EP2091268B1 - Procédé et dispositif destinés à la surveillance d'une aide auditive - Google Patents

Procédé et dispositif destinés à la surveillance d'une aide auditive Download PDF

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Publication number
EP2091268B1
EP2091268B1 EP08171802A EP08171802A EP2091268B1 EP 2091268 B1 EP2091268 B1 EP 2091268B1 EP 08171802 A EP08171802 A EP 08171802A EP 08171802 A EP08171802 A EP 08171802A EP 2091268 B1 EP2091268 B1 EP 2091268B1
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EP
European Patent Office
Prior art keywords
signal
hearing aid
hearing
monitoring
transceiver
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Active
Application number
EP08171802A
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German (de)
English (en)
Other versions
EP2091268A1 (fr
Inventor
Lilyana Joeng
Wee Haw Koo
Meng Kiang Lim
Poh Chye Lim
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Sivantos Pte Ltd
Original Assignee
Siemens Medical Instruments Pte Ltd
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Publication of EP2091268A1 publication Critical patent/EP2091268A1/fr
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Classifications

    • 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
    • H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting
    • 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
    • H04R25/30—Monitoring or testing of hearing aids, e.g. functioning, settings, battery power
    • 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
    • H04R2225/61—Aspects relating to mechanical or electronic switches or control elements, e.g. functioning
    • 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
    • H04R25/30—Monitoring or testing of hearing aids, e.g. functioning, settings, battery power
    • H04R25/305—Self-monitoring or self-testing
    • 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
    • H04R25/558—Remote control, e.g. of amplification, frequency
    • 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
    • H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
    • H04R25/603—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of mechanical or electronic switches or control elements

Definitions

  • the invention relates to a system, a portable transceiver and a method for monitoring a hearing aid and a suitable hearing aid.
  • Multichannel dynamics expansion systems allow to simulate the auditory impression produced by an individual hearing loss or by a hearing aid supply by channel-dependent amplification in several channels with additional dependence on the respective input level. This simulation process is also called auralization.
  • auralization for example, a normal hearing person with sound hearing can be given an acoustic impression of the hearing perception of a person with individual hearing loss.
  • the parameters specific to individual hearing loss or category of hearing loss Dynamic expansion systems are determined by audiometric measurements.
  • the hearing loss that occurs is very diverse and involves very different characteristics. Examples of these aspects are reduced time and frequency resolution or the so-called recruitment, which describes the changed perception of loudness of the hard of hearing.
  • the normal hearing family members can be imparted by simulation of the hearing impression of the hearing impaired with and without the assistance of the respective hearing aid. This may be used by a normal hearing person to test or empathize with the effect of hearing aid support on a hearing aid wearer, at least to a limited extent.
  • Prerequisite for the auralization is an audiometric measurement and creation of an individual audiogram.
  • Such measurements can only be made by those skilled in the art, e.g. Hearing aid operators and doctors.
  • the corresponding systems can only be operated by experts and are only economically viable for them.
  • a simulation device in which simulation data for a plurality of typical hearing loss categories and for a plurality of hearing aid models can be transmitted via a data network from or to a user.
  • simulation data for a plurality of typical hearing loss categories and for a plurality of hearing aid models can be transmitted via a data network from or to a user.
  • the measurements are only possible with access to a computer and a data network.
  • the measurement results must each be transferred to a computer system and evaluated there before they can be used for auralization. Conclusions on the hearing impression under real-time conditions and in any life situations, e.g. out of range of the computer, this will not be possible.
  • hearing aids can have different hearing programs for different noise environments. Between the different hearing programs can either automatically by the hearing aid or manually switched by the hearing aid wearer.
  • the various possible hearing programs result in an additional variety of possible variations. These would have to be taken into account in the auralization, if a respectively current hearing impression of the respective environmental situation should be conveyed taking into account the function of the hearing aid.
  • WO 2006/074655 A1 is a hearing aid system consisting of a hearing aid and a portable module for monitoring the hearing aid known.
  • the portable module may receive data from the hearing aid that represents hearing aid signal processing parameters in real time. This allows remote monitoring of the hearing aid.
  • a hearing aid in which the generation of a monitoring signal is provided.
  • the hearing aid includes a microphone, a receiver and a transmitter.
  • the transmitter transmits a monitoring signal dependent on an electrical output signal of the microphone.
  • the transceiver comprises a receiver for receiving a monitoring signal and a signal processing device of the received monitoring signal.
  • the signal processing device generates an indication signal indicating an operating state of the hearing aid or a simulation of the hearing ability of a person with hearing loss.
  • the object of the invention is to enable a monitoring of the effect of hearing aid support on a hearing aid wearer in real time and at arbitrary locations.
  • a basic idea of the invention is to provide a hearing aid monitoring system comprising the hearing aid and a portable transceiver, in which the hearing aid comprises a transmitter which transmits a monitoring signal dependent on an electrical output signal of the microphone of the hearing aid, and in which the portable one Transceiver a receiver for receiving the monitoring signal as well as a signal processing device for processing a received monitoring signal, wherein the signal processing device generates from the received monitoring signal a display signal that allows monitoring of the hearing aid by the hearing aid.
  • the indication signal makes it possible to monitor a signal state or operating state of the hearing aid.
  • the essential thing is that the display signal is dependent on a monitoring signal that is normally only available inside the hearing aid.
  • the monitoring signal is indicative of the hearing aid's supportive effect, which usually has an effect perceptible only to the hearing aid wearer. It can e.g. indicate an operating state of the hearing aid, such as the currently active hearing program, or a signal state within the hearing aid, such as a filter or gain setting, or it may reproduce the audio signal generated by the hearing aid. If the monitoring signal reproduces the audio signal generated by the hearing aid, it has already passed through the signal processing by the hearing aid. Thus, the change of the audio signal by the hearing aid no longer needs to be externally simulated, but the changed audio signal is immediately available.
  • the transceiver By sending the monitoring signal to the transceiver and the processing to the display signal information about the state of the hearing aid for monitoring the hearing aid is also available outside the same.
  • the display signal can therefore be used to the function of the hearing aid or the effect of the hearing aid without requiring a response or response from the hearing aid user.
  • the transceiver is designed as a portable device, such monitoring can take place anywhere.
  • the transceiver itself performs processing of the monitoring signal itself, causing only negligibly small time delays.
  • the generation of the display signal by the signal processing device comprises a limitation of the received monitoring signal such that restricting the restriction of the hearing of a person is simulated with hearing loss. If an electrical signal is now used as a monitoring signal, which essentially corresponds to the acoustic signal received by the microphone of the hearing aid after amplification by the hearing aid and shortly before transmission to the receiver, the auditory impression or the hearing perception can be simulated by the display signal the hearing aid is generated. As a result, the auditory perception of the hearing aid wearer can be auralized using the transceiver for normal hearing persons.
  • people in the hearing aid wearer's environment can monitor at any time whether the hearing aid wearer is receiving useful amplified acoustic signals through the hearing aid that enable hearing or understanding. For this purpose, only the display signal needs to be output by a speaker or headphones as an audible signal. In addition, people in the area can also monitor at any time whether the auditory signal amplified by the hearing aid is affected or distorted by excessive noise or other confounding factors.
  • the monitoring signal is obtained at a signal input of the receiver of the hearing aid.
  • the transceiver after receiving the monitoring signal, is provided with the signal amplified by the hearing aid, which signal is emitted by the receiver of the hearing aid to the hearing aid wearer.
  • this signal represents a particularly useful basis for the signal processing, in particular the auralization, by the transceiver.
  • the generation of the display signal by the signal processing device comprises determining a gain which depends on an audio frequency of the received monitoring signal.
  • the frequency-dependent amplification of the hearing aid can be recorded or made available in the transceiver.
  • this amplification spectrum can vary. The detection of this spectrum by the transceiver makes it possible at any time to compare with a predetermined setpoint, e.g. an audiogram of the hearing aid wearer as part of the so-called "Audiogram Matching".
  • the generation of the display signal by the signal processing device comprises determining a noise level of the received monitoring signal.
  • determining a noise level of the received monitoring signal In the case of hearing aids, operating states sometimes occur in which noise or background noise are disproportionately amplified. As a result, it may happen that the hearing perception of the hearing aid wearer is greatly distorted or disturbed, while a normal hearing perceives no increased level of noise.
  • the normal hearing person can monitor the function of the hearing aid in this way. On the one hand, it can cause the hearing aid wearer to change the hearing program, on the other hand it can take account of the limited or disturbed hearing perception of the hearing aid wearer.
  • the transceiver comprises a data memory for recording the monitoring signal.
  • the recordings may be used to subsequently analyze the function of the hearing aid or the state of the current auditory perception ability of the hearing aid wearer, for example by a physician or hearing aid acoustician.
  • the recording is started by a user.
  • the hearing aid wearer or a person in the environment can thus start the recording especially in problem situations in which the hearing aid causes only poor or limited hearing support. With the help of the recording such problem situations can be analyzed afterwards.
  • the recording takes place in dependence on the received monitoring signal.
  • the hearing aid in the monitoring signal can send the signal to start the recording so as to be able to initiate the recording itself. This allows a recording in dependence on an internal state or operating state of the hearing aid.
  • the recording is started as a function of a hearing program change notified by the monitoring signal.
  • FIG. 1 a hearing aid with portable transceiver is shown schematically.
  • Hearing aids have in principle as essential components an input transducer, an amplifier and an output transducer.
  • the input transducer is usually a sound receiver, such as a microphone, and / or an electromagnetic receiver, for. B. an induction coil.
  • the output transducer is usually used as an electroacoustic transducer, z. As miniature speaker, or as an electromechanical transducer, z.
  • B. bone conduction realized and is usually referred to as a receiver.
  • the amplifier is usually integrated in a control unit.
  • FIG. 1 illustrated by the example of a behind-the-ear hearing aid.
  • a hearing aid housing 1 for carrying behind the ear one or more microphones 2 are incorporated for receiving the sound from the environment.
  • a control unit 3 which is also integrated in the hearing aid housing 1, processes the microphone signals and amplifies them.
  • the output signal of the control unit 3 is transmitted to a receiver 4, which outputs an acoustic signal.
  • the sound is optionally transmitted via a sound tube, which is fixed with an earmold in the ear canal, to the eardrum of the device carrier.
  • the power supply of the hearing aid and in particular the control unit. 3 takes place by a likewise integrated into the hearing aid housing 1 battery. 5
  • a transmitter 6 Also integrated in the hearing aid housing 1 is a transmitter 6.
  • the transmitter 6 serves to send a monitoring signal from the hearing aid housing 1 to the outside.
  • the monitoring signal is provided by the control unit 3.
  • the activation of the transmitter 6 or of the transmission process is also performed by the control unit 3.
  • the transmitter 6 can operate, for example, on the basis of an RF radio link; when using an RF radio link advantageously no visual connection between transmitter and receiver is required.
  • the transmitter 6 may also operate on the basis of another connection, e.g. with an IR connection.
  • the hearing aid is connected via the radio link 7 with a portable transceiver 10 in connection. Via the radio link 7, the hearing aid can cause the transmission of a monitoring signal to the transceiver 10.
  • the transceiver 10 includes a receiver 8 for receiving the monitoring signal transmitted by the hearing aid.
  • a signal processing device 14 is provided which processes the received via the radio link 7 monitoring signal.
  • the transceiver 10 has an on / off switch 12, by means of which the transceiver 10 can be switched on or off.
  • a key 13 serves to start a recording of the monitoring signal received by the hearing aid.
  • a transceiver 10 integrated data memory 15 is provided for recording.
  • the data memory 15 may for example be designed as a solid-state memory; Solid-state storage work vibration-resistant and with low energy consumption. However, the data memory 15 can also be designed as a hard disk or tape storage.
  • a headphone 31 is connected via a corresponding output.
  • the headphone 31 serves to make audible monitoring signals received from the hearing aid audible to a user.
  • the volume of the headphone signal is adjustable via a volume control 11.
  • the transceiver 10 includes a battery 16 as a power supply.
  • the battery 16 may be designed, for example, as a rechargeable battery. However, non-rechargeable batteries can be used instead.
  • the monitoring signal sent by the hearing aid is used to monitor an operating or signal state of the hearing aid by means of the transceiver 10.
  • the hearing aid generates an amplified by different filter and amplification stages output signal that it outputs via the receiver 4 to the hearing aid wearer.
  • the amplification properties of the hearing aid are normally adapted to the individual hearing loss of the hearing aid wearer.
  • a distortion of the audio signal is caused by the hearing aid.
  • the audio signal should be distorted so that the distortion is compensated by the restriction of the audio signal by the individual hearing loss of the hearing aid wearer again.
  • the hearing aid should therefore ideally generate an audio signal that causes the hearing aid wearer a natural hearing impression that is as natural as possible.
  • the audio signal changed by the hearing aid can be sent to the transceiver 10 in one embodiment.
  • the transceiver 10 is information about the individual hearing loss of the Hearing aid carrier, which were detected as a so-called audiogram.
  • the signal processor 14 integrated in the transceiver 10 changes the input audio signal received as the monitor signal into an output audio signal.
  • the signal processing device 14 restricts the audio signal in such a way that the limitation is simulated by the hearing loss of the hearing aid wearer by restricting.
  • the original audio signal thus first passes through the processing by the hearing aid and after the transmission as a monitoring signal, the limiting processing by the signal processing device 14. As a result, an audio signal is generated that reproduces the hearing impression of the hearing aid wearer for normal hearing.
  • acoustic reproduction of this signal can therefore be simulated for a normal hearing the auditory impression, which receives the hearing aid wearer, which is referred to as auralization. If this auralization is performed using the monitoring signal, then the auralized monitoring signal represents just the audio signal that the hearing aid delivers to the hearing aid wearer. Any hearing program change, filter settings or similar The hearing aid need not be considered separately in the simulation, since the transmitted from the hearing aid monitoring signal has indeed gone through all such signal processing steps.
  • a largely natural and normal audio signal should result.
  • a normal hearing person can monitor whether the hearing aid wearer receives a useful acoustic signal that allows normal hearing and understanding.
  • FIG. 2 is the same hearing aid as in FIG. 1 shown schematically. about the radio connection 7 for the monitoring signal is opposite FIG. 1 slightly modified portable transceiver 20 shown.
  • the portable transceiver 20 insofar as the same reference numerals are used, also has a receiver 8 and a battery 16, a supply terminal for a power supply 17 and a data memory 15.
  • the transceiver 20 also has an on / off switch 22 and a button 23 for manually starting a recording of the monitoring signal by the data memory 15.
  • the transceiver 20 has no audio output for connecting a headphone. Instead, he has a display 21.
  • the integrated signal processing device 24 analyzes the monitoring signal received from the hearing aid in such a way that a noise level in the monitoring signal is determined.
  • the noise level is determined as a signal component of the audio signal amplified in the hearing aid and represents a background noise in the amplified acoustic signal delivered to the hearing aid wearer.
  • the transceiver 20 numerically or graphically displays a measure of this noise level on the display 21 group; the representation can be made, for example, as a number or as a line in a diagram representation of the acoustic signal spectrum.
  • the signal processing device 24 determines from the monitoring signal a frequency-dependent amplification spectrum of the hearing aid.
  • the frequency-dependent gain spectrum can be visualized numerically or graphically on the display 21. It may additionally or alternatively be analyzed comparatively with audiogram data of the hearing aid wearer stored in the transceiver 20. A result of the comparative analysis can be numerical or graphical on the Display 21 are shown. In this way, a so-called "audiogram matching" can be performed.
  • the previously discussed variants of the portable transceiver allow the monitoring of a hearing aid in real time and location-independent in a particular environment by a normal hearing in the hearing aid wearer's environment information about the current signal or operating state in the hearing aid or an impression of the current the hearing aid wearer emitted acoustic signal visually or acoustically gets displayed by the transceiver 20.
  • the normal hearing person can compare the environmental characteristics or information displayed by the transceiver 20 with the sound impression he actually perceives. In this way, the normal hearing, for example, recognize whether the hearing aid generates an unnaturally increased noise signal compared to the actual environmental situation.
  • the normal hearing person when audibly reproducing the auralized audio signal amplified by the hearing aid whether the hearing aid wearer receives an audible signal indicating that recognition of certain features, e.g. of language, at all possible. If the hearing aid wearer receives a severely distorted or impaired acoustic signal through the hearing aid that makes the recognition of speech difficult, the normal hearing person also receives a similar acoustic signal via the auralization; He is thus able to monitor subjective features such as the comprehensibility of speech.
  • a normal hearing person on the basis of monitoring by the transceiver, concludes that the hearing aid provides a severely distorted or limited signal, he or she can initiate a change of the hearing program. For this purpose, he may, for example, refer the hearing aid wearer to the required changeover. However, it is also conceivable that the normal hearing person, for example by using this one to be provided programming function of the transceiver, a conversion of the hearing aid for the hearing aid wearer.
  • a record of the monitoring signal can be started whenever problems are detected in monitoring the function of the hearing aid, e.g. strong noise or limited comprehensibility of speech.
  • a recording can be started manually for this purpose by the normal hearing.
  • the recording may also be started by the hearing aid wearer himself, e.g. whenever he feels a perception problem in a situation.
  • additional monitoring by a normal hearing in the environment is not required.
  • the recording can also be started automatically.
  • the transceiver may start recording if it detects an increased level of noise in the audio signal.
  • the recording can also be started if a predetermined frequency of hearing program changes in the hearing aid is exceeded or fallen below.
  • the signal processing device of the transceiver would have to monitor the frequency of the hearing program change, wherein the hearing program changes would be determined either by analysis of the monitoring signal or communicated by a corresponding element within the monitoring signal.
  • the monitoring signal may correspond to the audio signal amplified by the hearing aid.
  • This audio signal is tapped after processing within the hearing aid.
  • audio signal before the gain for the receiver 4 tapped by the transmitter 6 is transmitted.
  • the monitoring signal contains - in addition to the audio signal or exclusively - information about the operating state of the hearing aid, for example via the hearing program or filter settings.
  • the transceiver When appropriate information is displayed by the transceiver, it is possible to monitor, for example, or the hearing aid operates in a hearing program adapted to the respective noise environment.
  • the invention relates to a system, a transceiver and a method for monitoring a hearing aid and a hearing aid suitable for this purpose.
  • the hearing aid in this case comprises a microphone from which an acoustic input signal is detected and converted into an electrical output signal is, a receiver which generates an acoustic output dependent on an electrical output signal of the microphone, and a transmitter which transmits a signal dependent on an electrical output signal of the microphone monitoring signal.
  • the portable transceiver comprises a receiver for receiving the monitoring signal and a signal processing device for processing the received monitoring signal.
  • the signal processing device By processing the received monitoring signal, the signal processing device generates an indication signal which is acoustically limited in relation to the monitoring signal in such a way that the restriction simulates the impairment of the hearing of a person with hearing loss.
  • the transceiver can simulate the hearing impression that the hearing aid wearer is currently receiving for a normal hearing person.
  • the signal processing device can also display an operating state or signal state of the hearing aid.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Otolaryngology (AREA)
  • Neurosurgery (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Circuit For Audible Band Transducer (AREA)

Claims (22)

  1. Système de contrôle d'une prothèse auditive comprenant la prothèse auditive et un émetteur-récepteur ( 10, 20 ) portatif,
    la prothèse auditive comprenant :
    - un microphone ( 2 ) par lequel un signal d'acoustique d'entrée est détecté et est transformé en un signal électrique de sortie,
    - un récepteur ( 4 ) qui produit un signal acoustique de sortie dépendant d'un signal électrique de sortie du microphone ( 2 ),
    - un émetteur ( 6 ) qui émet un signal de contrôle dépendant d'un signal électrique de sortie du microphone ( 2 ),
    l'émetteur-récepteur ( 10, 20 ) portatif comprenant :
    - un récepteur ( 8 ) de réception du signal de contrôle,
    - un dispositif ( 14, 24 ) de traitement du signal pour le traitement du signal de contrôle reçu,
    caractérisé en ce que
    le dispositif ( 14, 24 ) de traitement du signal produit, en fonction du signal de contrôle reçu, un signal indicateur qui est limité acoustiquement par rapport au signal de contrôle de manière à ce que la limitation simule avec perte auditive la limitation de la capacité auditive d'une personne.
  2. Système suivant la revendication 1,
    caractérisé en ce que le signal de contrôle est obtenu sur une entrée de signal du récepteur ( 4 ).
  3. Système suivant l'une des revendications précédentes,
    caractérisé en ce que la production du signal indicateur par le dispositif ( 14, 24 ) de traitement du signal comprend une détermination d'une amplification dépendant de la fréquence audio du signal de contrôle.
  4. Système suivant l'une des revendications précédentes,
    caractérisé en ce que la production du signal indicateur par le dispositif ( 14, 24 ) de traitement du signal comprend une détermination d'un niveau de bruit parasite du signal de contrôle reçu.
  5. Système suivant l'une des revendications précédentes,
    caractérisé en ce que l'émetteur envoie le signal de contrôle sans câble.
  6. Système suivant l'une des revendications précédentes,
    caractérisé en ce que l'émetteur-récepteur ( 10, 20 ) est relié à un casque ( 31 ) d'écouteur pour la transformation du signal indicateur en un signal acoustique de sortie.
  7. Système suivant l'une des revendications précédentes,
    caractérisé en ce que l'émetteur-récepteur ( 10, 20 ) comprend une sortie de signal pour le transfert du signal indicateur à un dispositif indicateur acoustique et/ou optique.
  8. Système suivant l'une des revendications précédentes,
    caractérisé en ce que l'émetteur-récepteur ( 10, 20 ) comprend une mémoire ( 15 ) de données pour l'enregistrement du signal de contrôle.
  9. Prothèse auditive
    caractérisée par :
    - un microphone ( 2 ) qui détecte un signal acoustique d'entrée et le transforme en un signal électrique de sortie,
    - un récepteur ( 4 ) qui produit un signal acoustique de sortie dépendant d'un signal électrique de sortie du microphone ( 2 ),
    - un émetteur ( 6 ) qui émet un signal de contrôle dépendant d'un signal électrique de sortie du microphone ( 2 ), signal de contrôle qui est propre à être traité par un émetteur-récepteur ( 10, 20 ) suivant l'une des revendications 10 à 15.
  10. Emetteur-récepteur ( 10, 20 ) portatif de contrôle d'une prothèse auditive,
    dans lequel l'émetteur-récepteur ( 10, 20 ) comprend :
    - un récepteur ( 8 ) de réception d'un signal de contrôle par la prothèse auditive,
    - un dispositif ( 14, 24 ) du traitement du signal pour le traitement du signal de contrôle reçu,
    caractérisé en ce que
    le dispositif ( 14, 24 ) de traitement du signal produit, en fonction du signal de contrôle reçu, un signal indicateur qui est limité acoustiquement par rapport au signal de contrôle de manière à simuler avec une perte auditive, par la limitation, la capacité auditive d'une personne.
  11. Emetteur-récepteur ( 10, 20 ) portatif suivant la revendication 10,
    caractérisé en ce que la production du signal indicateur par le dispositif ( 14, 24 ) de traitement du signal comprend une détermination d'une amplification dépendant de la fréquence audio du signal de contrôle.
  12. Emetteur-récepteur ( 10, 20 ) portatif suivant l'une des revendications 10 ou 11,
    caractérisé en ce que la production du signal indicateur par le dispositif ( 14, 24 ) de traitement du signal comprend une détermination d'un niveau de bruit parasite du signal de contrôle reçu.
  13. Emetteur-récepteur ( 10, 20 ) portatif suivant l'une des revendications 10 à 12,
    qui est relié à un casque écouteur ( 31 ) pour la production de signal acoustique de sortie à partir du signal indicateur.
  14. Emetteur-récepteur ( 10, 20 ) portatif suivant l'une des revendications 10 à 13,
    comprenant une sortie de signal pour la transmission du signal indicateur à un dispositif indicateur acoustique et/ou optique.
  15. Emetteur-récepteur ( 10, 20 ) portatif suivant l'une des revendications 10 à 14,
    comprenant une mémoire ( 15 ) de données pour l'enregistrement du signal de contrôle.
  16. Procédé de contrôle d'une prothèse auditive comprenant les stades dans lesquels :
    - on émet un signal de contrôle par la prothèse auditive,
    - on reçoit le signal de contrôle par un émetteur-récepteur ( 10, 20 ),
    - on traite le signal de contrôle reçu dans l'émetteur-récepteur,
    - on produit un signal indicateur en fonction d'un traitement du signal de contrôle reçu,
    le signal indicateur étant limité acoustiquement par rapport au signal de contrôle de manière à simuler avec perte auditive, par la limitation, la limitation de la capacité auditive d'une personne.
  17. Procédé suivant la revendication 16,
    dans lequel la production du signal indicateur comprend une détermination d'une amplification dépendant d'une fréquence audio du signal de contrôle.
  18. Procédé suivant la revendication 16 ou 17,
    dans lequel la production du signal indicateur par le dispositif ( 14, 24 ) de traitement du signal comprend une détermination d'un niveau de bruit parasite du signal de contrôle reçu.
  19. Procédé suivant l'une des revendications 16 à 18, comprenant le stade supplémentaire :
    - enregistrement du signal de contrôle reçu.
  20. Procédé suivant la revendication 19,
    dans lequel un utilisateur fait commencer l'enregistrement.
  21. Procédé suivant l'une des revendications 19 ou 20,
    dans lequel on fait commencer l'enregistrement en fonction du signal de contrôle reçu.
  22. Procédé suivant l'une des revendications 19 à 21,
    dans lequel on fait commencer l'enregistrement en fonction d'un changement de programme auditif communiqué par le signal de contrôle.
EP08171802A 2008-02-13 2008-12-16 Procédé et dispositif destinés à la surveillance d'une aide auditive Active EP2091268B1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102008008898A DE102008008898B3 (de) 2008-02-13 2008-02-13 Verfahren und Vorrichtung zum Überwachen einer Hörhilfe

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EP2091268A1 EP2091268A1 (fr) 2009-08-19
EP2091268B1 true EP2091268B1 (fr) 2012-08-29

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EP (1) EP2091268B1 (fr)
DE (1) DE102008008898B3 (fr)
DK (1) DK2091268T3 (fr)

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US9812788B2 (en) 2014-11-24 2017-11-07 Nxp B.V. Electromagnetic field induction for inter-body and transverse body communication
US10015604B2 (en) 2014-05-05 2018-07-03 Nxp B.V. Electromagnetic induction field communication
US10009069B2 (en) 2014-05-05 2018-06-26 Nxp B.V. Wireless power delivery and data link
US9819395B2 (en) 2014-05-05 2017-11-14 Nxp B.V. Apparatus and method for wireless body communication
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Publication number Publication date
EP2091268A1 (fr) 2009-08-19
US8213627B2 (en) 2012-07-03
US20090202084A1 (en) 2009-08-13
DE102008008898B3 (de) 2009-05-20
DK2091268T3 (da) 2012-12-17

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