EP2180726B2 - Localisation du son avec des prothèses auditives binauriculaires - Google Patents

Localisation du son avec des prothèses auditives binauriculaires Download PDF

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Publication number
EP2180726B2
EP2180726B2 EP10000610.5A EP10000610A EP2180726B2 EP 2180726 B2 EP2180726 B2 EP 2180726B2 EP 10000610 A EP10000610 A EP 10000610A EP 2180726 B2 EP2180726 B2 EP 2180726B2
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Prior art keywords
signal
hearing aid
gain
hearing
ascertained
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EP10000610.5A
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German (de)
English (en)
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EP2180726B1 (fr
EP2180726A1 (fr
Inventor
Frank Beck
Gerhard Sporer
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Sivantos GmbH
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Siemens Audioligische Technik GmbH
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Application filed by Siemens Audioligische Technik GmbH filed Critical 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
    • H04R25/55—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

Definitions

  • the invention relates to a hearing aid system and a method for setting a hearing aid system having at least one first and one second hearing aid device, each having at least one input transducer for receiving an acoustic input signal and conversion to an electrical signal, a signal processing unit for processing the electrical signal and an output transducer for conversion comprise the electrical signal in an output signal and between which a signal path for data transmission is provided.
  • Directional hearing is the ability of a person to distinguish the direction in which a sound source is located. If a sound source is not in front of or behind the person, the finite propagation speed of the sound inevitably results in a difference in transit time between the two ears, and thus a time difference with which the ears perceive a sound wave coming from one direction. If a sound is e.g. from the perspective of the peson comes from the right, this reaches the right ear by a fraction of a second rather than the left ear. This time difference is much shorter than the person concerned can consciously recognize. The effect occurs through an automatic integration process in the acoustic nervous system.
  • the former solution has the disadvantage that a further assembly is necessary and the hearing aid wearer now requires three instead of two devices, which means a significant limitation of wearing comfort, maintenance and handling.
  • the second solution requires that all signal processing must be done by a single signal processing unit on a single page. While in the solution with a third device enough space is available to provide a correspondingly powerful signal processing and ensure their energy needs, the space is limited in a hearing aid located on the ear. Therefore, a master-slave solution with two differently designed hearing aids must necessarily have a lower computational capacity than would be available when using both hearing aids.
  • Another approach to solving the above problem is to transmit the incoming sound signals on the hearing aids of both sides to the other device and to process both signals on each side. In this way, the acoustic signals received at both ears undergo the same steps of signal processing together and therefore automatically experience the same signal delay.
  • This approach is for example from the WO 97/14268 as well as the WO 99/43185 out.
  • the transmission of the microphone signals on both sides of a binaural hearing aid system to the other side and the simultaneous processing of both signals on both sides solves the problem of a transit time difference, but is subject to the same limitations as the master-slave approach.
  • a method for operating a hearing aid system is known in which sound field characteristics are transmitted from one hearing aid to another. These can be signal levels.
  • a hearing aid is known in which a signal transmission from one to the other hearing aid via optical fibers is made. In this case, control signals can be transmitted.
  • the object of the present invention is to support the natural directional hearing in a hearing aid system for binaural care and to keep the additional computational effort required for this purpose low.
  • a hearing aid system In a hearing aid system, directional hearing in the case of binaural hearing aid supply is improved by matching the signal propagation times of the hearing aid devices attached to the two ears. However, the signal propagation times are only one factor affecting directional hearing.
  • an adaptation of the amplitude response of the two hearing aids is also carried out. Differences in the amplitudes of signals that occur from different directions are mainly caused by the shading effect of the head. The differences in the amplitudes are very small and can not be consciously perceived. Only by a very fine adjustment of the hearing aids of a hearing aid system, these minimum differences in amplitude, which are caused by different directions of incidence remain maintained. The exact amount of these differences is rather secondary.
  • a gain or gain change of an electrical signal in at least one of the hearing aid devices is determined.
  • the gain change may be e.g. be caused by the change of a parameter of the signal processing of the hearing aid.
  • data for identifying the current amplification or for characterizing the gain change is transmitted from the hearing aid device to the other hearing aid device of the hearing aid system. Also in this hearing aid then the gain is adjusted accordingly. This may mean that the gain is changed by the same amount.
  • the amplification in the second hearing aid device is changed such that the same loudness impression is produced again in the case of a sound signal arriving from the 0 degree direction (directly from the front) on both ears through the supply of the hearing aid devices. Deviating from the 0-degree direction sound signals are then perceived again with different loudness impression, so that the hearing aid wearer can perceive the direction from which the sound signal arrives.
  • the value of a gain change in a hearing aid according to the invention may be permanently assigned to certain settings or functions of the hearing aid. For example, in a feedback suppression algorithm, there may always be a 10 dB reduction in gain. Data for identifying this gain change can then, as soon as the algorithm is actively switched, be transferred to the other hearing aid device of the hearing aid system, so that a corresponding gain reduction is also performed in this case. In many applications, however, there is no fixed association between certain functions of the hearing aid and related gain changes. The amplification or gain change is then first determined automatically in the hearing aid. For this purpose, signal amplitudes or signal levels of an electrical signal to points in the signal path of the hearing aid behind one another recorded and evaluated.
  • a test signal is preferably fed into the signal path, which at least partially passes through the signal processing unit of the hearing aid.
  • the amplification in both hearing aids is determined and related data transferred to the other hearing aid in the gain adjustment.
  • filter media are preferably set.
  • an adjustment of the amplification of the two hearing aids of a hearing aid system is always carried out even when the gain setting when at least one of the hearing aids a parameter and / or functional change.
  • the gain adjustment can also be done at periodic intervals.
  • the determination and adaptation of the amplification or of the amplitude transmission behavior in a hearing device system with multi-channel hearing aid devices can in each case only relate to specific frequency bands.
  • the transmission behavior of signal amplitudes is also measured.
  • a test signal can be fed into the signal path at one point and read out again at the following point.
  • this measurement is also carried out for different signal frequencies. If a parameter or function change then takes place in at least one of the hearing aid devices, the transmission behavior with respect to the signal amplitudes can be measured again and differences in the transmission behavior can be ascertained. Data that are characteristic of the signal amplitudes are then transferred to the respective other hearing aid device of the hearing device system for adaptation to the changed transmission behavior.
  • the invention applies equally to behind the ear portable (BTE), in the ear portable (ITE) or implantable hearing aid systems application.
  • FIG. 1 shows a schematic representation of a hearing aid system with two hearing aids 1 and 1 '.
  • the processing of the electrical signal to compensate for the hearing loss of a hearing aid wearer takes place in the signal processing units 3 or 3 '.
  • the processed signal is finally converted back into a sound signal by an electric-acoustic output transducer (earphone) 4 or 4 'and fed to the ears of a hearing aid wearer.
  • earphone electric-acoustic output transducer
  • the adjustment of the hearing aid devices 1 and 1 'to the respective hearing situation takes place by actuation of a control element 7 or 7' on at least one of the hearing aid devices 1 or 1 '.
  • signal propagation times of the signal processing units 3 and 3' for the respective hearing programs and taking into account the respective settings of the hearing aid devices 1 and 1 'to compensate for the individual hearing loss of a hearing aid wearer are determined. This can be done, for example, by transit time measurements during the adaptation of the hearing aid devices 1 and 1 '. If the signal propagation times for both hearing aid devices 1 and 1 'are known under the selected settings for the respective hearing programs, the hearing programs are assigned data for characterizing the signal propagation times and are likewise stored in the memory units 6 or 6'. These data can be both the signal propagation times as such and also the respective transit time differences between the individual hearing programs or the hearing aid devices 1 and 1 '.
  • the hearing aid device 1 If, for example, the hearing aid device 1 is switched between two hearing programs, then not only the parameters of the new hearing program are read from the memory unit 6, but also the data assigned to the newly set hearing program for characterizing the signal delay time. The latter are then transmitted via a transmitting and receiving unit 8 to the hearing aid 1 '.
  • the hearing aid device 1 ' receives in turn by means of the transmitting and receiving unit 8' sent by the hearing aid 1 Data and supplies them to the control unit 5 '. This in turn compares the transmitted data with the information stored in the memory unit 6 'regarding the running time of the currently set hearing program. For example, by controlling a delay means, which is designed in the exemplary embodiment as an all-pass filter 9 or 9 ', then any differences in transit time can be compensated.
  • both hearing aid devices 1 and 1 'thus have the same signal propagation delay between the input transducer 2 and the output transducer 4 or the input transducer 2' and the output transducer 4 '.
  • both hearing aid devices 1 and 1 'thus have the same signal propagation delay between the input transducer 2 and the output transducer 4 or the input transducer 2' and the output transducer 4 '.
  • FIG. 2 Another hearing aid system shows FIG. 2 , Since in this case both hearing aids of the hearing aid system have the same equivalent circuit, is in FIG. 2 only one of the two, namely the hearing aid 11, shown. Also this includes as the hearing aids 1 and 1 'in the embodiment according to FIG. 1 a microphone 12 for receiving an acoustic signal and conversion into an electrical signal, a signal processing unit 13 for frequency-dependent processing of the electrical signal and a receiver 14 for converting the electrical signal into an acoustic output signal.
  • the hearing aid device 11 further comprises an A / D converter 15 for converting the output signal of the microphone into a digital signal, and a D / A converter 16 for reconverting the digital signal into an analog signal before the signal output via the receiver 14.
  • FIG. 2 a signal analysis of the digital electrical input signal in an analysis and control unit 17. Also, this is connected to a memory unit 18 in which different, the signal processing processing memory sets are stored.
  • a complete set of parameters which is stored in the memory unit 18, it is provided in the hearing aid 11, even adaptively change only individual settings and parameters for adjusting the signal processing to the respective hearing situation.
  • certain functions or algorithms can be switched on or off.
  • an algorithm for speech enhancement can be set in the hearing aid device, or an algorithm for noise suppression can be activated when detected noises.
  • the hearing aid device 11 has a transit time determination unit 19.
  • the fed-in signal passes through the signal processing unit 13 and is tapped before the output via the handset 14 and fed to the transit time determination unit 19.
  • the generated signal lies in a frequency range which is not audible acoustically by the hearing aid wearer.
  • the transit time measurement is advantageously carried out whenever a parameter or functional change has occurred in the hearing aid device 11.
  • the determined data relating to the signal transit time are finally transmitted via a transmitting and receiving unit 20 to the second hearing aid device (not shown) of the hearing aid system.
  • the hearing aid device 11 also receives the instantaneous signal transit time by means of the transmitting and receiving unit 20 through the signal processing unit of the second hearing aid device.
  • the analysis and control unit 17 is thus the information regarding the signal propagation times of both hearing aids of the hearing aid system.
  • a signal delay is subsequently performed by the difference of the signal propagation times determined in both hearing aid devices.
  • the hearing aid device 11 comprises a delay unit designed as a shift register 21.
  • the number of delay clocks by the analysis and control unit 17 is adjustable.
  • FIG. 3 Another hearing aid is in FIG. 3 shown.
  • a hearing aid 22 shows a hearing aid according to FIG. 2 very similar construction.
  • the hearing aid 22 has a clock generator 23 with adjustable clock frequency.
  • the system clock of the hearing aid 22 is adjustable.
  • the clock frequency is increased so far to compensate for the delay difference until the delay difference is compensated. Accordingly, the clock frequency of the hearing aid device 22 is reduced so far that the signal propagation times are equalized at a shorter signal propagation time determined for the hearing aid device 22.
  • Gain values are determined and related data stored in the memory units 6 and 6 '. In a gain change in one of the two hearing aids as a result of a parameter and / or functional change (eg changing the hearing program) then the gain in the other hearing aid is adjusted accordingly.
  • an amplitude compensation can be done.
  • a test signal is advantageously fed via the measuring device 19 into the signal path and picked up again at a later point in the signal path, preferably after the signal processing unit 13.
  • the signal transmission behavior with regard to the signal amplitudes is also measured so advantageously.
  • the measurement is carried out at different frequencies.
  • a different gain value can be determined for different frequencies.
  • Data relating to the amplification values thus determined are then transmitted to the respective other hearing aid device of the hearing aid system. Subsequently, an adjustment of the signal amplitudes takes place, with at least one of the hearing aid devices changing the gain or setting filter means.
  • the adjustment of the signal amplitudes follows, taking into account the audiograms measured in both ears. Data regarding these audiograms may also be stored in the storage units 18.
  • the loudness compensation then takes place in relation to the audiograms, which ensures that, for example, a slight loudness change caused by a parameter change on a hearing aid device causes a loudness change subjectively the same for the hearing aid wearer on the other hearing aid.
  • a slight loudness change caused by a parameter change on a hearing aid device causes a loudness change subjectively the same for the hearing aid wearer on the other hearing aid.
  • slight loudness differences in the two ears of a hearing aid wearer are always perceived the same regardless of the current hearing aid settings.
  • FIG. 4 shows only a hearing aid 24 of a hearing aid system with two identically constructed hearing aids.
  • the hearing aid device 24 comprises two microphones 25 and 26 whose output signals are fed to a signal preprocessing unit 27.
  • the signal pre-processing unit 27 an A / D conversion and an electrical connection of the microphone signals to produce a directional microphone characteristic.
  • a filter bank 28 serves to split the electrical signal into frequency bands.
  • signal processing units 29A, 29B, 29C and 29D a frequency band-specific signal processing of the electrical signals in the individual frequency bands then takes place.
  • the output signals of the signal processing units 29A to 29D are added and post-processed in a signal post-processing unit 30.
  • the signal post-processing may include, for example, an end gain and D / A conversion.
  • the analog electrical output signal is converted back into an acoustic output signal by a receiver 31.
  • the individual signal processing blocks of the hearing aid device that is to say the signal preprocessing unit 27, the filter bank 28, the signal processing units 29A to 29D in the individual channels, and the signal postprocessing unit 30, are collectively referred to as signal processing unit 29 in the exemplary embodiment.
  • the hearing aid device 24 has a signal analysis and control unit 33, into which the electrical input signal before dividing into different frequency bands and the electrical output signal after passing through the signal processing units 29A to 29D.
  • the signal analysis and control unit 33 for example, feedback-related oscillations in the electrical input signal can be detected.
  • the gain may be reduced.
  • Data relating to this gain change in the relevant channel are then acquired by the signal analysis and control unit 33 and transmitted by means of a transmitting and receiving unit 34 to the second hearing aid (not shown). This receives the transmitted data and in turn lowers the gain in the corresponding channel by means of a signal analysis and control unit of the hearing aid 24 corresponding signal analysis and control unit.
  • data relating to a change in gain in the second hearing aid device of the hearing aid system can also be transmitted to the hearing aid device 24, which acts by means of the signal analysis and control unit 33 on components (for example the signal processing units 29A to 29D in the individual channels) and the gain in the hearing aid device 24 adapts accordingly.
  • the gain change can be made in both hearing aids by the same amount. Preferably, however, it takes place taking into account the individual hearing loss of the hearing device wearer and the signal transmission characteristics of the hearing aid devices. The hearing aid wearer then subjectively perceives the same gain reduction on both hearing aids. Natural loudness differences in the acoustic input signals remain largely preserved for the hearing aid wearer.
  • parameter or functional changes in hearing aids result as a result of the current hearing situation not to predetermined gain changes. This is the case, for example, with hearing aid devices in which complete sets of parameters for adaptation to different listening situations are not predetermined, but in which an adaptive and continuous adaptation of individual parameters takes place.
  • a gain change is then advantageously determined by a hearing aid internal measurement.
  • the gain change can be determined from measurements of the gain before and after a parameter change.
  • the electrical input signal and the electrical output signal in the signal analysis and control unit 33 are evaluated.
  • Both an evaluation of the total input or output signal and the electrical input and output signals of the signal processing units 29A to 29D of the individual channels is possible, depending on whether a change in the parameter affects the entire frequency range or only signal frequencies within a frequency band.
  • Analogous to the adjustment of the amplification can in a hearing aid system with two hearing aids with a schematic block diagram according to the exemplary hearing aid device 24, as in FIG. 4 represented, the signal amplitudes or the signal propagation times of the two hearing aids are adapted to each other, so that the natural directional hearing is maintained even with worn hearing aids.
  • only other signal analysis methods in the signal analysis and control unit 33 are provided for the amplitude or delay compensation over the gain compensation.
  • the amplitude compensation is preceded by amplitude or level measurements or the delay compensation phase or signal propagation time measurements on the overall signal or in the individual channels of the hearing aid device 24.
  • the compensation is then preferably carried out by adjustable filter means within the signal processing unit 29, which are set by the signal analysis and control unit 33.
  • a correlation analysis is performed for the transit time measurement.
  • the signal analysis and control unit 33 electrical signals from successive points in the signal path between the microphones 25 and 26 and the handset 31 are supplied.
  • the phase shift and thus the signal propagation time can then be determined in a simple manner.
  • the envelopes of the supplied signals are first determined in the signal analysis and control unit.
  • the comparison of the envelopes in the signal analysis and evaluation unit 33 also makes it easy to deduce the phase shift of the relevant signals and thus the signal propagation time between the points of interest in the signal path of the hearing aid device 24.
  • the measurements are carried out in each case shortly before and shortly after parameter or functional changes in the hearing aid device 24 in order to detect the resulting amplification and / or amplitude and / or signal propagation time changes in the hearing aid device 24, related data to the second hearing aid device of the hearing aid system transmit, receive there, evaluate and finally compensate for the changes.
  • the invention proposes in each case to measure signal amplitudes and / or amplifications of an electrical signal in a signal path between an input transducer and an output transducer of a hearing aid device and to transmit data relating to the measured signal amplitudes and / or amplifications to the respective other hearing aid device.
  • the signal amplitudes of the electrical signals can be matched to each other by the two hearing aids.
  • no amplitude distortion is caused by the hearing aids and the natural amplitude difference of an incident from a particular direction sound signal is maintained.
  • the direction information for the hearing aid wearer is retained.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
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  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
  • Circuit For Audible Band Transducer (AREA)

Claims (22)

  1. Procédé de réglage d'un système de prothèses auditives, comprenant au moins une première ( 1, 11, 22, 24 ) et une deuxième ( 1' ) prothèses auditives, qui comprennent respectivement au moins un convertisseur ( 2, 2', 12, 25, 26 ) d'entrée, pour la réception d'un signal acoustique d'entrée et sa transformation en un signal électrique, une unité ( 3, 3', 13, 29 ) de traitement du signal, pour le traitement du signal électrique, et un convertisseur ( 4, 4', 14, 31 ) de sortie, pour la transformation du signal électrique en un signal de sortie, et entre lesquels est prévu un trajet ( 10 ) du signal pour la transmission de données, dans lequel
    on détermine une amplification ou une variation d'amplification du signal électrique dans le trajet du signal entre le convertisseur ( 2, 12, 25, 26 ) d'entrée et le convertisseur ( 4, 14, 31 ) de sortie de la première prothèse ( 1, 11, 22, 24 ) auditive et on transmet un signal à la deuxième prothèse ( 1' ) auditive par l'intermédiaire du trajet ( 10 ) au signal, pour adapter l'amplification du signal électrique dans le trajet du signal, entre le convertisseur ( 2' ) d'entrée et le convertisseur ( 4' ) de sortie de la deuxième prothèse ( 1' ) auditive, à l'amplification déterminée du signal électrique dans la première prothèse ( 1, 11, 22, 24 ) auditive,
    caractérisé en ce que
    pour la détermination de l'amplification ou de la variation d'amplification, on détermine des amplitudes et/ou des niveaux de signal électrique.
  2. Procédé suivant la revendication 1, caractérisé en ce qu'on détermine l'amplification ou la variation d'amplification du signal électrique pour une zone partielle du trajet du signal entre le convertisseur ( 2, 12, 25, 26 ) d'entrée et le convertisseur ( 4, 14, 31 ) de sortie de la première prothèse ( 1, 11, 22, 24 ) auditive.
  3. Procédé suivant la revendication 1 ou 2, caractérisé en ce qu'on détermine automatiquement l'amplification ou une variation d'amplification du signal électrique dans la première prothèse ( 1, 11, 22, 24 ) auditive et on transmet un signal à la deuxième prothèse ( 1' ) auditive.
  4. Procédé suivant l'une des revendications 1 à 3, caractérisé en ce que, pour la détermination de l'amplification et d'une variation d'amplification, on produit un signal test, qui parcourt au moins en partie le trajet du signal entre le convertisseur ( 2, 12, 25, 26 ) d'entrée et le convertisseur ( 4, 14, 31 ) de sortie de la première prothèse ( 1, 11, 22, 24 ) auditive.
  5. Procédé suivant l'une des revendications 1 à 4, caractérisé en ce qu'on détermine l'amplification ou une variation d'amplification dans la première prothèse ( 1, 11, 22, 24 ) auditive et dans la deuxième prothèse ( 1' ) auditive et on transmet respectivement un signal à l'autre prothèse auditive.
  6. Procédé suivant l'une des revendications 1 à 5, caractérisé en ce qu'on met des moyens ( 9, 9' ) de filtrage, pour l'adaptation de l'amplification.
  7. Procédé suivant l'une des revendications 1 à 6, caractérisé en ce qu'on effectue la détermination et l'adaptation de l'amplification ou d'une variation d'amplification à des intervalles périodiques.
  8. Procédé suivant l'une des revendications 1 à 7, caractérisé en ce qu'on effectue la détermination et l'adaptation de l'amplification à la suite d'une variation de paramètre et/ou de fonction, pour au moins l'une des prothèses ( 1, 1', 11, 22, 24 ) auditives.
  9. Procédé suivant l'une des revendications 1 à 8, caractérisé en ce qu'on effectue le traitement du signal dans la première prothèse ( 1, 11, 22, 24 ) auditive et dans la deuxième prothèse ( 1' ) auditive dans plusieurs canaux de fréquence parallèles de l'unité ( 3, 13 29 ) respective de traitement du signal et on effectue la détermination et l'adaptation de l'amplification respectivement dans au moins un canal de fréquence.
  10. Procédé de réglage d'un système de prothèses auditives ayant au moins une première prothèse ( 1, 11, 22, 24 ) auditive et une deuxième prothèse ( 1' ) auditive, qui comprennent respectivement au moins un convertisseur ( 2, 2', 12, 25, 26 ) d'entrée, pour la réception d'un signal acoustique d'entrée et sa transformation en un signal électrique, une unité ( 3, 3', 13, 29 ) de traitement du signal, pour le traitement du signal électrique, et un convertisseur ( 4, 4', 14, 31 ) de sortie, pour la transformation du signal électrique en un signal de sortie, et entre lesquels est prévu un trajet ( 10 ) du signal pour la transmission de données, dans lequel
    on détermine une amplitude du signal électrique dans le trajet du signal entre le convertisseur ( 2, 12, 25, 26 ) d'entrée et le convertisseur ( 4, 14, 31 ) de sortie de la première prothèse ( 1, 11, 22, 24 ) auditive, et on transmet un signal à la deuxième prothèse ( 1' ) auditive par l'intermédiaire du trajet ( 10 ) du signal, pour l'adaptation de l'amplitude du signal électrique dans le trajet du signal, entre le convertisseur ( 2' ) d'entrée et le convertisseur ( 4' ) de sortie de la deuxième prothèse ( 1' ) auditive, à l'amplitude déterminée du signal électrique dans la première prothèse ( 1, 11, 22, 24 ) auditive,
    caractérisé en ce que, pour déterminer l'amplitude du signal, on produit un signal test, qui parcourt au moins en partie le trajet du signal entre le convertisseur ( 2, 12, 25, 26 ) d'entrée et le convertisseur ( 4, 14, 31 ) de sortie de la première prothèse ( 1, 11, 22, 24 ) auditive.
  11. Procédé suivant la revendication 10, caractérisé en ce qu'on détermine automatiquement l'amplitude du signal électrique dans la première prothèse ( 1, 11, 22, 24 ) auditive et on transmet un signal à la deuxième prothèse ( 1' ) auditive.
  12. Procédé suivant l'une des revendications 10 ou 11, caractérisé en ce qu'on détermine l'amplitude du signal dans la première prothèse ( 1, 11, 22, 24 ) auditive et dans la deuxième prothèse ( 1' ) auditive et on transmet respectivement un signal à l'autre prothèse auditive.
  13. Procédé suivant l'une des revendications 10 à 12, caractérisé en ce qu'on met des moyens ( 9, 9' ) de filtrage, pour l'adaptation de l'amplification.
  14. Procédé suivant l'une des revendications 10 à 13, caractérisé en ce qu'on effectue la détermination et l'adaptation de l'amplification ou d'une variation d'amplification à des intervalles périodiques.
  15. Procédé suivant l'une des revendications 10 à 14, caractérisé en ce qu'on effectue la détermination et l'adaptation de l'amplitude du signal à la suite d'une variation de paramètre et/ou de fonction dans au moins l'une des prothèses ( 1, 1', 11, 22, 24 ) auditives.
  16. Procédé suivant l'une des revendications 10 à 15, caractérisé en ce qu'on effectue le traitement du signal dans la première prothèse ( 1, 11, 22, 24 ) auditive et dans la deuxième prothèse ( 1' ) auditive dans plusieurs canaux de fréquence parallèles de l'unité ( 3, 13, 29 ) respective de traitement du signal et on effectue la détermination et l'adaptation des amplitudes du signal respectivement dans au moins un canal de fréquence.
  17. Système de prothèses comprenant au moins une première prothèse ( 1, 11, 22, 24 ) auditive et une deuxième prothèse ( 1' ) auditive, qui comprennent respectivement au moins un convertisseur ( 2, 2', 12, 25, 26 ) d'entrée, pour la réception d'un signal acoustique d'entrée et sa transformation en un signal électrique, une unité ( 3, 3', 13, 29 ) de traitement du signal, pour le traitement du signal électrique, et un convertisseur ( 4, 4', 14, 31 ) de sortie, pour la transformation du signal électrique en un signal de sortie, et entre lesquels est prévu un trajet ( 10 ) du signal pour la transmission de données,
    caractérisé en ce que
    la première prothèse ( 1, 11, 22, 24 ) auditive comprend des moyens de mesure et des moyens d'envoi de données se rapportant à une amplification ou à une variation d'amplification d'un signal électrique dans le trajet du signal entre le convertisseur ( 2, 12, 25, 26 ) d'entrée et le convertisseur ( 4, 14, 31 ) de sortie de la première prothèse ( 1, 11, 22, 24 ) auditive et la deuxième prothèse ( 1' ) auditive comprend des moyens de réception des données émises et des moyens d'adaptation d'une amplification, dans le trajet du signal entre le convertisseur ( 2' ) d'entrée et le convertisseur ( 4' ) de sortie de la deuxième prothèse ( 1' ) auditive, à l'amplification ou à la variation d'amplification du signal électrique dans la première prothèse ( 1, 11, 22, 24 ) auditive.
  18. Système de prothèses suivant la revendication 17, caractérisé en ce que le traitement du signal dans la première prothèse ( 1, 11, 22, 24 ) auditive et dans la deuxième prothèse ( 1' ) auditive est effectué dans plusieurs canaux de fréquence parallèles de l'unité ( 3, 3', 13, 29 ) respective de traitement du signal et au moins la première prothèse ( 1, 11, 22, 24 ) auditive comprend des moyens de détermination de l'amplification d'une variation d'amplification et au moins la deuxième prothèse ( 1' ) auditive comprend des moyens d'adaptation de l'amplification dans au moins un canal de fréquence.
  19. Système de prothèses comprenant au moins une première prothèse ( 1, 11, 22, 24 ) auditive et une deuxième prothèse ( 1' ) auditive, qui comprennent respectivement au moins un convertisseur ( 2, 2', 12, 25, 26 ) d'entrée, pour la réception d'un signal acoustique d'entrée et sa transformation en un signal électrique, une unité ( 3, 3', 13, 29 ) de traitement du signal, pour le traitement du signal électrique, et un convertisseur ( 4, 4', 14, 31 ) de sortie, pour la transformation du signal électrique en un signal de sortie, et entre lesquels est prévu un trajet ( 10 ) du signal pour la transmission de données,
    caractérisé en ce que
    la première prothèse ( 1, 11, 22, 24 ) auditive comprend des moyens de mesure et des moyens d'émission de données se rapportant à une amplitude d'un signal électrique dans le trajet du signal entre le convertisseur ( 2, 12, 25, 26 ) d'entrée et le convertisseur ( 4, 14, 31 ) de sortie de la première prothèse ( 1, 11, 22, 24 ) auditive et la deuxième prothèse ( 1' ) auditive comprend des moyens de réception des données émises et des moyens d'adaptation d'une amplitude du signal dans le trajet du signal, entre le convertisseur ( 2' ) d'entrée et le convertisseur ( 4' ) de sortie de la deuxième prothèse ( 1' ) auditive, à l'amplitude du signal électrique dans la première prothèse ( 1, 11, 22, 24 ) auditive.
  20. Système de prothèses suivant la revendication 19, caractérisé en ce que le traitement du signal dans la première prothèse ( 1, 11, 22, 24 ) auditive et dans la deuxième prothèse ( 1' ) auditive s'effectue dans plusieurs canaux de fréquence parallèles de l'unité ( 3, 3', 13, 29 ) respective de traitement du signal et au moins la première prothèse ( 1, 11, 22, 24 ) auditive comprend des moyens de détermination de l'amplitude du signal et au moins la deuxième prothèse ( 1' ) auditive comprend des moyens d'adaptation de l'amplitude du signal dans au moins un canal de fréquence.
  21. Système de prothèses suivant la revendication 19 ou 20, caractérisé en ce que la première prothèse ( 1, 11, 22, 24 ) auditive comprend au moins une unité ( 8, 8', 20, 34 ) d'émission et la deuxième prothèse ( 1' ) auditive comprend au moins une unité ( 8' ) de réception pour la transmission sans fil du signal entre la première prothèse ( 1, 11, 22, 24 ) auditive et la deuxième prothèse ( 1' ) auditive.
  22. Système de prothèses suivant l'une des revendications 19 à 21, caractérisé en ce qu'au moins la première prothèse ( 1, 11, 22, 24 ) auditive comprend des moyens de production d'un signal de test.
EP10000610.5A 2002-06-26 2003-06-13 Localisation du son avec des prothèses auditives binauriculaires Expired - Lifetime EP2180726B2 (fr)

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EP2180726B1 (fr) 2011-02-23
DK2180726T4 (en) 2015-02-16
EP1379102A3 (fr) 2009-03-04
DE10228632B3 (de) 2004-01-15
DE50313499D1 (de) 2011-04-07
EP2180726A1 (fr) 2010-04-28
US7474758B2 (en) 2009-01-06
DK1379102T3 (da) 2010-11-08
DE50312941D1 (de) 2010-09-16
DK2180726T3 (da) 2011-06-14
US20040057591A1 (en) 2004-03-25
EP1379102B1 (fr) 2010-08-04
EP1379102A2 (fr) 2004-01-07

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