EP2699020B1 - Procédé et dispositif de détermination d'un facteur d'amplification d'un appareil de correction auditive - Google Patents

Procédé et dispositif de détermination d'un facteur d'amplification d'un appareil de correction auditive Download PDF

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Publication number
EP2699020B1
EP2699020B1 EP13171684.7A EP13171684A EP2699020B1 EP 2699020 B1 EP2699020 B1 EP 2699020B1 EP 13171684 A EP13171684 A EP 13171684A EP 2699020 B1 EP2699020 B1 EP 2699020B1
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EP
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Prior art keywords
signal
strength
wyi
weight
wxi
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EP13171684.7A
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German (de)
English (en)
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EP2699020A2 (fr
EP2699020A3 (fr
Inventor
Eghart Fischer
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Sivantos Pte Ltd
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Sivantos Pte Ltd
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Priority claimed from DE102013201043.5A external-priority patent/DE102013201043B4/de
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Publication of EP2699020A3 publication Critical patent/EP2699020A3/fr
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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
    • H04R25/40—Arrangements for obtaining a desired directivity characteristic
    • H04R25/407—Circuits for combining signals of a plurality of transducers
    • 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
    • H04R2225/43—Signal processing in hearing aids to enhance the speech intelligibility
    • 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
    • H04R2460/01—Hearing devices using active noise cancellation
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R3/00—Circuits for transducers, loudspeakers or microphones
    • H04R3/005—Circuits for transducers, loudspeakers or microphones for combining the signals of two or more microphones

Definitions

  • the invention relates to a method for determining an amplification factor of a hearing aid.
  • the method comprises the following steps: determining a strength of an approximately undisturbed signal, determining a strength of a noise signal, determining a strength of a disturbed signal, and generating the amplification factor.
  • the strength of the approximately undisturbed signal and / or the strength of the interfering signal and / or the strength of the disturbed signal may each be, for example, a moving average of an instantaneous power, a moving average of an effective value or a moving average of a time course of another amplitude value (for example a sound pressure, a voltage or a current signal).
  • the moving average can be generated for example by means of a sampling of a voltage signal and a subsequent filtering by means of a low-pass filter.
  • the voltage signal may be a voltage signal that is generated, for example, by means of a half-wave rectifier or by means of a bridge rectifier.
  • the rectified voltage signal can also be fed (without sampling) directly to low-pass filtering.
  • the invention relates to a corresponding device.
  • 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 handset (RIC: receiver in the canal ) and in-the-ear hearing aids (IDO), for example Concha hearing aids or canal hearing aids (ITE, CIC).
  • BTE behind-the-ear hearing aids
  • RIC hearing aid with external handset
  • IDO in-the-ear hearing aids
  • ITE canal hearing aids
  • the hearing aids listed by way of example are on the outer ear or in the auditory canal carried.
  • 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, 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.
  • 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
  • a poor signal-to-noise ratio is understood here and below to mean a small ratio Xpi / Ypi between the determined magnitude Xpi of the approximately undisturbed signal Xi and the determined magnitude Ypi of the disturbed signal Yi.
  • the invention has for its object to provide an alternative method by which a reliable determination of a gain factor can be performed even with poor signal-to-noise ratios.
  • this object is achieved in that the generation of the amplification factor comprises the following steps: determining a strength of an approximately undisturbed signal, determining a strength of a spurious signal, determining a strength of a disturbed signal and generating the amplification factor.
  • Generating the gain factor comprises the steps of: forming a counter, the counter comprising a sum having a first sum component formed by multiplying the magnitude of the approximately undisturbed signal by a first weight, and a second sum component obtained by multiplying the magnitude forming the denominated signal with a second weight, forming a denominator comprising as a first summand the counter and as a second summand the strength of the interfering signal, and determining the amplification factor by forming a quotient of the numerator divided by the denominator.
  • the device is prepared for carrying out the method according to the invention.
  • the range of values of the amplification factor (under boundary conditions, which are explained in the figure description) to a numerically good manageable range (for example, between 0.5 and 1) implicitly and in a continuously differentiable manner can be limited.
  • a continuously differentiable manner is meant that a non-continuously differentiable dependence of the gain on a magnitude of the distorted signal and / or on a strength of the interfering signal is avoided.
  • the method also comprises the step of determining a strength of a disturbed signal and in that the forming of the counter comprises adding up the first summation component and a second summation component which is formed by multiplying the strength of the disturbed signal by a second weighting Influence of the approximately undisturbed signal on a signal sink increases when a good signal-to-noise ratio is present, and the influence of the approximately undisturbed signal on the signal sink is reduced if there is a poor signal-to-noise ratio.
  • the signal sink can be, for example, the ear of a hearing aid wearer, for whom an acoustic signal is generated in consideration of the disturbed signal.
  • the second weighting is determined by subtracting the first weighting from a constant value. In this way, an attenuation of one of the two signals is adapted to an attenuation of the other signal by means of an operation which can be carried out quickly and efficiently with minimal effort.
  • a further embodiment provides that the first weighting by means of a handle by hand is adjustable.
  • the first weighting can be adjustable by means of an automatic control.
  • the automatic control or regulation can set the first weighting, for example, as a function of an evaluation of the approximately undisturbed signal and / or the interference signal and / or the disturbed signal.
  • the automatic control or regulation it is also conceivable for the automatic control or regulation to set the first weighting as a function of an evaluation of the first signal defined below and / or of the second signal defined below and / or of the third signal defined below. Accordingly, the feature combinations described for adjustability of the first weighting can alternatively or additionally also be provided for adjustability of the second weighting.
  • the approximately undisturbed signal is a band-limited part of a first signal and / or that the interference signal is a band-limited part of a second signal and / or that the disturbed signal is a band-limited part of a third signal.
  • the method specifically those signal components of the disturbed signal which have a poor signal-to-noise ratio can be attenuated, while those signal components of the disturbed signal which have a good signal-to-noise ratio are attenuated or are not attenuated.
  • the interfering signal is detected from a second signal received from a second spatial direction that deviates from a first spatial direction from which a first signal is received from which the approximate one undisturbed signal is derived.
  • signals are preferably supplied to the signal sink which are received from the first spatial direction, with signals received from the second direction being suppressed.
  • the second spatial direction is opposite to the first spatial direction.
  • a preferred embodiment results when the perturbed signal is derived from a third signal received with a directional selectivity that is less than a directional selectivity with which the second signal is received.
  • the disturbed signal is derived from a third signal which is received with a directional selectivity which is less than a directional selectivity with which the first signal is received.
  • the first, second and / or third signal is an acoustic signal which is detected by means of a hearing aid.
  • the method can be used to improve a benefit of a hearing aid.
  • FIG. 1 shows in a simplified block diagram the structure of a hearing aid according to the prior art.
  • Hearing aids have in principle as essential components one or more input transducers, an amplifier and an output transducer.
  • the input transducer is usually a sound receiver, such as a microphone, or an electromagnetic receiver, such as an induction coil.
  • the output transducer is usually as an electro-acoustic transducer, eg miniature speaker or handset, or as an electromechanical transducer, eg bone conduction, realized.
  • the amplifier is usually integrated in a signal processing unit.
  • FIG. 1 illustrated by the example of a behind-the-ear hearing aid 1.
  • two microphones 3 and 4 are installed for receiving the sound from the environment.
  • a signal processing unit 5 which is also integrated into the hearing aid housing 2, processes the microphone signals and amplifies them.
  • the output signal of the signal processing unit 5 is transmitted to a loudspeaker or earpiece 6, which outputs an acoustic signal. If necessary, the sound is transmitted to the eardrum of the hearing aid wearer via a sound tube, which is fixed in the auditory canal with an earmold.
  • the power supply of the hearing device and in particular of the signal processing unit 5 is effected by a likewise integrated into the hearing aid housing 2 battery. 7
  • FIG. 2 Device 10 for determining a gain factor of a hearing aid shown has three inputs EYi, ESSi, EXi for each microphone signal Y ', SS', X '.
  • the first input EXi is provided for a bandpass-limited microphone signal Xi which is received from a direction RX in which there is an acoustic useful source QX whose sound signal X "is to be supplied to an ear 20 of a hearing aid wearer in a conditioned form.
  • Si is provided for a bandpass-limited microphone signal SSi, which is received from a direction RSS, in which there is an acoustic interference source QSS, whose sound signal
  • the third input EYi is for a bandpass-limited microphone signal Yi which is received with an omnidirectional characteristic, ie one or more sound sources QZ, QSS, which are in one or more arbitrary indeterminate directions which are not coincide with the direction RX.
  • the double microphone preferably comprises a first and a second microphone, each having an omnidirectional receiving characteristic.
  • the two microphones are arranged at a distance of 6 to 10 mm in the direction RX one behind the other.
  • the units FX, FY and FSS are filter banks which are prepared to convert the respective microphone signal X ', Y' or SS 'into a plurality of band-limited input signals Xi, Yi, SSi which are adjacent in the frequency domain.
  • the letter i in the reference numbers indicates that the circuit parts between the filter banks FSS, FX, FY and the frequency multiplexer C are executed several times.
  • the signal strength detectors PXi, PYi and PSSi are prepared from the band-limited input signals Xi, Yi, SSi each to determine a signal strength Xpi, Ypi, SSpi.
  • At least one of the units FX, FY, FSS or each of the units FX, FY, FSS can be designed to convert the microphone signal X ', Y' or SS 'supplied thereto in the time domain by means of a Fourier transformer into an amplitude distribution density function over the frequency and to sample their signal strength in (preferably equidistant) frequency intervals.
  • the apparatus 10 comprises a differential adder DAi which adds up the two signal strengths Xpi and Ypi and provides the added signal strength value as a first intermediate signal Zi (counter Zi). Prior to adding the signal strengths of the two signal strengths Xpi, Ypi, the differential adder DAi applies a first weight WXi to the signal strength Xpi of the approximately undisturbed signal Xi and a second weight WYi to the signal strength Ypi of the disturbed signal Yi.
  • the differential adder DAi has an input EWi for a weighting signal WXSi whose value WXi can be set manually and / or whose value WXi is set by means of an automatic control or regulation (not shown in the figures).
  • the first weight WXi corresponds to the value of the weighting signal WXSi.
  • the device 10 comprises a summer Si, which adds the first intermediate signal Zi (counter Zi) and the signal strength of the interference signal SSi. The result is a second intermediate signal ZS2i.
  • a zero-avoidance unit NVEi converts the second intermediate signal ZS2i into a zero-set third intermediate signal Ni (denominator Ni). This avoids a subsequent division by zero.
  • the device 10 comprises a quotient generator QBi, the one Amplification factor Qi (quotient Qi) by dividing the first intermediate signal Zi (counter Zi) by the third intermediate signal Ni (denominator Ni) generated.
  • the device 10 comprises a multiplier Mi for applying the gain Qi to the approximately undisturbed signal Xi and forming a frequency band specific output Xai. Furthermore, the device 10 comprises a frequency multiplexer C for combining the frequency band-specific output signals Xai of the different frequency bands into a synthesized output signal Xa '.
  • the synthesized output signal Xa ' is supplied to a sound generator SG, which converts the synthesized output signal Xa' into a corresponding sound signal Xa ", which is supplied to an ear 20 of a hearing aid wearer.
  • the 3, 4 . 5 show in dB (ie in logarithmic representation) for different values of the weighting signal WXi such as a gain Qi of a first level difference V1 between a signal strength Xpi of the approximately undisturbed signal Xi and a signal strength Ypi of the disturbed signal Yi and a second level difference V2 between a signal strength SSpi of the interfering signal SSi and the signal strength Ypi of the disturbed signal Yi.
  • the first weight WXi is set so that the signal strength Ypi of the perturbed signal Yi does not enter into the gain Qi.
  • the first weighting WXi is set such that approximately the signal strength Ypi of the undisturbed signal Xi is not included in the gain factor Qi.
  • the first weighting WXi is set so that the signal strength Xpi, Ypi of the approximately undisturbed signal Xi and of the perturbed signal Yi are each half in the amplification factor Qi.
  • the gain Qi is high regardless of the weight WXi in any case when the second level difference V2 is low.
  • the gain Qi is high regardless of the weight WXi in each case in which the first level difference V1 is low and at the same time the second level difference V2 is high.
  • the weight WXi thus has a significant effect on the gain Qi only if the second level difference V2 is not small. In this case, the larger the first level difference V1, the greater the effect on the gain Qi.
  • the method 100 for determining an amplification factor of a hearing aid shown comprises the following steps: In a first step 110, a signal strength Xpi of an approximately undisturbed signal Xi is determined. In a second step 120, a signal strength SSpi of an interference signal SSi is determined. In a third step 130, a signal strength Ypi of a disturbed signal Yi is determined. In a fourth step 140, a gain factor Qi is generated. The generation 140 of the amplification factor Qi comprises the following substeps. In a first sub-step 142, a counter Zi is formed.
  • the counter Zi comprises a sum having a first sum component formed by multiplying the signal strength Xpi of the approximately undisturbed signal Xi by a first weight WXi, and a second sum component obtained by multiplying the signal strength Ypi of the distorted signal Yi by a second weight WYi is formed.
  • a denominator Ni is formed which comprises the counter Zi as a first summand and the signal strength SSpi of the interference signal SSi as a second summand.
  • a gain factor Qi is determined by forming a quotient Qi from the counter Zi divided by the denominator Ni.
  • the second weighting WYi is determined by subtracting the first weighting WXi from a constant value.
  • first weighting WXi can be set manually by means of a handle and / or if the first weighting WXi can be set by means of an automatic control or and / or if the second weighting WYi can be set manually by means of a handle and / or when the second weighting WYi is adjustable by means of an automatic control.
  • the approximately undisturbed signal Xi is a band-limited part of a first microphone signal X 'and / or if the interference signal SSi is a band-limited part of a second microphone signal SS' and / or if the disturbed signal Yi is a band-limited part of a third microphone signal Y '.
  • the interference signal SSi is determined from a second signal SS ', which is received from a second spatial direction RSS, which deviates from a first spatial direction RX, from which a first signal X' is received from which the approximately undisturbed signal Xi is derived.
  • the first spatial direction RX is opposite to the second spatial direction RSS.
  • the disturbed signal Yi is derived from a third signal Y 'which is received with a directional selectivity which is less than a directional selectivity with which the second signal SS' is received.
  • the first X ', second SS', and / or third signal Y ' is typically an audible signal detected by a hearing aid 10.
  • WYi is set to a value greater than 0.1, preferably greater than 0.2, more preferably greater than 0.4. Alternatively or additionally, WYi is set to a value which is less than 0.9, preferably greater than 0.8, more preferably less than 0.6.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Soundproofing, Sound Blocking, And Sound Damping (AREA)
  • Circuit For Audible Band Transducer (AREA)
  • Control Of Amplification And Gain Control (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)

Claims (10)

  1. Procédé (100) de détermination d'un facteur d'amplification (Qi) d'un appareil de correction auditive, dans lequel le procédé (100) comprend les étapes consistant à :
    - déterminer (110) une intensité (Xpi) d'un signal (Xi) pratiquement non perturbé,
    - déterminer (120) une intensité (SSpi) d'un signal de perturbation (SSi),
    - déterminer (130) une intensité (Ypi) d'un signal perturbé (Yi),
    - générer (140) le facteur d'amplification (Qi), caractérisé en ce que la génération (140) du facteur d'amplification (Qi) comprend les étapes consistant à :
    - établir (142) un compteur (Zi), dans lequel le compteur (Zi) comprend une somme ayant une première composante de somme qui est établie par multiplication de l'intensité (Xpi) du signal pratiquement non perturbé (Xi) par une première pondération (WXi), et comprend une deuxième composante de somme qui est établie par multiplication de l'intensité (Ypi) du signal perturbé (Yi) par une deuxième pondération (WYi) ;
    - établir (144) un dénominateur (Ni) qui comprend, en tant que premier opérande, le compteur (Zi) et, en tant que deuxième opérande, l'intensité (SSpi) du signal de perturbation (SSi) ;
    - déterminer (146) le facteur d'amplification (Qi) en établissant un quotient (Qi) du compteur (Zi) divisé par le dénominateur (Ni).
  2. Procédé (100) selon la revendication 1, caractérisé en ce que la deuxième pondération (WYi) est obtenue par soustraction de la première pondération (WXi) à une valeur constante.
  3. Procédé (100) selon la revendication 1 ou 2, caractérisé en ce que la première pondération (WXi) peut être réglée à la main au moyen d'une manette et/ou en ce que la première pondération (WXi) peut être réglée au moyen d'une unité de commande ou d'une unité de régulation automatique et/ou en ce que la deuxième pondération (WYi) peut être réglée à la main au moyen d'une manette et/ou en ce que la deuxième pondération (WYi) peut être réglée au moyen d'une unité de commande ou d'une unité de régulation automatique.
  4. Procédé (100) selon l'une quelconque des revendications 1 à 3, caractérisé en ce que le signal pratiquement non perturbé (Xi) est une partie à bande limitée d'un premier signal (X') et/ou en ce que le signal de perturbation (SSi) est une partie à bande limitée d'un deuxième signal (SS') et/ou en ce que le signal perturbé (Yi) est une partie à bande limitée d'un troisième signal (Y').
  5. Procédé selon l'une quelconque des revendications 1 à 4, caractérisé en ce que le signal de perturbation (SSi) est déterminé à partir d'un deuxième signal (SS') qui est reçu en provenance d'une deuxième direction spatiale (RSS) qui est différente d'une première direction spatiale (RX) en provenance de laquelle le premier signal (X') est reçu, dont le signal pratiquement non perturbé (Xi) est dérivé.
  6. Procédé selon la revendication 5, caractérisé en ce que la deuxième direction spatiale (RSS) est opposée à la première direction spatiale (RX).
  7. Procédé selon l'une quelconque des revendications 1 à 6, caractérisé en ce que le signal perturbé (Yi) est dérivé d'un troisième signal (Y') qui est reçu avec une sélectivité directionnelle qui est plus faible qu'une sélectivité directionnelle avec laquelle le deuxième signal (SS') est reçu.
  8. Procédé selon l'une quelconque des revendications 1 à 7, caractérisé en ce que le signal perturbé (Yi) est dérivé d'un troisième signal (Y') qui est reçu avec une sélectivité directionnelle inférieure à une sélectivité directionnelle avec laquelle le premier signal (X') est reçu.
  9. Procédé selon l'une quelconque des revendications 5 à 8, caractérisé en ce que le premier signal (X'), le deuxième signal (SS') et/ou le troisième signal (Y') est un signal acoustique qui est détecté au moyen d'un appareil de correction auditive (10).
  10. Dispositif, caractérisé en ce que le dispositif (10) est conçu pour mettre en oeuvre un procédé (100) selon l'une quelconque des revendications 1 à 9.
EP13171684.7A 2012-08-17 2013-06-12 Procédé et dispositif de détermination d'un facteur d'amplification d'un appareil de correction auditive Active EP2699020B1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US201261684166P 2012-08-17 2012-08-17
DE102013201043.5A DE102013201043B4 (de) 2012-08-17 2013-01-23 Verfahren und Vorrichtung zum Bestimmen eines Verstärkungsfaktors eines Hörhilfegeräts

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EP2699020A2 EP2699020A2 (fr) 2014-02-19
EP2699020A3 EP2699020A3 (fr) 2015-04-15
EP2699020B1 true EP2699020B1 (fr) 2016-04-13

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AU3414200A (en) * 2000-03-31 2000-06-26 Phonak Ag Method for providing the transmission characteristics of a microphone arrangement and microphone arrangement
DK2537351T3 (da) * 2010-02-19 2020-12-07 Sivantos Pte Ltd Fremgangsmåde til den binaurale laterale opfattelse for høreinstrumenter

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