EP2104376B1 - Procédé de réduction d'occlusion active à l'aide d'une vérification de plausibilité et dispositif auditif correspondant - Google Patents

Procédé de réduction d'occlusion active à l'aide d'une vérification de plausibilité et dispositif auditif correspondant Download PDF

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Publication number
EP2104376B1
EP2104376B1 EP09153568.2A EP09153568A EP2104376B1 EP 2104376 B1 EP2104376 B1 EP 2104376B1 EP 09153568 A EP09153568 A EP 09153568A EP 2104376 B1 EP2104376 B1 EP 2104376B1
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European Patent Office
Prior art keywords
rvm
transmission function
microphone
transducer transmission
transducer
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EP09153568.2A
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German (de)
English (en)
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EP2104376A3 (fr
EP2104376A2 (fr
Inventor
Georg-Erwin Arndt
Frank Koch
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Sivantos Pte Ltd
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Siemens Medical Instruments Pte Ltd
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    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/30—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
    • H04R2460/00—Details of hearing devices, i.e. of ear- or headphones covered by H04R1/10 or H04R5/033 but not provided for in any of their subgroups, or of hearing aids covered by H04R25/00 but not provided for in any of its subgroups
    • H04R2460/05—Electronic compensation of the occlusion effect

Definitions

  • the present invention relates to a method for active occlusion reduction in a hearing device.
  • a sound in an auditory canal is recorded by a microphone with the output of a corresponding microphone signal and the recorded microphone signal is filtered by means of an adaptive filter.
  • the filtered microphone signal is fed back to an input of a receiver, which is used to output sound into the ear canal.
  • At least a portion of a transducer transfer function defined for the link from the earphone input to the ear canal to the microphone output is measured, and the adaptive filter is adjusted in response to it.
  • a hearing device here means any sound-emitting device that can be worn in or on the ear, such as a hearing aid, a headset, headphones and the like.
  • Hearing aids are portable hearing aids that are used to care for the hearing impaired.
  • different types of hearing aids such as behind-the-ear hearing aids (BTE), hearing aid with external receiver (RIC: receiver in the canal) and in-the-ear hearing aids (IDO), e.g. Concha hearing aids or canal hearing aids (ITE, CIC).
  • BTE behind-the-ear hearing aids
  • RIC hearing aid with external receiver
  • IDO in-the-ear hearing aids
  • ITE canal hearing aids
  • the hearing aids listed by way of example are worn on the outer ear or in the ear canal.
  • bone conduction hearing aids, implantable or vibrotactile hearing aids are also available on the market. The stimulation of the damaged hearing takes place either mechanically or electrically.
  • Hearing aids have in principle as essential components an input transducer, an amplifier and an output transducer.
  • the input transducer is usually a sound receiver, z. As a microphone, and / or an electromagnetic Receiver, e.g. B. an induction coil.
  • the output transducer is usually used as an electroacoustic transducer, z. As miniature speaker, or as an electromechanical transducer, z. B. bone conduction, realized.
  • the amplifier is usually integrated in a signal processing unit. This basic structure is in FIG. 1 shown using the example of a behind-the-ear hearing aid. In a hearing aid housing 1 for carrying behind the ear, one or more microphones 2 for receiving the sound from the environment are installed.
  • a signal processing unit 3 which is also integrated in the hearing aid housing 1, processes the microphone signals and amplifies them.
  • the output signal of the signal processing unit 3 is transmitted to a loudspeaker or earpiece 4, which outputs an acoustic signal.
  • the sound is optionally transmitted via a sound tube, which is fixed with an earmold in the ear canal, to the eardrum of the device carrier.
  • the power supply of the hearing device and in particular the signal processing unit 3 is effected by a likewise integrated into the hearing aid housing 1 battery. 5
  • An unpleasant effect when wearing a hearing aid is that your own voice sounds unnatural. This is due to the fact that one's own voice is led via bone conduction into the auditory canal and there causes a certain sound pressure, especially at lower frequencies. If the auditory canal is open, the corresponding pressure waves can be directed to the outside. However, if the auditory canal is closed by the hearing aid, a high sound pressure builds up here, which is called an occlusion effect and, since it is unnatural, is perceived as unpleasant.
  • a generic method for active occlusion reduction in hearing aids is from the document WO 2004/021740 A1 'and the publication WO 2006/037156 A1 known.
  • the transducer transfer function from the input of the listener via the ear canal to the output of the ear canal microphone is described in detail in the first-mentioned document. It can be determined very accurately in situ with the hearing aid as a measuring device.
  • the Transformer transfer function is complex, ie a function of magnitude and phase versus frequency.
  • a 1 a method for occlusion reduction is known.
  • an audio signal in the transmission path of the acoustic device is processed by a signal processing device and output via an output transducer arranged in the auditory canal as an acoustic signal.
  • a resulting sound signal is then detected by an ear canal microphone and fed to an adjustable loop filter disposed in a feedback loop of an occlusion reduction device of the acoustic device.
  • the output of the loop filter is coupled into the transmission path of the audio signal.
  • the occlusion reduction device is thereby controlled adaptively.
  • the measured transducer transfer function is used to determine in a computer the optimal configuration of digital signal processing for active occlusion reduction. In principle, this optimization process could also be completely automatic. However, there is the problem that in certain situations, the algorithm is irreversibly incorrectly changed, or that a lot of computing time is needed. In these situations, a manual intervention is necessary or helpful.
  • the object of the present invention is thus to further automate an adaptive implementation of an active occlusion reduction.
  • this object is achieved by a method for active occlusion reduction in a hearing device by recording a sound in an ear canal through a microphone with output of a corresponding microphone signal, filtering the microphone signal by means of an adjustable filter, feeding back the filtered microphone signal to an input of a listener who for outputting sound into the ear canal, measuring at least a spectral part of a transducer transmission function defined for the transmission path from the earphone input via the ear canal to the microphone output, and adjusting the tunable filter as a function of the transducer transmission function, the transducer transmission function being an automatic plausibility check is subjected and the adjustable filter is only changed if the transformer transfer function is plausible according to a predetermined criterion.
  • the term "adjustable" does not exclude that a Tel of the filter is adaptive, i. H. is automatically adaptable by an adaptation rule.
  • the invention provides a hearing device with active occlusion reduction comprising a receiver for sound output in an auditory canal, a microphone for recording a sound in the ear canal and for outputting a corresponding microphone signal, an adjustable filter for filtering the microphone signal, wherein the filtered microphone signal to the input a measuring device for measuring at least a spectral part of a Wandlerübertragungsfunktion which is defined for the transmission path from the entrance of the listener via the ear canal to the output of the microphone, and an adjusting means for adjusting the adjustable filter in response to the transducer transfer function, as well as a Testing device for the automatic plausibility check of the transformer transfer function, wherein the adjustable filter is changeable by the adjusting means only if the transducer transfer function is plausible according to a predetermined criterion.
  • the measured part of the transformer transfer function for the plausibility check is smoothed.
  • certain measurement uncertainties can be compensated.
  • the transducer transmission function is measured in a first frequency range and extrapolated in a second frequency range on the basis of the measured data using a model.
  • a safely measurable range can be used to estimate a less reliable area to be measured for the converter function or the plausibility check.
  • the transducer transmission function can be assessed as not plausible if, according to the predetermined criterion, its magnitude in a given frequency range is less than a predetermined threshold.
  • a blockage of the hearing device with cerumen can be detected.
  • the transducer transfer function can also be considered implausible if, according to the predetermined criterion, their phase in a predetermined frequency range is below a predetermined minimum phase. This can also be checked, for example, if one of the components involved is defective or the measurement signal was too quiet.
  • the transducer transfer function can be considered implausible if, according to the predetermined criterion, its value, including magnitude and phase, lies outside a predetermined tolerance tube in the space defined by the coordinates magnitude, phase and frequency. With such a tolerance tube, it can be detected whether the hearing device works correctly within a certain scope.
  • the tolerance tube can also be used to keep the computation time for the change in the algorithm to a certain extent. For example, if the transducer transfer function is not in a very tight tolerance tube, changing the algorithm may quickly bring about a small change in the fit of the hearing aid in the ear, and a longer computation time can be avoided.
  • FIG. 2 is an ITE hearing aid 10 shown in cross section, as it is inserted into an ear canal 11.
  • the ear canal 11 is closed by a tympanic membrane 12.
  • Between the eardrum 12 and the eardrum end of the ITE hearing aid 10 results in a closed space 13.
  • the seclusion of this space leads to the known, unpleasant Okissesions monoen.
  • the ITE hearing aid 10 has an outwardly directed microphone 14 in order to record the ambient sound (see microphone 2 of FIG. 1 ).
  • the microphone signal is forwarded to a signal processing unit 15, which processes and amplifies the signal in the usual way (compare signal processing unit 3 of FIG. 1 ).
  • the processed signal is supplied to a receiver 16 or 4, which converts the signal into a sound and emits it into the auditory canal 13. Due to the own voice, an unnaturally high noise sound pressure arises in the ear canal space 13 due to the occlusion by the ITE hearing device 10 (for example, also in the case of an earpiece of a BTE hearing device). This can be passively activated by a vent or active with the in FIG.
  • the transfer function V represents the acoustic signal path in the auditory canal space 13 from the earpiece 16 to the auditory canal microphone 17. It depends on the individual shape of the auditory canal 11, on the depth of insertion of the ITE hearing device 10, on the shell shape of the ITE device 10, but also on the degree of occlusion. However, for a particular wearing situation, this transfer function V is fixed. On the other hand, the transfer function S of the loop filter 18 is variable. It is, for example, the one in the publication WO 2004/021740 A1 adapted manner, so that the occlusion effect is reduced as much as possible.
  • the transducer transmission function of the transmission path 19 from the input of the handset 16, through the ear canal space 13 to the output of the ear canal microphone 17, ie the product RVM, measured.
  • This measured transducer transfer function RVM of the transmission path 19 is complex, ie both the amplitude and the phase of a signal is influenced during the transmission. Depending on the feature (eg hearing device is too loose), it is better to evaluate the amplitude, the phase information or other properties of the measured transducer transfer function RVM.
  • the system itself is out of order or unable to operate properly. This is the case, for example, when the handset 16 or auditory canal microphone 17 has failed, or the sound output of the handset 16 and / or the sound output of the auditory canal microphone 17 is blocked by cerumen. In such cases, the transformer transfer function is not plausible. With a Plausibility check these cases can be detected. It follows the principle of the block diagram of Fig. 4 , In this case, the transducer transfer function is measured in a first step S1. Under certain circumstances, the measurement data scatter strongly, so that according to step S2 a smoothing of the raw data of the measured transfer function is necessary. Furthermore, it may be necessary to extrapolate the measured data. For certain frequencies, especially low frequencies, it is usually difficult to determine the transducer transfer function. The accuracy for this frequency range can be increased by determining model-based parameters in a higher frequency range and applying this model in the poorly measurable frequency range.
  • the extrapolation of the transformer transfer function can be performed using the example of a first order high pass according to FIG. 3 be explained.
  • the transfer function of a first-order high pass is completely described by the corner frequency f g . If it is known that a first-order high pass is present in an unknown system to be measured, only the corner frequency f g needs to be determined.
  • the model parameter corner frequency f g is determined by taking measurement data from a frequency range classified as "reliable". In the example of FIG. 3 is the phase ⁇ and the amplitude A of a high-pass first order including the corner frequency f g shown. The data in the high-frequency range are classified as reliable and therefore the amplitude A and the phase ⁇ is drawn there with a solid line.
  • the parameter corner frequency f g is determined via the variation of the corner frequency f g of a parameterizable high-pass transfer function so that the measured data coincide as far as possible with the correctly parameterized high-pass transfer function.
  • the high-pass transfer function thus found is now used for the non-reliably measurable, here the low, frequency ranges (see dashed amplitude). and phase history in FIG. 3 ).
  • the measured and supplemented by extrapolation transformer transfer function for the plausibility check can now be evaluated.
  • step S4 the phase of the transducer transfer function can be extracted.
  • the phase can not assume any values at low frequencies in the range of 100 Hz.
  • a minimum phase is given at low frequencies.
  • the typical value of the minimum phase can be specified depending on the converter. If there is a lower measured phase than the minimum phase, the measurement result itself does not have to be in order. For example, the measurement signal may have been too quiet if the S / N ratio was temporarily too low. In this case, the measurement must be repeated with a louder measurement signal in order to obtain a valid measurement result.
  • the measured transducer transfer function according to step S1 or a transfer function prepared according to step S2 can also be evaluated directly, which is indicated by the arrow S5 in FIG FIG. 4 is indicated. In most cases, however, it is favorable to perform a normalization of the transfer function at an arbitrary frequency for the evaluation, which is indicated by step S6 in FIG FIG. 4 is indicated.
  • the data obtained from steps S3 to S6 can now be compared, for example, with certain threshold values or evaluated on the basis of specific criteria in accordance with step S7.
  • the phase can be compared to a minimum phase.
  • the amount of the transfer function should not be below a minimum amount for a larger frequency range.
  • the normalized measured or extrapolated transfer function which in fact represents a spatial curve in the amplitude-phase frequency space, can be compared, for example, with a tolerance tube around this curve. If the tolerance hose is never left, the measured transfer function is accepted as valid or plausible.
  • a decision is made as to whether the transfer function is valid or not valid or plausible or not plausible. Only after decided plausibility is the occlusion reduction optimized by adapting the loop filter S.
  • the advantage of this approach is that only meaningful transducer transfer functions are used for determining the optimal configuration of the signal processing (in particular the loop filter).
  • the optimization algorithm is thus protected from converging into an unfavorable state by an inappropriate transducer transfer function.
  • this leads to a limitation of the solution space for the algorithm and thus to a shortening of the computation time.
  • an indication of the cause of the fault can be given.
  • the indication of a leak can be given if the cutoff frequency of the high-pass transfer function is relatively high.

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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 (7)

  1. Procédé de réduction d'occlusion active dans une prothèse auditive par
    - enregistrement d'un son dans un conduit ( 13 ) auditif par un microphone ( 17 ) avec émission d'un signal de microphone correspondant,
    - filtrage du signal de microphone à l'aide d'un filtre ( 18 ) réglable,
    - rétroinjection du signal de microphone filtré à une entrée d'un écouteur ( 16 ), qui sert à l'émission de son dans le conduit ( 13 ) auditif,
    - mesure d'au moins une partie spectrale d'une fonction ( RVM ) de transfert de transducteur, qui est définie pour la section ( 19 ) de transmission allant de l'entrée de l'écouteur ( 16 ) à la sortie du microphone ( 17 ) en passant par le conduit ( 13 ) auditif, et
    - réglage du filtre ( 18 ) réglable en fonction du résultat de la mesure mentionnée de la fonction ( RVM ) de transfert de transducteur,
    caractérisé en ce que
    - on soumet la fonction de transfert de transducteur à un contrôle de vraisemblance automatique et
    - on ne modifie le filtre ( 18 ) réglable que si la fonction ( RVM ) de transfert de transducteur est vraisemblable suivant un critère donné à l'avance.
  2. Procédé suivant la revendication 1, dans lequel on lisse la partie spectrale mesurée de la fonction ( RVM ) de transfert de transducteur pour le contrôle de vraisemblance.
  3. Procédé suivant la revendication 1 ou 2, dans lequel on mesure la fonction ( RVM ) de transfert de transducteur dans une première plage de fréquence et on l'extrapole ainsi dans une deuxième plage de fréquence.
  4. Procédé suivant l'une des revendications précédentes, dans lequel la fonction ( RVM ) de transfert de transducteur n'est pas vraisemblable si, conformément au critère donné à l'avance, sa valeur absolue est, dans une plage de fréquence donnée à l'avance, plus petite qu'un seuil donné à l'avance.
  5. Procédé suivant l'une des revendications précédentes, dans lequel la fonction ( RVM ) de transfert de transducteur n'est pas vraisemblable si, conformément au critère donné à l'avance, sa phase est, dans une plage de fréquence donnée à l'avance, inférieure à une phase minimum donnée à l'avance.
  6. Procédé suivant l'une des revendications 1 à 3, dans lequel la fonction ( RVM ) de transfert de transducteur n'est pas vraisemblable si, conformément au critère donné à l'avance, sa valeur, incluant sa valeur absolue et sa phase, sont en-dehors d'un canal de tolérance donné à l'avance dans l'espace qui est défini par les coordonnées valeur absolue, phase et fréquence.
  7. Prothèse auditive ayant une réduction d'occlusion active, comprenant
    - un écouteur ( 16 ) pour l'émission de son dans un conduit ( 13 ) auditif,
    - un microphone ( 17 ) d'enregistrement d'un son dans le conduit ( 13 ) auditif et d'émission d'un signal de microphone correspondant,
    - un filtre ( 18 ) réglable pour le filtrage du signal de microphone, le signal de microphone filtré étant rétroinjecté à l'entrée de l'écouteur ( 16 ),
    - un dispositif de mesure d'au moins une partie spectrale d'une fonction ( RVM ) de transfert de transducteur, qui est définie pour la section ( 19 ) de transversale allant de l'entrée de l'écouteur ( 16 ) à la sortie du microphone ( 17 ) en passant par le conduit ( 13 ) auditif, et
    - un dispositif de réglage du filtre ( 18 ) réglable en fonction du résultat de la mesure mentionnée de la fonction ( RVM ) de transfert de transducteur,
    caractérisée par
    - un dispositif de contrôle automatique de la vraisemblance de la fonction ( RVM ) de transfert de transducteur, dans laquelle
    - le filtre ( 18 ) réglable ne peut être modifié par le dispositif de réglage que si la fonction ( RVM ) de transfert de transducteur est vraisemblable suivant un critère donné à l'avance.
EP09153568.2A 2008-03-20 2009-02-25 Procédé de réduction d'occlusion active à l'aide d'une vérification de plausibilité et dispositif auditif correspondant Active EP2104376B1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102008015264A DE102008015264A1 (de) 2008-03-20 2008-03-20 Verfahren zur aktiven Okklusionsreduktion mit Plausibilitätsprüfung und entsprechende Hörvorrichtung

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EP2104376A2 EP2104376A2 (fr) 2009-09-23
EP2104376A3 EP2104376A3 (fr) 2010-06-09
EP2104376B1 true EP2104376B1 (fr) 2014-11-26

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US (1) US8553917B2 (fr)
EP (1) EP2104376B1 (fr)
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DK (1) DK2104376T3 (fr)

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DE102008015264A1 (de) 2009-10-01
US20090238387A1 (en) 2009-09-24
EP2104376A3 (fr) 2010-06-09
DK2104376T3 (en) 2015-03-09
US8553917B2 (en) 2013-10-08
EP2104376A2 (fr) 2009-09-23

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