WO2011107545A2 - Procédé pour régler un dispositif d'audition à effet directif - Google Patents

Procédé pour régler un dispositif d'audition à effet directif Download PDF

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Publication number
WO2011107545A2
WO2011107545A2 PCT/EP2011/053191 EP2011053191W WO2011107545A2 WO 2011107545 A2 WO2011107545 A2 WO 2011107545A2 EP 2011053191 W EP2011053191 W EP 2011053191W WO 2011107545 A2 WO2011107545 A2 WO 2011107545A2
Authority
WO
WIPO (PCT)
Prior art keywords
directivity
hearing device
hearing
signals
microphones
Prior art date
Application number
PCT/EP2011/053191
Other languages
German (de)
English (en)
Other versions
WO2011107545A3 (fr
Inventor
Jens Hain
Tobias Wurzbacher
Original Assignee
Siemens Medical Instruments Pte. Ltd.
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Application filed by Siemens Medical Instruments Pte. Ltd. filed Critical Siemens Medical Instruments Pte. Ltd.
Publication of WO2011107545A2 publication Critical patent/WO2011107545A2/fr
Publication of WO2011107545A3 publication Critical patent/WO2011107545A3/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
    • H04R25/40—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
    • H04R2430/00—Signal processing covered by H04R, not provided for in its groups
    • H04R2430/03—Synergistic effects of band splitting and sub-band processing

Definitions

  • the invention relates to a method for adjusting a hearing device, which is designed to generate a directivity based on signals from at least two microphones.
  • hearing device is understood here in particular a hearing aid.
  • the term includes other portable acoustic devices such as headsets, 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, 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 shown in FIG. 1 using the example of a behind-the-ear hearing device.
  • a hearing aid housing 1 for carrying behind the ear are one or more microphones 2 to Built-in sound recording from the environment.
  • a signal ⁇ processing unit 3 which is also integrated into the hearing aid housing 1 processes the microphone signals and ver ⁇ strengthens 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 through a sound tube which is fixed with a otoplasty in the auditory canal, the eardrum of the wearer übertra ⁇ gene also as Dome (Dome - dome) Instead of an otoplastic.
  • Designated domed earpiece used ⁇ to that upon insertion in the ear canal adapts to a shape of the same. In the context of open fitting, a so-called tip (tip) is often used, which has a particularly narrow shape so that it does not impair ventilation of the auditory canal.
  • the Energyver ⁇ supply of the hearing aid and in particular the Signalverar ⁇ beitungsech 3 by a likewise integrated into the hearing ⁇ housing 1 battery 5.
  • hearing aids with at least two microphones it is possible to use a transit time difference of sound waves between the microphones to a directivity when detecting a sound to produce. This allows a processing of a sound signal depending on which direction the sound is hit on the hearing.
  • a useful signal is often the signal of that
  • a directional characteristic of the hearing device can be determined. In such a directional characteristic is indicated which damping a
  • Sound signal in dependence learns from which direction Rich ⁇ the sound hits the hearing.
  • To create a directivity signals of individual microphones can be delayed against each other and then summed who ⁇ .
  • a period of time is usually set, which corresponds to a transit time of a sound between the microphones.
  • Delay period T as T d / c where d is the microphone distance and c is the speed of sound in air.
  • the adaptive system uses the standard least squares algorithm.
  • the parameters b and ß ß f representing the relationship between the in ⁇ Neren and the external time delay, is in the so-
  • the ⁇ -value pairs are determined for a number of frequencies.
  • the object of the present invention is to improve a directivity in a hearing device.
  • a suitable hearing device may be configured to generate a directivity based on signals from at least two microphones.
  • signal components of different frequencies are delayed by a predetermined period of time in at least one of the signals.
  • Different time periods here are set for at least two signal ⁇ shares. This makes it possible in an advantageous manner a value dependent on a frequency of a signal component propagation time difference between the at least two microphones in producing the directivity for each of the frequency components separated from brideen ⁇ .
  • the invention is based on the finding that the effective transit time of a sound between two microphones is also dependent on a wavelength of the sound, i. from the frequency of
  • Sound signal depends.
  • the frequency dependence is determined here by the propagation paths that result when wearing the hearing device on the body, eg on the head, a device carrier between two microphones.
  • the time periods are in this case predetermined, ie they must not be estimated during a Be ⁇ drive of the hearing when the hearing device is used by the device carrier in everyday life.
  • the directional effect generated by means of the delay is therefore sta ⁇ table.
  • the hearing device can be set for at least one of the signal components, a period of time which is different from the duration of the sound, which the sound benö ⁇ taken to get directly from one of the two microphones to the other.
  • T d / c.
  • the directivity can be achieved by superimposing a cardioid polar pattern and an anti-cardioid
  • Directional characteristics are generated.
  • a special design of the hearing device is obtained when in a proper wearing position of the hearing device on a person's head results in a directivity, in which the anti-cardioid directional characteristic for at least one of the signal components a notch for a straight ahead. direction of the head.
  • a notch here represents a local minimum in a graph for a directional characteristic, by which a dependence of a damping of a sound signal from an angle of incidence of the associated
  • a delay which results in a directional characteristic with a notch for the straight-line orientation, can be determined, for example, by means of a numerical method.
  • a hearing device in another hearing device, means are provided by which optionally two signals can be interchanged along signal paths in the hearing device.
  • a hearing device can be adapted individually to a person in a simple manner with the aid of standardized methods.
  • a Hörvor ⁇ direction can be adjusted, which is laid out ⁇ for generating a directivity on the basis of signals from at least two microphones being provided for generating the directivity, that in at least one of the signals signal components un- ter Kunststoffaji frequencies around delayed for a certain period of time.
  • the following three steps are performed for each of the signal components of different frequency.
  • a value for a directional parameter for adjusting the directivity is determined, so that the directivity for a predetermined direction satisfies a predetermined criterion.
  • the directional parameter can be changed until a level of a microphone signal generated by a frontal sound impinging on the hearing device from the front is minimized or maximized.
  • a time period for the delay of the signal component is determined on the basis of the value determined for the directional parameter.
  • the specific time duration in the hearing device is set for later operation.
  • d stands again for the distance between the two microphones and c for the Sound Velocity ⁇ speed in air.
  • the method can be developed in an advantageous manner if, for determining the value, the hearing device is attached to a head in a designated wearing position and the hearing device is sonicated from the predetermined direction.
  • the hearing device can be individu ⁇ ell customize for a particular user of the hearing device.
  • FIG. 1 shows a schematic representation of a structure of a
  • Signal processing for generating a directional character derives from a Kardioid- and an anti-cardioid directional characteristic
  • Anti-Kardioidzweig in a hearing aid according to the prior art results when worn on a head
  • FIG. 6 shows a Richtcharakerizing an anti-Kardioidzweigs of the hearing aid of Figure 5 as it results in accordance with the He ⁇ invention when the hearing aid is ge ⁇ bear on a head.
  • FIG. 2 shows a signal flow graph for processing signals of two microphones 10, 12 of a hearing aid (not further shown in FIG. 2).
  • an output signal 14 is generated from the microphone signals, in which signal components of a sound signal to the microphone signals are attenuated depending on which direction a corresponding sound is hit on the microphones 10, 12.
  • the hearing aid can be, for example, a behind-the-ear hearing aid.
  • a hearing aid is worn in a proper manner, for example, by being fastened with a carrying hook to an auricle of an ear of a device wearer.
  • the microphones 10 and 12 are on a line arranged one behind the other, that a from the front of a direction 16 on the head of the equipment carrier meeting
  • the signals of the two microphones 10, 12 are superimposed by summers 20, 22 with each other.
  • one of the signals is delayed by a time period T by means of a delay element 24, 26 with respect to the respective other signal.
  • the time delay T corresponds to a transit time difference of a sound from the direction 16 between the microphones 10, 12.
  • one of the two signals is inverted at the summers 20 and 22, which is indicated in FIG. 2 by a minus sign.
  • the signal of the Anti-Kardioidzweigs 30 is weighted by means of a Mul ⁇ tiplizierers 32 with a weighting factor a.
  • the weighting factor a represents a directional parameter by which the output signal 14 is a directional effect can be ⁇ represents.
  • the signals of the branches 28 and 30 are superimposed by a summer 34, whereby the output signal 14 is formed.
  • the signal of the anti-cardioid branch 30 can be used to determine a power of noise from an environment of the hearing aid.
  • a directional characteristic 36 is shown in FIG. 3, as it results in the case of the hearing device explained in conjunction with FIG. 2 in a free field, ie in a reflection-free environment, for the anti-cardioid branch 30.
  • a notch 38 For a sound from a zero-degree direction, ie from the direction 16 frontally from the front, results in a notch 38, which indicates a particularly strong suppression of a signal from this direction.
  • a directional characteristic 40 is shown which results for the anti-cardioid branch 30 when the hearing aid of FIG. 2 is worn on a person's head.
  • a notch 42 corresponding to the notch 38 is formed at an incident direction of about fifty degrees.
  • a signal of sound striking the hearing aid from the zero-degree direction (direction 16) is attenuated by less than 20 dB. The attenuation is dependent on a frequency of each processed signal components.
  • curves 40 ', 40 ", 40"' of the directional characteristic 40 are shown for frequencies 1000 Hz, 2500 Hz and 5000.
  • the different curves 40 ', 40'',40' give 'by differences in the Ausbreitungspfa ⁇ between the microphones 10 and 12, a sound for the individual signal components.
  • the actual terms of the Sig ⁇ nalanmaschine are frequency dependent. Due to the displacement of the notch away from the zero-degree direction, the performance and Robust ⁇ standardized algorithms reduce for generating an adaptive directivity by which, for example, the value for the weighting factor a in an operation of the hearing aid can be controlled, and also by Algorithms for a spatial Störgerauschredukti ⁇ on.
  • the hearing device can be a behind-the-ear hearing device, in which the microphones 48 and 50 are arranged in the same way as has already been described in connection with the hearing device explained in FIG.
  • the direction 16 is the zero-degree direction.
  • the microphones 48, 50 are arranged at a distance d from one another in the hearing device.
  • the signal processing graph shown in FIG. 5 represents a processing that can be performed in one of a plurality of frequency channels of the hearing device.
  • Results in the same Signal Let ⁇ phen for the other frequency channels values for the time period T 0 and the weighting factor a for the individual frequency channels may differ from each other.
  • the time period T 0 for the individual frequency channels is adjustable. Before a device wearer can wear the hearing aid intended for him in everyday life, the hearing aid must be adjusted by determining an optimum value for the time duration T 0 for each frequency channel and setting it for the respective delay element 44, 46. The adjustment can be made for example by a hearing care professional.
  • the hearing device is first attached to the ear of the equipment wearer in the appropriate manner. Subsequently, the hearing ⁇ device by means of a sound source, such as a loudspeaker ⁇ , with a sound from the zero-degree direction of Hearing aid, ie from the direction 16, sonicated.
  • a sound source such as a loudspeaker ⁇
  • Sound may be noise, for example.
  • a value for the weighting factor a is determined, for which an optimum value of, for example, a signal power for one of the branches of the signal flow graph results.
  • Such optimal value may be for example a minimum or a maximum signal power ⁇ .
  • the algorithm can be beispielswei ⁇ se be a numerical optimization method or an algorithm, as it is also used for adapting the weighting factor a for generating an adaptive directionality.
  • Adaptive directional microphone structures of this type are well known in the art.
  • the time duration T 0 is calculated for each frequency channel.
  • T 0 (la) / (l + a) * d / c ⁇ ver applies in the example of FIG.
  • the formula can be used or numerical mapping rules can be determined by experiments.
  • the durations T 0 for the individual frequency channels are subsequently stored in the hearing device so that they are available for later operation of the hearing device as the time periods T 0 for the delay elements 44 and 46. For the individual frequency channels so can different time delays. During operation of the hearing aid by the wearer, the values for time delays may remain unchanged.
  • FIG 6 a directional characteristic of the hearing aid 52 is shown which is obtained for an anti Kardioidzweig 30 ', when the hearing aid is worn by the device ⁇ carrier for which the time period T 0 has been set in the manner described.
  • the directional characteristic 52 includes curves 52 ', 52'',52''' for the frequencies 1000 Hz, 2500 Hz and 5000 Hz. For the zero-degree direction, ie for a sound from the direction 16, results in the directional pattern 52 as compared to the directional pattern 40 significantly greater attenuation.
  • Richtcha ⁇ rakterizing 52 influences the useful signal are reduced to the calculation ⁇ voltage of the interference power as one based on Signal of the anti-Kardioidzweigs 30 'can be performed.
  • time duration T 0 has been optimized for a single implement carrier. However, it is also possible to determine an average value for an optimal time duration T 0 for several test persons and to use this as the standard value for hearing aids. Instead of volunteers, of course, a dummy head can be used. Furthermore, it is possible for a single frequency channel different values for the time delay in the tarry ⁇ approximately element 44 on the one hand and to the delay element 46 on the other hand set.
  • the hearing aid is also particularly robust if the weighting factor a is changed during operation of the hearing aid by means of an algorithm for generating an adaptive directivity.
  • sound signals from sources of interference in a front hemisphere of the hearing aid may also less disturb the computation of the weighting factor a to produce a desired characteristic.

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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)
  • Headphones And Earphones (AREA)
  • Circuit For Audible Band Transducer (AREA)

Abstract

L'invention concerne un procédé pour régler un dispositif d'audition à effet directif. Les dispositifs d'audition comportant deux ou plusieurs microphones (48, 50) permettent du fait de la différence des temps de parcours des ondes sonores entre les microphones (48, 50) de régler une caractéristique directive désirée. Pour cela, pour un traitement correct des signaux des microphones, le temps de parcours réel des ondes sonores entre les microphones doit être connu. Si on porte un dispositif d'audition sur le corps, par exemple fixé à la tête, ceci peut conduire à une modification du temps de parcours effectif. Ceci peut atténuer un effet directif statique d'un dispositif d'audition. L'objectif de la présente invention est d'améliorer un effet directif d'un dispositif d'audition. Pour cela, on propose selon l'invention une audioprothèse dans laquelle un effet directif est produit à partir de signaux d'au moins deux microphones (48, 50), et pour cela, pour au moins un des signaux, des quotes-parts de signal de différentes fréquences sont retardées d'une durée prédéterminée (To), des durées (To) différentes étant fixées pour au moins deux quotes-parts de signaux. L'invention convient en particulier aux audioprothèses.
PCT/EP2011/053191 2010-03-05 2011-03-03 Procédé pour régler un dispositif d'audition à effet directif WO2011107545A2 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE102010010416.7 2010-03-05
DE102010010416 2010-03-05

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WO2011107545A2 true WO2011107545A2 (fr) 2011-09-09
WO2011107545A3 WO2011107545A3 (fr) 2012-08-16

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Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE60316474T2 (de) 2002-12-20 2008-06-26 Oticon A/S Mikrofonsystem mit richtansprechverhalten

Family Cites Families (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
AU3414200A (en) * 2000-03-31 2000-06-26 Phonak Ag Method for providing the transmission characteristics of a microphone arrangement and microphone arrangement
EP1773100A1 (fr) * 2005-10-04 2007-04-11 Siemens Audiologische Technik GmbH Adaptation d'un microphone directionnel à des effets de longue durée
EP1994788B1 (fr) * 2006-03-10 2014-05-07 MH Acoustics, LLC Reseau de microphones directionnels reducteur de bruit

Patent Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE60316474T2 (de) 2002-12-20 2008-06-26 Oticon A/S Mikrofonsystem mit richtansprechverhalten

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