EP2104376A2 - Procédé de réduction d'occlusion active à l'aide d'une vérification de plausibilité et dispositif auditif approprié - Google Patents

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

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Publication number
EP2104376A2
EP2104376A2 EP09153568A EP09153568A EP2104376A2 EP 2104376 A2 EP2104376 A2 EP 2104376A2 EP 09153568 A EP09153568 A EP 09153568A EP 09153568 A EP09153568 A EP 09153568A EP 2104376 A2 EP2104376 A2 EP 2104376A2
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EP
European Patent Office
Prior art keywords
transfer function
rvm
microphone
transducer
ear canal
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.)
Granted
Application number
EP09153568A
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German (de)
English (en)
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EP2104376A3 (fr
EP2104376B1 (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; ELECTRIC HEARING AIDS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Electric hearing aids
    • 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; ELECTRIC HEARING AIDS; 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 transmission path 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.
  • 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 portion 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 in response to the transducer transmission function, the transducer transmission function undergoing an automatic plausibility check and the adjustable filter is only changed if the transducer transfer function is plausible according to a predetermined criterion.
  • the term "adjustable" does not exclude that a Tel of the filter is adaptive, ie 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 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, and a testing device for the automatic plausibility check of the transducer transfer function, wherein the adjustable filter is only changeable by the adjusting means when the transducer transfer function according to a vo criterion is plausible.
  • 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. So that can For example, a safely measurable range can be used to estimate a less secure area to be measured for the converter function or the plausibility check.
  • the transducer transmission function can be assessed as not plausible if 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 its phase is within a predetermined frequency range 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 may be considered implausible if its value, including magnitude and phase, is outside a given tolerance tube in the space defined by the coordinates, 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 computing time for the change of the algorithm within a certain range. 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 by varying the cut-off frequency f g of a parameterizable high-pass transfer function such 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)
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 true EP2104376A2 (fr) 2009-09-23
EP2104376A3 EP2104376A3 (fr) 2010-06-09
EP2104376B1 EP2104376B1 (fr) 2014-11-26

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US (1) US8553917B2 (fr)
EP (1) EP2104376B1 (fr)
DE (1) DE102008015264A1 (fr)
DK (1) DK2104376T3 (fr)

Cited By (3)

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Publication number Priority date Publication date Assignee Title
WO2014198306A2 (fr) 2013-06-12 2014-12-18 Phonak Ag Procédé de fonctionnement d'un dispositif auditif capable d'une commande d'occlusion active, et dispositif auditif ayant une commande d'occlusion active ajustable par l'utilisateur
WO2014198307A1 (fr) 2013-06-12 2014-12-18 Phonak Ag Procédé de mise en fonctionnement d'un dispositif auditif capable d'un contrôleur actif d'occlusion et dispositif à contrôle actif d'occlusion
WO2018103899A1 (fr) * 2016-12-09 2018-06-14 Sivantos Pte. Ltd. Procédé de surveillance de la performance électro-acoustique d'un dispositif auditif et dispositif auditif

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US20050058313A1 (en) * 2003-09-11 2005-03-17 Victorian Thomas A. External ear canal voice detection
US9219964B2 (en) 2009-04-01 2015-12-22 Starkey Laboratories, Inc. Hearing assistance system with own voice detection
US8477973B2 (en) * 2009-04-01 2013-07-02 Starkey Laboratories, Inc. Hearing assistance system with own voice detection
EP2378788A3 (fr) 2010-04-13 2012-01-25 Sony Corporation Dispositif et procédé de génération sonore intra-auriculaire
EP2640095B2 (fr) 2012-03-15 2020-11-18 Sonova AG Méthode d'appareillage d'une aide auditive avec contrôle actif de l'occlusion à un utilisateur
US10129668B2 (en) * 2013-12-31 2018-11-13 Gn Hearing A/S Earmold for active occlusion cancellation
DE102016011719B3 (de) 2016-09-30 2017-09-07 Rheinisch-Westfälische Technische Hochschule Aachen Aktive Unterdrückung des Okklusionseffektes in Hörhilfen
IT201700066873A1 (it) * 2017-06-15 2018-12-15 Maurizio Casaluce Apparecchio acustico e metodo per ridurre l'autofonia
CN113056924A (zh) * 2018-11-14 2021-06-29 （株） 奥菲欧 具有关键词唤醒功能的智能带麦耳机
EP3896990A4 (fr) * 2018-12-14 2022-01-26 Sony Group Corporation Dispositif et système acoustique
DE102020209906A1 (de) 2020-08-05 2022-02-10 Sivantos Pte. Ltd. Verfahren zum Betrieb eines Hörgeräts und Hörgerät
DE102020209907A1 (de) 2020-08-05 2022-02-10 Sivantos Pte. Ltd. Verfahren zum Betrieb eines Hörgeräts und Hörgerät

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WO2004021740A1 (fr) 2002-09-02 2004-03-11 Oticon A/S Procede de lutte contre les effets d'occlusion
WO2006037156A1 (fr) 2004-10-01 2006-04-13 Hear Works Pty Ltd Systeme et procede de reduction d'occlusion acoustiquement transparente

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WO2004021740A1 (fr) 2002-09-02 2004-03-11 Oticon A/S Procede de lutte contre les effets d'occlusion
WO2006037156A1 (fr) 2004-10-01 2006-04-13 Hear Works Pty Ltd Systeme et procede de reduction d'occlusion acoustiquement transparente

Cited By (3)

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Publication number Priority date Publication date Assignee Title
WO2014198306A2 (fr) 2013-06-12 2014-12-18 Phonak Ag Procédé de fonctionnement d'un dispositif auditif capable d'une commande d'occlusion active, et dispositif auditif ayant une commande d'occlusion active ajustable par l'utilisateur
WO2014198307A1 (fr) 2013-06-12 2014-12-18 Phonak Ag Procédé de mise en fonctionnement d'un dispositif auditif capable d'un contrôleur actif d'occlusion et dispositif à contrôle actif d'occlusion
WO2018103899A1 (fr) * 2016-12-09 2018-06-14 Sivantos Pte. Ltd. Procédé de surveillance de la performance électro-acoustique d'un dispositif auditif et dispositif auditif

Also Published As

Publication number Publication date
DK2104376T3 (en) 2015-03-09
EP2104376A3 (fr) 2010-06-09
DE102008015264A1 (de) 2009-10-01
US8553917B2 (en) 2013-10-08
EP2104376B1 (fr) 2014-11-26
US20090238387A1 (en) 2009-09-24

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