EP3926982A2 - Procédé de réduction directionnelle du bruit pour un système auditif comprenant un dispositif auditif - Google Patents

Procédé de réduction directionnelle du bruit pour un système auditif comprenant un dispositif auditif Download PDF

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Publication number
EP3926982A2
EP3926982A2 EP21175709.1A EP21175709A EP3926982A2 EP 3926982 A2 EP3926982 A2 EP 3926982A2 EP 21175709 A EP21175709 A EP 21175709A EP 3926982 A2 EP3926982 A2 EP 3926982A2
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EP
European Patent Office
Prior art keywords
signal
weighting factor
target
hearing
input
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EP21175709.1A
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German (de)
English (en)
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EP3926982A3 (fr
Inventor
Gabriel Gomez
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Sivantos Pte Ltd
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Sivantos Pte Ltd
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Publication of EP3926982A2 publication Critical patent/EP3926982A2/fr
Publication of EP3926982A3 publication Critical patent/EP3926982A3/fr
Pending legal-status Critical Current

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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
    • H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
    • H04R25/505—Customised settings for obtaining desired overall acoustical characteristics using digital signal processing
    • 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
    • H04R25/35—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using translation techniques
    • H04R25/353—Frequency, e.g. frequency shift or compression
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10L—SPEECH ANALYSIS TECHNIQUES OR SPEECH SYNTHESIS; SPEECH RECOGNITION; SPEECH OR VOICE PROCESSING TECHNIQUES; SPEECH OR AUDIO CODING OR DECODING
    • G10L25/00—Speech or voice analysis techniques not restricted to a single one of groups G10L15/00 - G10L21/00
    • G10L25/48—Speech or voice analysis techniques not restricted to a single one of groups G10L15/00 - G10L21/00 specially adapted for particular use
    • G10L25/51—Speech or voice analysis techniques not restricted to a single one of groups G10L15/00 - G10L21/00 specially adapted for particular use for comparison or discrimination
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R1/00—Details of transducers, loudspeakers or microphones
    • H04R1/10—Earpieces; Attachments therefor ; Earphones; Monophonic headphones
    • H04R1/1083—Reduction of ambient noise
    • 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
    • H04R25/405—Arrangements for obtaining a desired directivity characteristic by combining 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
    • 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
    • H04R25/48—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using constructional means for obtaining a desired frequency response
    • 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
    • H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
    • H04R25/604—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational 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
    • H04R25/65—Housing parts, e.g. shells, tips or moulds, or their manufacture
    • 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
    • H04R2410/00—Microphones
    • H04R2410/01—Noise reduction using microphones having different directional characteristics
    • 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 direction-dependent noise suppression for a hearing system, which comprises a hearing device, with the aid of at least a first input transducer of the hearing system and a second input transducer of the hearing system, an interfering signal and a target signal being generated from sound in the surroundings, the interfering signal and / or the target signal are related to a first useful signal source arranged in a first direction, a weighting factor for the respective frequency band being determined for at least a plurality of frequency bands based on an acoustic parameter of the target signal and a corresponding acoustic parameter of the interference signal, and an input signal to be processed of the hearing system is weighted by frequency band based on the respective weighting factor, and an output signal is generated based on the input signal weighted in this way.
  • Hearing aids are portable devices that are used to compensate for a hearing loss of the respective wearer. Initially, the level of individual frequencies is increased, usually individually depending on the wearer, in order to make sound audible in those frequency bands for which the sound would otherwise be inaudible without a hearing aid or would be perceived too quietly due to the hearing loss. In order to provide additional support to the wearer, hearing aids often amplify a target signal (mostly speech) compared to background noise. The corresponding increase in the signal-to-noise ratio (“signal-to-noise ratio", SNR) is mainly carried out using two separate approaches.
  • SNR signal-to-noise ratio
  • the first approach uses two or more microphones, with the aid of which directional microphones can be used to achieve directional amplification of a target signal, while sound from other directions can be attenuated. While a satisfactory noise suppression can often be achieved in this way, the spatial perception of the wearer's surroundings is often impaired by the suppression of sound from individual spatial directions.
  • the second type of noise reduction in hearing aids tries to filter the energy of interfering signals from the overall signal. This is often done using spectral subtraction, e.g. using a Wiener filter.
  • the spectrum of interference signals is estimated (e.g. from speech pauses) in order to then subtract this spectrum from the overall signal. While the spectral subtraction gives very good results for stationary or only slowly changing noise, it works only inadequately for fast spectral changes in the interfering signal or in so-called "cocktail party" situations.
  • the spectral subtraction can often result in artifacts that can degrade the speech signal.
  • the problem described also applies in a broader sense to other hearing devices in which an input signal is to be processed and fed to the ear of a wearer, e.g. headphones, headsets for communication or the like.
  • the invention is therefore based on the object of specifying a method for direction-dependent noise suppression for a hearing system with a hearing device, which method is intended to allow the most efficient and yet natural-sounding noise suppression.
  • a method for direction-dependent noise suppression for a hearing system which comprises a hearing device, in particular a hearing aid, with the aid of at least one first input transducer of the hearing system and a second input transducer of the hearing system, an interfering signal and a target signal are generated from sound in the environment, the interfering signal and / or the target signal being related to a useful signal source arranged in a target direction, the target signal being generated with a target directional characteristic which is via one of the The half-space opposite the target direction runs homogeneously or essentially homogeneously, with an acoustic parameter of the target signal being compared with a corresponding acoustic parameter of the interfering signal for at least a first plurality of frequency bands Signal amplitude and / or a signal power of the respective signal is used, and a preliminary weighting factor is determined on the basis of said comparison, the value range of which has at least three values, a weighting factor in each case for the frequency band based
  • a hearing device includes, in particular, a hearing aid which is preferably designed and set up to compensate for a hearing loss and / or a hearing impairment of the wearer. Any device is also included by means of which a sound signal is converted into a corresponding input signal by an input transducer and is processed for reproduction to the ear of the wearer of the device via corresponding signal processing, e.g. headphones or headset for communication.
  • an input transducer generally includes any form of electro-acoustic transducer which is set up to convert ambient sound into a corresponding electrical signal, the voltage or current amplitudes of which preferably reflect the amplitude profile of the ambient sound.
  • a hearing system is to be understood here in particular as any system that includes the hearing device and, if applicable one or more further devices, and thereby having the required number of input transducers as well as a control or computer device for processing the corresponding signals, in the event that the hearing system is not provided by the hearing device alone, between the said further device or devices a data connection, in particular a wireless connection, to the hearing device can be established to transmit the signals used and / or possibly further information.
  • the hearing system can also be provided completely by the hearing device.
  • the generation of an interfering signal and a target signal based on at least a first input transducer of the hearing system and a second input transducer of the hearing system includes in particular that the interfering signal and / or the target signal is each formed as a directional signal, which is based on the two signals of the first and the second Input transducer is generated.
  • this also includes the fact that the interference signal is generated only on the basis of the first input transducer, and the target signal is only generated on the basis of the second input transducer, a reverse assignment to the respective input transducers also being possible here.
  • the interfering signal and / or the target signal are related to a useful signal source, which means in particular that the target signal contains a higher proportion of signals from the useful signal source than the interfering signal. This can be achieved in particular by weakening the interfering signal in the target direction, but also by emphasizing the target direction relative to other directions or angular ranges in the target signal, or by both of the measures mentioned.
  • Generating the target signal with a target directional characteristic which runs homogeneously or essentially homogeneously over a half-space opposite the target direction preferably includes the target directional characteristic being the result of signal processing of the signal or signals used by the or . the input transducer used, and is related in particular to a free field as a result of said signal processing.
  • the described course of the target directional characteristic over the mentioned Half-space includes in particular that the course of the sensitivity according to the target directional characteristic has no turning points and no local minima, and / or that the sensitivity in the said half-space only has variations that compared to the maximum sensitivity of the target signal (preferably in the target direction ) are suppressed by at least 10 dB, preferably 15 dB, ie the difference between maximum and minimum sensitivity in said half-space is at most -10 dB, preferably at most -15 dB, based on the maximum sensitivity of the target signal (in the target direction). Such variations can then be neglected compared to a signal contribution from the target direction.
  • a homogeneous curve here means in particular that there is no variation in sensitivity in the said half-space within the framework of technical feasibility and accuracy. If you assign the angle 0 ° to the target direction, the opposite half-space is given by the angle range from 90 ° to 270 °.
  • the course of the target directional characteristic is homogeneous or essentially homogeneous for as large an angular range as possible, with the exception of a range of, for example, +/- 45 ° around the target direction, the transition to the mentioned range being around the target direction preferably designed continuously.
  • a homogeneous course of the target directional characteristic can be achieved in particular by an omnidirectional target signal.
  • the signal processing for generating the target signal from the signals of the first and the second input transducer includes a corresponding directional microphone; for a generation from only one signal of one of the two input transducers, this can mean in particular that the signal processing does not impose any directivity on the target signal.
  • weighting factors for noise suppression based on frequency bands are determined, based on which frequency bands with a high proportion of noise can be lowered in the input signal to be processed or frequency bands with a high proportion of a useful signal of the useful signal source can be relatively increased.
  • the input signal to be processed is here preferably given by the signal of a single input transducer, i.e. the first or second or possibly the further input transducer mentioned, with preprocessing such as A / D conversion, but possibly also preamplification, preferably as part of the Input transducer is to be treated.
  • an acoustic parameter of the target signal is now formed for a plurality of frequency bands and compared with the corresponding acoustic parameter of the interference signal.
  • the acoustic parameter is preferably such that information about the energy content in the relevant frequency band can be given for the respective signal.
  • a signal level and / or a signal amplitude and / or a signal power of the respective signal is used as the acoustic parameter, wherein the named parameter can be formed either directly from one of the named signal variables or from a monotonic, in particular strictly monotonic function, eg a quadratic or logarithmic function of the signal level and / or the signal power and / or the signal amplitude.
  • a quotient is formed from the signal level of the target signal in the frequency band as numerator and the signal level of the interference signal in the frequency band as denominator, or the said signal levels are compared with one another in some other way.
  • the comparison of the acoustic parameters mentioned is then mapped onto the preliminary weighting factor, the value range of which comprises at least three values, the value range being able to be discrete or continuous.
  • the comparison can take place in particular by dividing the said parameters.
  • a quotient based on the acoustic parameter of the target signal is preferred for at least some frequency bands of the first plurality formed as a numerator and based on the corresponding acoustic parameter of the interference signal as a denominator, and based on the respective quotient, the preliminary weighting factor is formed.
  • the preliminary weighting factor can be continuous or discrete.
  • the quotient is mapped monotonically to a value range comprising at least three discrete values for the relevant frequency bands to form the preliminary weighting factor, e.g. by assigning individual intervals of the value range of the quotient to individual discrete values of the preliminary weighting factor.
  • the comparison can, however, also take place in such a way that for at least some frequency bands of the first plurality the acoustic parameter of the target signal and the corresponding acoustic parameter of the interfering signal are subjected to a plurality of size comparisons, one of the two parameters being scaled differently for the individual size comparisons, and the respective value from the discrete, at least three-valued value range being assigned to the preliminary weighting factor on the basis of the size comparisons.
  • the signal level of the useful signal is compared with the signal level of the interference signal in the band for individual frequency bands. If the signal level of the useful signal is higher, the frequency band is assigned the largest value from the discrete value range for the preliminary weighting factor (e.g. 1.3). However, if the signal level of the interfering signal is higher, the target signal can be multiplied by a given factor> 1, for example, and the next comparison can be made with the interfering signal level. If the useful signal level is higher, the next value of the discrete value range (e.g. 0.75) can be assigned to the preliminary weighting factor for the frequency band. If the interference signal level is still higher, either the smallest value (e.g. 0.5) can be assigned for the preliminary weighting factor, or the process of scaling the useful signal can first be repeated again.
  • the smallest value e.g. 0.5
  • the input signal to be processed can now be weighted accordingly will. This can be done by directly applying the weighting factor to the signal components of the input signal to be processed in the relevant frequency band, or by averaging over time and / or normalizing the weighting factor before multiplication to the signal components of the associated frequency band.
  • individual static correction factors can be applied for each frequency band, which take into account, for example, spectral differences of the input transducers involved for different frequency bands, but also level and / or transit time differences, and correct the corresponding influence on the noise suppression.
  • An output signal is now generated on the basis of the input signal to be processed and weighted in this way. On the one hand, this can take place in that the output signal is generated directly from the signal components of said weighted input signal. If necessary, however, further signal processing of these signal components can take place here, such as suppression of acoustic feedback or the like, additional frequency band-dependent lowering or increasing depending on the individual audiological requirements of the wearer of the hearing device.
  • the output signal can, however, also be generated using signal components of a further signal, for example by directional microphones using a further signal, but also by the particularly broadband mixing of the weighted input signal with an omnidirectional signal or a directional signal.
  • the invention is based on the assumption that a useful signal from the useful signal source and a noise signal from one or more noise sources have different spectral information at each individual point in time, ie that the amplitude spectrum and the phase of the sound from the various sources are different at any point in time. Since the sound pressure fields of several sources add up through superposition, the spectral information is also a sum of the individual components of the individual sources. This means, in particular, that the sound pressure at the location of an input transducer is a sum of individual sources and reflections at any point in time, which may be filtered by transfer functions that determine the propagation of the sound from a source for the respective input converter.
  • a subtraction of the individual spectral components can lead to a selective attenuation or removal of these components from the total sum of the target signal (e.g. at the location of an input transducer for the input signal to be processed), or desired signal components can be specifically selected and can be raised.
  • the frequency band-wise energy components of the useful signal and of the noise signal are used if possible at any point in time or a sufficiently dense sequence of discrete points in time, the latter given, for example, via the sampling rate or via the individual "frames" of a spectral analysis using FFT or the like determine which energetic components originate from the useful signal source or the noise sources at any point in time, a direction-dependent filtering of the sound field by means of the target signal and the interfering signal is carried out in such a way that the proportion of the useful signal of the useful signal source in the generated target signal is significantly higher than in the generated interfering signal, which accordingly contains a significantly higher proportion of noise in its total energy.
  • the input signal to be processed can be relatively increased in such a frequency band compared to other frequency bands in which the acoustic parameter of the interfering signal is greater than the acoustic parameter of the target signal, since in those frequency bands a higher proportion of noise and a lower useful signal component is assumed.
  • the spatial isolation that the target signal carries out with respect to the interference signal with regard to the sound from the useful signal source is preferably used.
  • the essentially homogeneous course of the target signal in the half-space opposite the target direction due to the essentially homogeneous course of the target signal in the half-space opposite the target direction, a particularly natural sound can be achieved.
  • an interference signal is preferably used which, in the aforementioned half-space in the sense described above, also has as homogeneous a sensitivity as possible to the noise sources to be reduced.
  • Spectral components of noise from a direction that is clearly different from the target direction can thus be reduced from the input signal to be processed in such a way that a natural sound image is retained.
  • the advantages are not limited to the said half-space, but are also effective to a limited extent beyond the exact boundaries of the half-space due to the conditions of continuity and regularity of the signals used.
  • the weighting factor is preferably formed in each case on the basis of the preliminary weighting factor and on the basis of a normalization factor which is determined as a function of at least one preliminary weighting factor of the second plurality of frequency bands.
  • the normalization factor is preferably determined directly, that is to say in particular linearly and preferably identically, from a preliminary weighting factor of one of the frequency bands, possibly after time averaging.
  • Such a normalization allows a weighting of the individual frequency bands to be related to one another through the normalization, in that, for example, all relevant frequency bands are subject to the same normalization.
  • Determining the weighting factor as a function of at least one preliminary weighting factor includes in particular a respective time averaging of the acoustic parameters of the respective target and interference signal on which the at least one preliminary weighting factor is based.
  • the value of the normalization factor can also be limited upwards
  • the normalization factor for a frequency band is advantageously determined using a time average of the values of the acoustic parameters used and / or the values of the preliminary weighting factor in the same frequency band, and / or based on a maximum and / or a sum of the values of the preliminary weighting factors and / or one Signal level over all relevant frequency bands.
  • This also includes, in particular, a time average over the instantaneous maximum of the frequency band-wise values of the individual preliminary weighting factors and a maximum over the time averages of all relevant frequency bands.
  • a normalization of the preliminary weighting factor in a frequency band based on the maximum of the values of the preliminary weighting factors over all relevant frequency bands has the advantage, especially for a comparison based on a quotient, that for the frequency band in which the preliminary weighting factor is maximum, i.e. compared to the interference signal Most of the spectral energy is contained in the target signal (and thus the proportion of the useful signal is probably the largest), the weighting factor assumes the maximum value of 1.
  • a corresponding weighting of the input signal to be processed corresponds to a signal unchanged by the weighting.
  • a normalization based on a time average over the instantaneous maximum of the frequency band-wise values of the individual preliminary weighting factors or on the basis of a maximum over the time average of all relevant frequency bands is particularly advantageous.
  • a time averaging is preferably carried out over a period of time from 0.1 s to 1 s.
  • Such a temporal mean value formation can prevent a "pumping" of the background from occurring in the output signal as a result of short-term fluctuations in the useful signal.
  • the normalization can take place by means of a fixed value for the normalization factor, which can depend in particular on a weakening of the interference signal and on the absence of a useful signal (recognizable from the interference signal and the target signal).
  • Such a procedure has the advantage that in an acoustic environment in which there is no instantaneous useful signal, everything is reduced by the said fixed value, which is often perceived as more pleasant due to the noise or the background noise as the only noise component.
  • a signal with an essentially omnidirectional directional characteristic is expediently generated as the target signal, and a directional signal with a relative attenuation in the target direction is used as the interference signal.
  • a generation of a signal with an essentially omnidirectional directional characteristic is to be understood here in particular as meaning that said directional characteristic results as a result of the signal generation. This can be done on the one hand by a signal from an omnidirectional microphone as an input transducer, or on the other hand by an omnidirectional sum-and-delay signal or delay-and-subtract signal from an array of input transducers.
  • a directional signal with a relative attenuation in the target direction includes on the one hand that said attenuation occurs as a result of the signal generation, e.g. through differential directional microphones using the first and second input transducers.
  • an omnidirectional signal can also be generated (in the sense described above) and the desired attenuation can be achieved, e.g. via shadowing effects.
  • the generation of a signal with a specific directional characteristic means in particular the said directional characteristic in the free field as a result of the electroacoustic signal generation, while the use of a signal with a specific directional characteristic also means that it is due to the spatial circumstances of use Directional characteristics may include.
  • the interference signal preferably has a maximum, as total as possible, attenuation in the target direction;
  • the interference signal can be generated as an anti-cardioid directional signal based on the signals of the first and the second input transducer by corresponding time-delayed superimposition.
  • this is preferably limited to an upper limit value of 6 dB, preferably 12 dB, particularly preferably 15 dB, which is advantageous if there are no significant noise components in the meantime to counter a strong useful signal.
  • an anti-cardioid-shaped interference signal such a limitation can also be replaced or supplemented by a notch with a finite depth in the anti-cardioid-shaped directional characteristic, which can be achieved, for example, by a complex-valued superposition parameter of the two signals from the input transducers.
  • a directional signal oriented in the target direction is used as the target signal, which directional signal has an almost complete attenuation in the half-space opposite the target direction.
  • Almost complete attenuation includes, in particular, an attenuation of -10 dB, preferably -15 dB, such as in the case of one Signal with a club-shaped directional characteristic.
  • the interference signal preferably has as homogeneous a sensitivity as possible in said half-space, for example as a cardioid-shaped directional signal (with attenuation in the target direction) or as an omnidirectional signal.
  • the interference signal is advantageously generated at least on the basis of a first input transducer which is arranged in a housing that is worn at least partially behind a pinna by a wearer of the hearing device during normal operation of the hearing device.
  • the second or a further input transducer is preferably also arranged in the said housing.
  • the interference signal is then preferably formed as a directional signal from the two corresponding input signals of the two input transducers (that is to say of the first and the second or further input transducer).
  • the target signal can in particular be formed as an omnidirectional signal from the two input signals which are generated by the first and second input transducers arranged in the housing.
  • a so-called roll-on compensation of the interfering signal is preferably carried out, e.g. by means of a low-pass filtering if the interfering signal is generated as a delay-and-subtract directional signal of the input transducer signals, but the target signal, for example, as a delay-and-sum signal or as a signal from just one input transducer.
  • the aforementioned low-pass filtering can be omitted if the target signal is also generated as a delay-and-subtract signal.
  • the interference signal can, however, also be generated from just one input transducer using the natural shading effect of the pinna; the target signal is then preferably generated solely by the other input transducer, which can be arranged, for example, at the entrance of the auditory canal.
  • the first and the second input transducer are both arranged in the housing, which is given, for example, by a housing of a BTE or RIC hearing aid.
  • the interference signal can then be generated using differential directional microphones, the target signal as a "2-mic-omni" signal.
  • the input signal to be processed is expediently generated by an earpiece input transducer which is arranged in an earpiece which is worn by the wearer of the hearing device when it is used as intended, at least partially inserted into a concha and / or an auditory canal.
  • the earpiece input transducer can also be provided by the first or second input transducer in such a way that the input signal to be processed is also used to determine the interference signal and / or the target signal.
  • Interference and target signals can, however, also be generated separately from the input signal to be processed, e.g. as described above in a BTE / RIC housing.
  • the target signal is generated in a device that is external to the hearing apparatus.
  • the external device is to be understood here in particular as part of the hearing system and, as such, is preferably designed for communication with the hearing device via a corresponding connection.
  • a mobile phone can be used here as an external device, which is set up for the method in particular by a corresponding application that controls the microphone of the mobile phone as the first input transducer and the signal transmission with the hearing device.
  • the comparison of the useful signal with the interfering signal can in this case preferably take place on the hearing device after the target signal or the acoustic parameter has been transmitted accordingly by the mobile phone.
  • the interference signal can also preferably be generated by a second input transducer of the hearing device and then transmitted to the external device for the corresponding comparison of the acoustic parameters.
  • a dedicated external unit can be used as the external device, e.g. a so-called partner unit for a hearing aid as a hearing device.
  • the partner unit is worn on the body by a conversation partner of the wearer of the hearing aid, for example around the neck or in his vicinity, for example on a table in front of him, in order to make conversations more audible for the wearer of the hearing aid.
  • a conversation partner of the wearer of the hearing aid for example around the neck or in his vicinity, for example on a table in front of him, in order to make conversations more audible for the wearer of the hearing aid.
  • only one input transducer of the partner unit can be used to generate the target signal can be used, since the useful signal - the conversation contributions of the conversation partner who is in the immediate vicinity of the partner unit - is included in a signal that is generated by the partner unit in a particularly emphasized manner compared to any interfering noises.
  • the weighting factor is expediently further formed on the basis of a factor which takes into account volume differences and / or runtime differences and / or spectral differences in the respective frequency band between the first input transducer and / or the second input transducer and / or the further input transducer for generating the input signal to be processed.
  • the additional factor can e.g. if necessary, consider the different shading effects of the pinna.
  • the factor can take into account a relative transfer function from the location of the generation of the interference signal (e.g. housing on or behind the pinna) to the location of generation of the target signal (e.g. at the ear canal or in an external unit), preferably with regard to the assumed useful signal source. In this way, components for the weighting factor which arise due to different propagation of the sound to the location of the generation of the interference signal or the location of the generation of the target signal can be compensated.
  • the output signal is formed on the basis of the input signal to be processed, weighted in frequency bands with the respective weighting factors, and a further omnidirectional signal and / or a further directional signal.
  • a directional signal e.g. a cardioid-shaped directional signal
  • an audibility of artifacts can be reduced, while the natural sound impression is still retained.
  • the weighted input signal to be processed can be mixed with an omnidirectionally generated signal (in particular in the aforementioned proportions) for the formation of the output signal, which is particularly preferably generated by a different input transducer than the input signal to be processed.
  • first weighting factors are determined for a first useful signal source arranged in a first target direction in a frequency band
  • second weighting factors are determined in a frequency band for a second useful signal source arranged in a second target direction
  • the input signal to be processed in the respective Frequency band is weighted on the basis of a weighting factor, which is formed on the basis of the respective first weighting factor and on the basis of the respective second weighting factor, preferably as a mean value or as a product.
  • first weighting factors are determined with regard to a first useful signal source. This takes place on the basis of comparisons of acoustic parameters, which are obtained in the respective frequency bands from a first interference signal and a first target signal, which are related to the first useful signal source.
  • the first interference signal has a relative and, in particular, greatest possible attenuation in a first target direction, which is preferably given by the direction of the first useful signal source.
  • second weighting factors are determined for the input signal to be processed with respect to a second useful signal source, which is different from the first useful signal source and is in particular occupied in a second target direction different from the first target direction.
  • Those weighting factors that are now to be applied to the input signal to be processed are now determined by frequency band based on the first weighting factors (i.e. with regard to the first useful signal source) and using the second weighting factors (i.e. with regard to the second useful signal source), preferably using a product or one arithmetic mean, possibly weighted with a sound power of the respective useful signal sources, and in particular a suitable global normalization.
  • the hearing system preferably has a further hearing device, the preliminary weighting factor being determined for at least one frequency band in the hearing device, a contralateral preliminary weighting factor being transmitted to the hearing device from the further hearing device, and the weighting factor or a weighting factor for one transmitted by the further hearing device Contra-lateral input signal is determined by comparing the preliminary weighting factor with the contra-lateral preliminary weighting factor.
  • the hearing system is given in this case as a binaural hearing aid system, the hearing apparatus and the further hearing apparatus each being provided by a single hearing aid to be worn on one ear.
  • the contra-lateral input signal is then an input signal for a hearing aid which is generated in the other hearing aid and which is transmitted for binaural signal processing.
  • the contra-lateral preliminary weighting factor is preferably formed in the other hearing device in the same way as the preliminary weighting factor in the hearing device.
  • the weighting factor to be used by the hearing device is then formed on the basis of a comparison of the "local" preliminary weighting factor generated in the hearing device with the contra-lateral preliminary weighting factor from the other hearing device.
  • This procedure allows, in particular for a binaural hearing aid system, to "synchronize" the preliminary weighting factors on both sides, so to speak, in individual frequency bands, so that a distortion, for example of the "interaural level difference", can be prevented by, for example, a mean value of the preliminary weighting factors for the weighting factor is used on both sides (or, if necessary, the local preliminary weighting factor is weighted slightly more than the contra-lateral preliminary weighting factor, e.g. 0.6 to 0.4 or 0.7 to 0.3).
  • the contra-lateral preliminary weighting factor is preferably transmitted to the hearing device as a binary value, the contra-lateral weighting factor being assigned the value of the preliminary weighting factor if a deviation of the contra-lateral preliminary weighting factor from the preliminary weighting factor does not exceed a predetermined limit value.
  • the contra-lateral preliminary weighting factor is preferably discretized to three values or a few values more, and is compared with the "locally" present preliminary weighting factor, whose value range can initially also have even more values.
  • This range of values for the local provisional weighting factor can now on the one hand be mapped to coarser intervals for comparison with the contra-lateral provisional weighting factor (preferably the same number as the value range of the contra-lateral provisional weighting factor), so that the local provisional weighting factor is assigned as the weighting factor - and if necessary still normalized - if the contra-lateral provisional weighting factor lies in the same “coarser interval” as the “local” provisional weighting factor. If this is not the case, the preliminary weighting factors can be averaged for the weighting factor.
  • the invention also mentions a hearing system with a hearing device, the hearing system comprising at least two input transducers for generating an interference signal, a target signal and an input signal to be processed, the hearing device comprising at least one output transducer, and the hearing system comprising a control device which is used to carry out the The procedure described above is set up.
  • the hearing system according to the invention shares the advantages of the method according to the invention. The advantages specified for the method and for its further developments can be applied analogously to the hearing system.
  • the input signal to be processed can either be generated using one or both input transducers, which are also used for generating the interference signal and the target signal, or can be generated using a further input transducer of the hearing system.
  • the control device is preferably implemented in the hearing device. If the hearing device is provided by a binaural hearing aid system, the control device can also be provided by the entirety of the signal processing devices in both local units of the binaural system.
  • the hearing system can in particular comprise an external unit which is not to be regarded as part of the hearing apparatus, for example a mobile phone or the like with an input transducer, which is set up in particular to generate the target signal and / or the interfering signal, as well as possibly with a signal processing device, which in this case can also form part of said control device.
  • the hearing device is preferably designed as a hearing aid.
  • the use of the method described above is particularly advantageous for a hearing aid which is designed and set up in particular to compensate for a hearing impairment or a hearing loss of the wearer.
  • the hearing aid preferably comprises a housing in which a first input transducer and a second input transducer are arranged, the hearing aid comprising an earpiece in which a further input transducer is arranged for generating the input signal to be processed, and the control device is set up to use of the signals from the first input transducer and the second input transducer to form the interference signal and the target signal.
  • the interfering signal and / or the target signal for obtaining the frequency band-dependent weighting factors for the input signal to be processed can be generated efficiently and literally precisely using directional microphones, so that particularly good noise suppression is possible.
  • the input signal to be processed is generated at the ear canal of the wearer, and thus contains particularly natural spatial information of the acoustic environment of the wearer, with the natural shading effect of the pinna for the input signal to be processed being retained, which further favors the natural spatial hearing impression.
  • FIG 1A a hearing system 2 formed by a hearing device 1 is shown schematically in a side view.
  • the hearing device 1 is given here by a hearing aid 4.
  • the hearing aid 4 has a housing 6 and an earpiece 8 connected to the housing 6.
  • the hearing aid 4 is designed as a RIC device which has an output transducer 10 designed as a loudspeaker at the end of the earpiece 8.
  • the earpiece 8 is mechanically connected to the housing 6 via a connection 12, with a signal connection 14 running along the connection 12, which uses the output transducer 10 electronically with a signal processing device 16 in the housing 6 in a manner to be described later (dashed line).
  • the signal processing device 16 here forms a control device 18 for the hearing system 2, and is in particular provided by one or more signal processors, each with an assigned main memory.
  • a first input transducer 21 and a second input transducer 22 are arranged slightly spaced apart from one another and are each electronically connected to the control device 18 (dashed line).
  • the first and second input transducers 21, 22 each generate input signals (not shown in detail) and output them to the signal processing device 16, where they are processed as a function of the individual audiological specifications and requirements of a wearer of the hearing aid 4, and in particular, are amplified and, if necessary, compressed as a function of the frequency.
  • the signal processing device 16 outputs an output signal (not shown in detail) to the output transducer 10 via the signal connection 14, which converts the said output signal into an output sound (not shown in detail) which is fed to the wearer's hearing.
  • spatial processing in the signal processing device 16 by means of directional microphones is also possible for generating the said output signal.
  • the present hearing aid 4 is therefore set up to use the signals from the first and second input transducers 21, 22 to determine frequency-dependent weighting factors to be described, by means of which an a priori, preferably omnidirectional, input signal to be processed is weighted in the signal processing device 16, with the weighting factors should bring about an advantageous noise suppression over individual frequency bands.
  • the signal 24 generated by the first input transducer 21 can be used as an input signal to be processed.
  • the hearing aid 4 can also have a further input transducer 26 in the earpiece 8, and the input signal to be processed can then be given by the signal of the said further input transducer 26.
  • this has the advantage that when the hearing aid 4 is worn as intended, the housing 6 being at least partially worn by the wearer behind the pinna of one of his ears, and the earpiece 8 with the end of the output transducer 10 being inserted into the entrance of the associated auditory canal, the further input transducer 26 is arranged in the area of the entrance of the auditory canal, and thus the signal generated by the further input transducer 26 with regard to a shadowing effect of the head and in particular the pinna of the wearer has essentially the same behavior as sound, which without the presence of the hearing aid 4 to the ear of the carrier advances.
  • FIG 1B is a schematic side view of an alternative embodiment of the hearing device 1 according to FIG Figure 1A shown.
  • the hearing device 1 is provided by a hearing device 4 designed as a RIC device with a housing 6 to be worn partially behind the pinna during operation and an earpiece 8, with a first input transducer 21 being arranged in the housing 6, which is in signal connection with a likewise in the housing 6 arranged control device 18 is.
  • An output transducer 10 is arranged in the earpiece 8 and is connected to the control device 18 via a signal connection 14, the signal connection 14 being along the mechanical connection 12 between the housing 6 and the earpiece 8 runs.
  • the earpiece 8 is inserted with the free end for the operation of the hearing aid 4 into the entrance of the ear canal of the wearer.
  • a second input transducer 22 is arranged in the earpiece 8.
  • Figure 1A frequency-dependent weighting factors are determined in a manner yet to be described, by means of which the input signal to be processed, generated in the present example by the second input transducer 22, is weighted in the control device 18 for noise suppression.
  • the hearing aid 4 shown here consists in that the second input transducer 22, the signal of which is used to determine the frequency-dependent weighting factors, is arranged in the earpiece 8 (and not, like the first input transducer 21, in the housing 6).
  • the hearing aid 4 after Figure 1A or after Figure 1B can in particular also be designed as a BTE device, the connection 12 then being formed by the sound tube of the BTE device.
  • the second input transducer 22 can be arranged in the housing 6 of the BTE device. Is the second input transducer (or the further input transducer 26 after Figure 1A ) arranged in or on the earpiece 8 (the free end of which is formed in a BTE device by, for example, a dome or an earmold), the signal connection 14 to the control device 18 in the housing 6 runs along the said sound tube, preferably in a dedicated cable.
  • a signal processing device 16 can also be arranged in the earpiece 8 as part of the control device 18. If the earpiece 8 has an input transducer, the hearing device 4 can in particular be provided by a type of combination of a BTE or RIC device with an ITE or CIC device.
  • FIG 2 is schematically in a block diagram of the hearing system 1 formed by the hearing aid 4 according to Figure 1A with the signal processing for noise suppression already described.
  • the hearing aid 4 comprises the first input transducer 21 and the second input transducer 22, which from the first Input transducer is arranged at a distance D.
  • the first input transducer 21 generates a first signal 31
  • the second input transducer 21 generates a second signal 32 from an ambient sound not shown in detail.
  • a possible pre-amplification and pre-processing, such as broadband compression and A / D conversion, should already be included in the function of the first and second input transducers 21, 22, respectively.
  • the first and the second signal 31, 32 are now transformed into the time-frequency domain in each case in filter banks 33, 34.
  • the first signal 31 filtered in this way is now delayed in each frequency band by a time constant T, possibly filtered with a complex transfer function (not shown), which can take into account possible level and / or phase differences of the two input transducers 21, 22, and from the filtered signal 32 subtracted, and then filtered with a low pass 35.
  • the low-pass filtering takes place because low-frequency signal components are attenuated by the subtraction, since the time constant T as the acoustic transit time between the two input transducers 21, 22 as a result of the distance D means that low-frequency signal components in both input transducers 21, 22 are still similar despite the propagation Have amplitudes.
  • Said low-pass filtering now results in an interference signal 36 which, as a result of the time delay T before the subtraction of the two input signals 31, 32, which corresponds exactly to the acoustic transit time for the distance D, has essentially an anti-cardioid-shaped directional characteristic 64 in each frequency band, whose maximum attenuation points in a target direction 38, which is given by a connecting line from the second input transducer 22 to the first input transducer 21, and coincides with the frontal direction when the hearing aid 4 is worn as intended.
  • the second signal 32 broken down into individual frequency bands by the filter bank 34, has essentially an omnidirectional directional characteristic 63 as a microphone signal for each frequency band.
  • This second signal 32 is now used as target signal 40.
  • an acoustic parameter 42 is then determined, which in each case provides information should give about the energy content of the signal in question in the respective frequency band. In the present case, this is ensured in that the absolute value of the respective signal is selected as the acoustic parameter 42.
  • a signal power or a signal level or a monotonic, for example a quadratic or logarithmic function of the signal power, the absolute value or the signal level can also be used as parameter 42.
  • Time averages 48 and 49, respectively, are now formed from the absolute amount 44 of the interference signal 36 and from the absolute amount 46 of the target signal 40 for smoothing.
  • a quotient 50 is then formed from the time average 49 of the absolute amount 46 of the target signal 40 as a numerator and the time average 48 of the absolute amount 44 of the interference signal 36 as the denominator.
  • This quotient which can optionally be restricted to an upper limit value of, for example, 6 dB or higher (for example 12 dB or 15 dB), forms a preliminary weighting factor 51 for the respective frequency band.
  • a maximum 52 of the preliminary weighting factors 51 is now determined over all frequency bands and defined as the normalization factor 52.
  • the preliminary weighting factors 51 are normalized using the normalization factor 52 determined in this way, so that a weighting factor 54 results for each frequency band.
  • An input signal 56 to be processed is generated on the basis of the further input transducer 26.
  • the input signal 56 to be processed is transformed by a filter bank 57 into the time-frequency domain.
  • the filter banks 33, 34, 57 preferably have an identical frequency resolution and an identical edge steepness.
  • the weighting factor 54 is then applied multiplicatively to the input signal 56 that is to be processed and transformed in this way.
  • a broadband output signal 58 is generated from the frequency band-wise weighted signal components of the input signal 56 to be processed, for example by means of an inverse fast Fourier transformation, which is converted by the output converter 10 into an output sound 60.
  • an additional, not shown, can in particular be used Signal processing take place, which can include, for example, a frequency band-wise lowering or increasing of the signal contributions depending on the individual audiological requirements of the wearer and / or additional measures for suppressing interfering noises and / or acoustic feedback.
  • an absolute amount and a phase can first be determined from the input signal 56 to be processed for the application of the weighting factor 54 to the input signal 56 to be processed in the respective frequency band, the weighting factor 54 being applied only to the absolute amount, and the phase for an inverse transformation is used to generate the output signal 58.
  • the input signal 56 to be processed is generated by the first or the second input transducer 21 or 22, respectively.
  • the directional signal 56 to be processed thus corresponds to the first or second signal 31 or 32.
  • other alternative configurations of the hearing aid 4 are also conceivable for noise suppression, for example a so-called ITE hearing aid with two input transducers arranged in the area of the auditory canal as the first and second second input transducer 21, 22 for generating the two signals 31, 32 and the input signal 56 to be processed.
  • FIG. 3 is schematic in a plan view and simplifies the effect of the preliminary weighting factor 51 according to FIG Figure 2 in terms of sound signals from different spatial directions.
  • the left picture shows a wearer 62 of the hearing aid 4 and the omnidirectional directional characteristic 63 of the target signal 40 that surrounds it Direction 38. It can be immediately recognized that for a sound signal from the half-space 66 opposite the target direction 65, there is no noticeable attenuation by the interference signal 36, since there the anti-cardioid directional characteristic 64 is essentially homogeneous and similar to the omnidirectional directional characteristic 63.
  • the right-hand image shows the directional dependency 68 of the preliminary weighting factor 51, as can be guessed schematically from the two directional characteristics 63, 64. While the target signal 40 and the interference signal 36 have a largely similar sensitivity to sound signals in the rear half-space 66, the preliminary weighting factor 51 runs essentially homogeneously in this area and is therefore independent of direction. Only with increasing approach to the target direction 38 do the differences in the two directional characteristics 63, 64 become increasingly noticeable, so that the preliminary weighting factor 51 has a strong bulge in the target direction 38. This bulge can be limited to a finite value, in particular by compression or limiting.
  • FIG 4 is schematically in a plan view one with respect to the in Figures 1A and 1B
  • the variants shown are an alternative embodiment of the hearing system 2, which comprises a hearing device 1 and an external device 70.
  • the external device 70 is given by a mobile phone 71.
  • the hearing device 1 is provided by a hearing aid 4 which is worn by the wearer 62 on one ear (not shown in detail).
  • the hearing aid 4 has at least one first input transducer 21 and can be designed as an ITE device, for example.
  • the mobile phone 71 is positioned directly in front of a conversation partner 74 of the carrier 62 in such a way that a microphone of the mobile phone is used as a second input transducer 22 of the hearing system 1 can record speech contributions 75 of the interlocutor 74 unhindered and particularly clearly.
  • the signals in the hearing aid 4 are used
  • the first input transducer 21 and the second input transducer 22 arranged in the mobile phone 71 generate frequency-dependent weighting factors in a manner still to be described, which weighting factors are applied in the hearing aid 4 to the signal from the first input transducer 21.
  • the weighting factors are generated in such a way that spectral components of the interference sources 76, 78 (or also diffuse background noise) in the signal of the first input transducer 21, which ultimately represents the total sound incident there, are reduced as far as possible by the weighting that takes place.
  • spectral components of the speech contributions 35 are to be preserved as far as possible by the weighting and, in particular, are to be increased relative to the interference noises of the interference sources 76, 78.
  • the weighting factors are obtained in frequency bands using a target signal and an interfering signal, the target signal being intended to contain as high a relative proportion as possible of the useful signal (based, for example, on the total energy in a frequency band), i.e. in the present case of the speech contributions 75, and in the interfering signal the lowest possible relative proportion of the useful signal.
  • the strength of the suppression of the interference sources 76, 78 should, if possible, not depend on their direction, but preferably only on their volume. This specification is now achieved in that the signal from the first input transducer 21 is used as the interference signal and the signal from the second input transducer 22 is used as the target signal.
  • the signal of the second input transducer 22 has a particularly high proportion of speech contributions 75 from the interlocutor 74, while the first input transducer 21 in the hearing aid 4 has a lower proportion of speech contributions 75 solely due to the physical distance between the wearer 62 and the interlocutor 74 will record and to the extent that higher spectral components of the interference sources 76, 78 are recorded in its signal.
  • the hearing system 2 can also be designed as a binaural hearing aid system which, in addition to the hearing aid 4, has a further hearing aid (not shown) with the second input transducer, which is to be worn by the wearer 62 on the other ear.
  • first preliminary weighting factors 51 can be determined (cf. Figure 2 ). These preliminary weighting factors, which are then contra-lateral with respect to the hearing aid 4, are transmitted to the hearing aid 4, where on the one hand the weighting factors of the individual frequency bands to be applied locally in the hearing aid 4 can be generated by comparing the local preliminary weighting factors with the contra-lateral preliminary weighting factors.
  • the contra-lateral preliminary weighting factors can also be used in the context of binaural signal processing if, for example, a signal to be processed is also transmitted from the (contra-lateral) further hearing aid to the hearing aid 4. Weighting factors which are to be applied to the contra-lateral signal of the further hearing aid in the hearing aid 4 as part of the binaural signal processing are then formed on the basis of the contra-lateral preliminary weighting factors.
  • Fig. 5 is a schematic block diagram of an alternative to noise suppression according to Fig. 2 for the hearing aid 4 shown there.
  • the signal processing can proceed essentially identically (the low pass 35 for the interfering signal 36 was not shown for the sake of simplicity)
  • the input signal 56 to be processed is also given by the second signal 32 in the time-frequency domain (and thus the useful signal 40).
  • the first signal 31 (in the time-frequency domain) or the signal of a further input transducer 26 could also be used as the signal to be processed (which in the exemplary embodiment after Fig. 5 not provided).
  • the weighting factor 54 can now also be generated in the individual frequency bands in that the quotient 50 is mapped onto a discrete value range 80 of, for example, three values 80a, 80b, 80c for the preliminary weighting factor 51.
  • a discrete value range 80 of, for example, three values 80a, 80b, 80c for the preliminary weighting factor 51.
  • an upper, a middle and a lower interval 82a, 82b, 82c are defined for the quotient 50, which are each set to the highest value 80a (for example 1 or 1.3 or a value in between) or the middle value 80b (eg 0.75 or the like) or the smallest value 80c (eg 0.5 or less) for the preliminary weighting factor 51 can be mapped.
  • the preliminary weighting factor 51 generated in this way can also be smoothed over time.
  • a normalization (not shown) is also possible (in particular if a value ⁇ 1 is defined as the largest value of the discrete value range).
  • the acoustic parameter 42 of the target signal 40 i.e. in the present example its absolute value 46
  • the corresponding acoustic parameter 42 of the interference signal 36 i.e. in this case its absolute value 44
  • the absolute amount 46 of the target signal 40 is greater than the absolute amount 44 of the interference signal 36
  • the largest value 80a of the predetermined, discrete value range 80 is assigned as the preliminary weighting factor 51.
  • the absolute amount 44 of the interference signal 36 is greater, the absolute amount 46 of the target signal 40 is scaled by a factor> 1 (eg 1.1 or 1.2) and compared again with the absolute amount 44 of the interference signal 36.
  • the mean value 80b of the discrete value range 80 is assigned as the preliminary weighting factor 51, otherwise the smallest value 80c.
  • the said cascaded greater than smaller comparisons with interim scaling can also be mathematically formulated as the above-described mapping of the quotient 50 to the discrete value range 80 for the preliminary weighting factor 51, but are sometimes easier in practice, e.g. on hard-wired circuits to implement.

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  • Acoustics & Sound (AREA)
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  • Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • General Health & Medical Sciences (AREA)
  • Otolaryngology (AREA)
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  • Audiology, Speech & Language Pathology (AREA)
  • Human Computer Interaction (AREA)
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  • Manufacturing & Machinery (AREA)
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EP21175709.1A 2020-06-18 2021-05-25 Procédé de réduction directionnelle du bruit pour un système auditif comprenant un dispositif auditif Pending EP3926982A3 (fr)

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US20210345042A1 (en) * 2020-08-14 2021-11-04 Gn Hearing A/S Hearing device with microphone switching and related method
DE102022111300A1 (de) 2022-05-06 2023-11-09 Elevear GmbH Vorrichtung zur Reduzierung des Rauschens bei der Wiedergabe eines Audiosignals mit einem Kopfhörer oder Hörgerät und entsprechendes Verfahren

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CN114120950B (zh) * 2022-01-27 2022-06-10 荣耀终端有限公司 一种人声屏蔽方法和电子设备

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CN102771144B (zh) 2010-02-19 2015-03-25 西门子医疗器械公司 用于方向相关空间噪声减低的设备和方法
DK2544462T3 (en) * 2011-07-04 2019-02-18 Gn Hearing As Wireless binaural compressor
DE102012206759B4 (de) * 2012-04-25 2018-01-04 Sivantos Pte. Ltd. Verfahren zum Steuern einer Richtcharakteristik und Hörsystem
DK3306956T3 (da) * 2016-10-05 2019-10-28 Oticon As En binaural stråleformerfiltreringsenhed, et høresystem og en høreanordning
DE102016225205A1 (de) * 2016-12-15 2018-06-21 Sivantos Pte. Ltd. Verfahren zum Bestimmen einer Richtung einer Nutzsignalquelle
DE102016225204B4 (de) * 2016-12-15 2021-10-21 Sivantos Pte. Ltd. Verfahren zum Betrieb eines Hörgerätes
EP4009667A1 (fr) * 2018-06-22 2022-06-08 Oticon A/s Appareil auditif comprenant un détecteur d'événement acoustique

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20210345042A1 (en) * 2020-08-14 2021-11-04 Gn Hearing A/S Hearing device with microphone switching and related method
US11653147B2 (en) * 2020-08-14 2023-05-16 Gn Hearing A/S Hearing device with microphone switching and related method
DE102022111300A1 (de) 2022-05-06 2023-11-09 Elevear GmbH Vorrichtung zur Reduzierung des Rauschens bei der Wiedergabe eines Audiosignals mit einem Kopfhörer oder Hörgerät und entsprechendes Verfahren

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US11570557B2 (en) 2023-01-31

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