxième signal audio, une amplification, qui ne dépasse pas la valeur de seuil qui n'est pas critique pour ce qui concerne l'apparition de réactions, étant établie dans la deuxième prothèse ( 5', 18' ) auditive pour ce qui concerne le deuxième signal audio, une amplification plus grande que pour le deuxième signal audio étant établie en ce qui concerne le premier signal audio au moins pour la plage de fréquences déterminée, le signal acoustique de sortie et émis par l'écouteur ( 5, 18 ) de la première prothèse ( 1, 10 ) auditive provenant du premier et du deuxième signal audio, une amplification étant établie dans la première prothèse ( 5, 18 ) auditive en ce qui concerne le premier signal audio, amplification qui ne dépasse pas une valeur de seuil non critique en ce qui concerne l'apparition de réactions et une amplification plus grande que pour le premier signal audio étant établie pour ce qui concerne le deuxième signal audio.
  5. Procédé pour faire fonctionner un système de prothèse auditive suivant l'une des revendications 1 à 4, dans lequel les signaux audio entre les prothèses ( 1, 1', 10, 10' ) auditives sont transmis par fil.
  6. Procédé pour faire fonctionner un système de prothèse auditive suivant l'une des revendications 1 à 4, dans lequel les signaux audio entre les prothèses ( 1, 1', 10, 10' ) auditives sont transmis sans fil.
  7. Procédé pour faire fonctionner un système de prothèse auditive suivant l'une des revendications 1 à 6, dans lequel le signal audio sortant du microphone ( 1, 11, 12 ) de l'une des deux prothèses ( 1, 10 ) auditives ou le signal audio qui en provient est transmis complètement à l'autre prothèse ( 1', 10' ) auditive.
  8. Procédé pour faire fonctionner un système de prothèse auditive suivant l'une des revendications 1 à 6, dans lequel le signal audio sortant du microphone ( 1, 11, 12 ) de l'une des deux prothèses ( 1, 10 ) auditives ou le signal audio qui en provient n'est transmis que sur une certaine plage ( FBn, FBn' ) de fréquences entre les prothèses ( 1, 1', 10, 10' ) auditives.
  9. Procédé pour faire fonctionner un système de prothèse auditive suivant l'une des revendications 1 à 8, dans lequel, au moins pour une plage ( FBn ) de fréquences, une amplification du signal acoustique d'entrée, nécessaire pour la compensation d'une perte auditive de l'utilisateur, est déterminée par la prothèse ( 1, 10 ) auditive concernée et la transmission du signal entre les prothèses auditives s'effectue en fonction de l'amplification déterminée.
  10. Procédé pour faire fonctionner un système de prothèse auditive suivant l'une des revendications 1 à 8, dans lequel, au moins pour une plage ( FBn ) de fréquences, on détermine le niveau de pression acoustique d'un signal acoustique de sortie produit par la prothèse ( 1, 10 ) auditive concernée et on effectue la transmission du signal entre les prothèses auditives en fonction du niveau de pression acoustique déterminée.
  11. Procédé pour faire fonctionner un système de prothèse auditive suivant la revendications 9 ou 10, dans lequel on règle des valeurs de seuil de l'amplification ou du niveau de la pression acoustique en programmant la prothèse ( 1, 10 ) auditive concernée.
  12. Procédé pour faire fonctionner un système de prothèse auditive suivant l'une des revendications 1 à 11, dans lequel chaque prothèse ( 10, 10' ) auditive a plusieurs microphones ( 11, 12, 11', 12' ), qui sont câblés entre eux respectivement pour former un microphone directionnel, dans lequel des signaux de microphone directionnel ayant des caractéristiques directionnelles différentes sont produits respectivement par les microphones directionnels et dans lequel seul un signal de microphone directionnel d'une caractéristique directionnelle déterminée est transmis d'une prothèse ( 10 ) auditive à l'autre prothèse ( 10' ) auditive.
  13. Procédé pour faire fonctionner un système de prothèse auditive suivant l'une des revendications 1 à 12, dans lequel on effectue la transmission du signal entre les prothèses ( 1, 1', 10, 10' ) auditives en fonction d'une situation d'écoute instantanée dans laquelle se trouve le système de prothèse auditive ou en fonction d'un programme d'écoute régulé.
EP06121022A 2005-09-30 2006-09-21 Procédé d'utilisation d'un système de prothèse auditive pour le traitement binaural d'un utilisateur Not-in-force EP1771038B2 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102005047049 2005-09-30

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EP1771038A2 EP1771038A2 (fr) 2007-04-04
EP1771038A3 EP1771038A3 (fr) 2008-12-10
EP1771038B1 true EP1771038B1 (fr) 2009-12-02
EP1771038B2 EP1771038B2 (fr) 2013-02-27

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EP06121022A Not-in-force EP1771038B2 (fr) 2005-09-30 2006-09-21 Procédé d'utilisation d'un système de prothèse auditive pour le traitement binaural d'un utilisateur

Country Status (6)

Country Link
US (1) US7953237B2 (fr)
EP (1) EP1771038B2 (fr)
CN (1) CN101026903B (fr)
AT (1) ATE450986T1 (fr)
DE (1) DE502006005495D1 (fr)
DK (1) DK1771038T4 (fr)

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Publication number Priority date Publication date Assignee Title
EP2071874B1 (fr) * 2007-12-14 2016-05-04 Oticon A/S Dispositif auditif, systeme de dispositif auditif et procedure pour controler le systeme de dispositif auditif
DE102008015263B4 (de) 2008-03-20 2011-12-15 Siemens Medical Instruments Pte. Ltd. Hörsystem mit Teilbandsignalaustausch und entsprechendes Verfahren
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ATE450986T1 (de) 2009-12-15
DE502006005495D1 (de) 2010-01-14
US7953237B2 (en) 2011-05-31
DK1771038T3 (da) 2010-04-12
EP1771038A3 (fr) 2008-12-10
CN101026903A (zh) 2007-08-29
DK1771038T4 (da) 2013-06-03
US20070076910A1 (en) 2007-04-05
CN101026903B (zh) 2011-10-19
EP1771038B2 (fr) 2013-02-27
EP1771038A2 (fr) 2007-04-04

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