EP2919485B1 - Transmission d'un signal à bruits de vent réduits à temps de latence diminué - Google Patents

Transmission d'un signal à bruits de vent réduits à temps de latence diminué Download PDF

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Publication number
EP2919485B1
EP2919485B1 EP15156739.3A EP15156739A EP2919485B1 EP 2919485 B1 EP2919485 B1 EP 2919485B1 EP 15156739 A EP15156739 A EP 15156739A EP 2919485 B1 EP2919485 B1 EP 2919485B1
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Prior art keywords
wind
filter
signals
signal
transmission signal
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EP15156739.3A
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German (de)
English (en)
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EP2919485A1 (fr
Inventor
Marc Aubreville
Eghart Fischer
Homayoun Kamkar Parsi
Stefan Petrausch
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Sivantos Pte Ltd
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Sivantos 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
    • H04R3/00—Circuits for transducers, loudspeakers or microphones
    • H04R3/002—Damping circuit arrangements for transducers, e.g. motional feedback circuits
    • 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
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2410/00—Microphones
    • H04R2410/07—Mechanical or electrical reduction of wind noise generated by wind passing a microphone
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
    • H04R25/552—Binaural

Definitions

  • the present invention relates to a method for generating a transmission signal based on a wind-disturbed useful signal, and which is transferable from a hearing device to an external device.
  • a first and a second microphone signal is generated from the disturbed by wind useful signal in the hearing, and the two microphone signals are filtered with a filter system having a latency, whereby first filter signals are obtained. From the first filter signals parameters are determined with which a portion of the wind from the two microphone signals can be reduced.
  • the present invention relates to a hearing device for correspondingly generating a transmission signal.
  • a hearing device here means any device which can be worn in or on the ear and produces a sound stimulus, in particular a hearing device, 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, 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
  • Wind noise is a problem for hearing aids and especially for behind-the-ear hearing aids or for hearing aids with an external microphone.
  • Wind noise is a very strong frequency-dependent effect, resulting in FIG. 2 can be removed.
  • the acoustic power in the lower and middle frequencies of the audible spectrum increases in the first place. Due to the frequency dependence, it is advantageous to estimate the wind over the frequency, for example using Wiener filters, and to correspondingly reduce the amplitude of the frequency bands.
  • Such noise reduction requires a filter bank or a configurable high-pass filter.
  • Filter banks for channel-specific processing in hearing aids usually use between 16 and 48 channels, but this also entails a high latency period in the relevant signal. Because of the large number of channels namely steep filters are required, which require a certain filter length, resulting in correspondingly long delays.
  • a high-resolution filter bank with, for example, 48 channels has the advantage that wind can be detected precisely. In fact, such wind detection is already the first step in monaural wind noise reduction.
  • the object of the present invention is therefore to find a way to reduce wind noise in a hearing system, in which a signal transmission of useful sound is necessary.
  • this object is achieved by a method for generating a transmission signal which is based on a useful signal disturbed by wind, and which can be transmitted from a hearing device to an external device by generating a first and a second microphone signal from the useful signal disturbed by wind the hearing device, filtering the two microphone signals with a first filter system having a first latency, whereby first filter signals are obtained, and obtaining a wind disturbed transmission signal from one of the two microphone signals or from the two microphone signals independently of the first filter signals, and reducing a portion of Winds from the wind disturbed transmission signal, so that the transmission signal is obtained.
  • the invention provides a hearing device for generating a transmission signal based on a wind-disturbed useful signal, and which is transferable from the hearing device to an external device, with a microphone device for generating a first and a second microphone signal from the wind disturbed A useful signal in the hearing device, a first filter system having a first latency, for filtering the two microphone signals, whereby first filter signals are obtained, and a processing means for obtaining a wind disturbed transmission signal from one of the two microphone signals or from the two microphone signals independently of the first filter signals and a wind noise reducing means for reducing a proportion of the wind from the wind disturbed transmission signal so that the transmission signal is obtained.
  • a wind noise reduction is carried out in a separate branch which is provided parallel to the main signal processing branch of the hearing device and in which the transmission signal is generated.
  • parameters to be used for filtering out wind noise are obtained by a first filter system, and the signal intended for transmission is obtained by a second filter system, which has a shorter latency than the first filter system.
  • the wind noise reduction parameters are then applied to the lesser-latency signal so that a wind-noise-free signal is available for transmission after a shortened latency period.
  • the small difference in time between the wind-laden signal available after the second filter system and the parameters obtained via the first filter system plays practically no role.
  • the respective microphone signal when filtering with the first filter system, is divided into more channels than when filtering with the second filter system. Due to this higher number of channels in the first filter system, wind can be detected more reliably and accurately. For the wind reduction per se, the splitting of the signal (s) into fewer channels is sufficient.
  • Applying the parameters to the second filter signals may be accomplished by multiplying every other filter signal by a factor that depends on the parameters.
  • the parameters are gains with which the second filter signals are easy to multiply.
  • each factor for the multiplication can be formed by mean value assignment, minimum value assignment or maximum value assignment. Basically, an assignment of several channels is necessary in each case to one channel, if after the first filter system with more channels is expected than after the second filter system. It can then be assigned to a resulting channel, an average of the input channels, a minimum value of the input channels or a maximum value of the input channels. Depending on the choice of assignment, the degree of wind reduction can be influenced.
  • both microphone signals can be filtered by the second filter system, and intermediate signals which initially arise can be combined by a beam shaping device to form the second filter signals.
  • the first filter system may on average have longer filters than the second filter system. Although these longer filters lead to a sharper separation of the channels and thus to a better detectability of the wind, they also mean a longer latency.
  • the output of the first filter system can also have more channels than the second filter system. With more channels, a higher frequency resolution can be achieved, which is beneficial for wind detection, but in turn increases latency.
  • the output side of the second filter system may have two to ten channels and the first filter system may have fifteen channels on the output side.
  • the second filter system has, for example, four channels and the first filter system has 16 or 48 channels. This makes it possible, on the one hand, to achieve a high-quality wind detection after the first filter system and, on the other hand, a qualitatively sufficient wind reduction according to the second filter system.
  • a binaural hearing aid system can be provided in a particularly advantageous manner in which a first hearing device with the above-mentioned properties is formed and in which a second hearing device represents the external device.
  • a wind-reduced signal with low latency can be transmitted from one hearing aid to the other side of the head to the other hearing aid.
  • a special application is the binaural wind noise suppression or reduction. It is checked on which side of the head there are larger wind noise artifacts. From the side that is less affected by the wind, signals are then transmitted to the other side. Due to the typical wind spectrum (cf. FIG. 2 ) this transmission can be restricted to frequencies below a cutoff frequency.
  • wind artefacts are additionally reduced.
  • the wind noise on the receiver side of the transmission could be detected for this purpose.
  • this presupposes that two microphone signals are available after transmission in such a high quality that the fine structure of the signals necessary for the wind detection is obtained. So that would be one two-channel transmission of high quality necessary.
  • this requires such a high transmission data rate that it is advisable to reduce wind noise even before transmission.
  • frequency dependent or frequency independent wind intensity values or wind noise attenuation parameters could also be transmitted to the other hearing aid to reduce the amplitudes in the affected frequency bands (or in low frequency bands in general).
  • additional data must be transmitted at a sufficiently high refresh rate, which in turn seems impractical.
  • a reduction in the latency is achieved by generating a wind-reduced signal (transmission signal) to be transmitted in a parallel branch 11 independently of a main processing branch 10 in which the acoustic output signal of the hearing device is generated.
  • a wind-disturbed transmission signal is provided in the parallel branch 11 by one or more microphones.
  • the reduction of the wind fraction in the wind disturbed transmission signal may occur in the parallel branch 11 independently of the main processing branch 10.
  • a wind reduction (device direction) already present in the main processing branch 10 (in the following short: branch 10) is used for the wind reduction in the parallel branch 11.
  • the processing takes place, for example, in 16 or 48 channels, while the processing in the second branch takes place only with significantly fewer channels, for example with one channel or four channels.
  • the data from the first branch 10 are then used to clear wind noise in the second branch 11.
  • the second branch 11 with the few channels could be used to detect the wind intensity, it is more favorable in terms of computational effort to take the values of an existing wind noise liberator available in several channels (here 48) and these many channels on the few channels in the second branch 11 map.
  • Such mapping is associated with less computational effort and represents a less complex transformation with mean or maximum value operations of the corresponding higher resolution channels in the first branch 10.
  • the exemplary hearing device has as input transducer means two microphones 12 and 13.
  • the microphones 12 and 13 absorb the ambient sound, which includes, for example, wind noise. From this they produce analog microphone signals which are each fed to an analog / digital converter 14, 15. Optionally, can also be dispensed with such an analog / digital conversion. After the digital conversion, a digital first microphone signal ms1 results here for the first microphone 12 and a second digital microphone signal ms2 for the second microphone 13.
  • the first microphone signal ms1 is fed to a first high-resolution filter bank 16.
  • the second microphone signal ms2 is fed to another high-resolution filter bank 17.
  • Both filter banks 16, 17 split their input signals here into 48 channels (possibly also a different number).
  • the two high-resolution filter banks 16 and 17 can be combined to form a first filter system.
  • This first filter system or the filter banks 16 and 17 deliver first filter signals fs1 having a first latency, which is for example 5 ms. The latency is so high because the first filter system is high resolution and provides many channels or the individual filters of the first filter system are relatively long in order to achieve high selectivity.
  • All the first filter signals fs1 from both microphone channels are supplied to a wind noise analysis unit 18, 22 having a wind noise evaluation unit 18 and an imaging device 22, with which wind noise is detected, for example, by correlation analysis.
  • a gain is calculated for each of the 48 channels here, so that a multi-channel amplification signal v results on the output side. In a channel, for example, the gain is reduced if there is a lot of wind noise.
  • Both the multi-channel amplification signal v and the first filter signals fs1 are typically further processed in the hearing device, but this is described in detail in US Pat FIG. 3 not shown.
  • the multi-channel amplification signal v is used to free the entire signal, namely the first filter signals fs1, from wind and to produce a corresponding output signal.
  • the generation of a transmission signal for a preferably wireless transmission is of primary interest.
  • the second branch 11 a broadband transmission signal u is now generated, which is freed from wind noise or in which at least wind noise is reduced.
  • the second branch 11 has a shorter latency than the first branch 10.
  • the first microphone signal ms1 and / or the second microphone signal ms2 as wind-disturbed transmission signal is optionally supplied to a second filter system, which supplies second filter signals fs2, in the second branch 11.
  • the optional second filter system consists only of a single small filter bank (such as the filter bank 19 in FIG. 3 ), which splits the signal into, for example, four channels, wherein the signals in the channels together represent the second filter signals fs2.
  • the first digital microphone signal ms1 a first, here four-channel filter bank 19 and the second digital microphone signal ms2 a second, here four-channel filter bank 20 is supplied.
  • intermediate signals zs1 and zs2, which are fed to a beam-shaping device 21, are first of all produced at the filter banks 19 and 20. This forms the second filter signals fs2, which are present in four channels in parallel.
  • the filter banks 19 and 20 split the respective signals only a few (here four) channels, their latency is lower than that of the filter banks 16 and 17 in the first branch 10.
  • the individual filters can also be shorter because a less steep slope is required. This also results in a shorter latency. This can be dispensed with a sub-sampling, which is why the filter banks 19 and 20 can also be referred to as time-domain filter banks.
  • the gain values v obtained in the first branch 10 in here 48 channels should in the present example now be applied to the second filter signals fs2 obtained with shortened latency and present in four channels.
  • the mapping is made to four parameters fp.
  • the respective second filter signal fs2 is multiplied by the associated parameter fp in each channel. Because of the higher latency in the first branch 10, the parameters fp originate from wind events which lie before the event time of the second filter signals fs2. However, this is not relevant for wind noise.
  • the second filter signals fs2 acted upon by the parameters fp are supplied to a synthesis filter bank, in the simplest case an adder 24, which forms a broadband transmission signal u from this.
  • a transmitting device 25 receives the transmission signal in order to send it wirelessly or by wire to an external device, in particular another hearing device.
  • the imaging device 22 for example, the first two of the 48 input channels are mapped to the first of the four output channels. Furthermore, the next four of the 48 input channels are mapped to the second of the four output channels, and so on.
  • a non-uniform mapping takes place here that corresponds to the typical wind spectrum (cf. FIG. 2 ).
  • the wind is reduced in a signal generated from at least two microphone signals prior to transmission to another hearing aid or accessory.
  • an additional delay or latency is avoided by using a filter bank or a filter bank system with low delay for the signal transmission parallel to the multi-channel filter bank for the usual processing.
  • additional computational effort can be saved by using the commonly available multi-channel wind noise estimates (and corresponding gains) for mapping to a smaller filter bank or filter bank system (which can also be used for directional microphone purposes).

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

Claims (6)

  1. Procédé pour générer un signal de transmission (u) basé sur un signal utile perturbé par le vent, et pouvant être transmis par un dispositif d'aide auditive à un appareil externe à celui-ci, en
    - générant un premier et un deuxième signal de microphone (ms1, ms2) à partir du signal utile perturbé par le vent dans le dispositif d'aide auditive,
    - filtrer les deux signaux de microphone (ms1, ms2) au moyen d'un premier système de filtrage (16, 17) présentant un premier temps de latence, de manière à obtenir des premiers signaux filtrés (fs1),
    - obtenir un signal de transmission perturbé par le vent à partir de l'un des deux signaux de microphone ou à partir des deux signaux de microphone indépendamment des premiers signaux filtrés (fs1),
    - réduire une partie correspondant au vent dans le signal de transmission perturbé par le vent de manière à obtenir le signal de transmission,
    - déterminer des paramètres (fp) à partir des premiers signaux de filtrage (fs1), au moyen desquels une partie correspondant au vent peut être réduite dans les deux signaux de microphone (ms1, ms2),
    - filtrer le signal de transmission perturbé par le vent (ms1, ms2) au moyen d'un deuxième système de filtrage (19, 20, 21) présentant un temps de latence inférieur au premier temps de latence, de manière à obtenir des deuxième signaux de filtrage (fs2) en tant que base pour le signal de transmission,
    - appliquer les paramètres (fp) déterminés à partir des premiers signaux de filtrage (fs1) aux deuxièmes signaux de filtrage (fs2) pour réduire la partie correspondant au vent,
    dans lequel le signal de transmission (u) est généré dans une branche parallèle (11) indépendamment de la branche de traitement principale (10) dans laquelle un signal de sortie acoustique du dispositif d'aide auditive est généré.
  2. Procédé selon la revendication 1, dans lequel l'application des paramètres (fp) au deuxièmes signaux de filtrage (fs2) est effectuée en multipliant chaque deuxième signal de filtrage (fs2) par un facteur qui dépend des paramètres (fp).
  3. Procédé selon l'une quelconque des revendications précédentes, dans lequel les deux signaux de microphone (ms1, ms2) sont filtrés par le deuxième système de filtrage (19, 20, 21) et en ce que les signaux intermédiaires qui en résultent (zs1, zs2) sont tout d'abord combinés en les deuxièmes signaux de filtrage (fs2) par un dispositif de formation de faisceau (21).
  4. Dispositif d'aide auditive destiné à générer un signal de transmission (u) qui est basé sur un signal utile perturbé par le vent et qui peut être transmis par le dispositif d'aide auditive à un appareil externe à celui-ci, comportant
    - un dispositif à microphone (12, 13) destiné à générer un premier et un deuxième signal de microphone (ms1, ms2) à partir du signal utile perturbé par le vent dans le dispositif d'aide auditive,
    - un premier système de filtrage (16, 17) présentant un premier temps de latence, destiné à filtrer les deux signaux de microphone (ms1, ms2) de manière à obtenir des premiers signaux de filtrage (fs1),
    - un dispositif de traitement destiné à obtenir un signal de transmission perturbé par le vent à partir de l'un des deux signaux de microphone ou à partir des deux signaux de microphone indépendamment des premiers signaux de filtrage (fs1),
    - un dispositif de réduction de bruit du vent destiné à réduire une partie correspondant au vent dans le signal de transmission perturbé par le vent de manière à obtenir le signal de transmission,
    dans lequel le dispositif d'aide auditive est conçu pour générer le signal de transmission (u) dans une branche parallèle (11), indépendamment d'une branche de traitement principale (10) dans laquelle le signal acoustique de sortie du dispositif d'aide auditive est généré, et dans lequel le dispositif de d'analyse de bruit du vent est conçu pour déterminer des paramètres (fp) à partir des premiers signaux de filtrage (fs1), dans lequel il est prévu un deuxième système de filtrage (19, 20, 21) présentant un temps de latence inférieur au premier temps de latence, destiné à filtrer le signal de transmission perturbé par le vent, de manière à obtenir des deuxièmes signaux de filtrage (fs2) en tant que base pour le signal de transmission, et
    dans lequel le dispositif d'analyse de bruit du vent est conçu pour appliquer les paramètres (fp) aux deuxièmes signaux de filtrage (fs2) afin de réduire la partie correspondant au vent.
  5. Dispositif d'aide auditive selon la revendication 4, dans lequel le premier système de filtrage (16, 17) présente en moyenne des filtres de plus grande longueur que le deuxième système de filtrage (19).
  6. Système d'aide auditive binaural, dans lequel un premier appareil d'aide auditive est réalisé conformément au dispositif d'aide auditive selon l'une quelconque des revendications 4 à 5 et dans lequel un deuxième appareil d'aide auditive représente l'appareil externe.
EP15156739.3A 2014-03-12 2015-02-26 Transmission d'un signal à bruits de vent réduits à temps de latence diminué Active EP2919485B1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102014204557.6A DE102014204557A1 (de) 2014-03-12 2014-03-12 Übertragung eines windreduzierten Signals mit verminderter Latenzzeit

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EP2919485B1 true EP2919485B1 (fr) 2018-04-18

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US (1) US9584907B2 (fr)
EP (1) EP2919485B1 (fr)
JP (1) JP6198765B2 (fr)
AU (1) AU2015201124B2 (fr)
DE (1) DE102014204557A1 (fr)
DK (1) DK2919485T3 (fr)

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AU2015201124A1 (en) 2015-10-01
EP2919485A1 (fr) 2015-09-16
US20150264478A1 (en) 2015-09-17
DK2919485T3 (da) 2018-07-30
JP6198765B2 (ja) 2017-09-20
AU2015201124B2 (en) 2018-11-15
US9584907B2 (en) 2017-02-28
DE102014204557A1 (de) 2015-09-17
JP2015177546A (ja) 2015-10-05

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