WO2019086433A1 - Procédé de fonctionnement d'un système d'aide auditive et système d'aide auditive - Google Patents

Procédé de fonctionnement d'un système d'aide auditive et système d'aide auditive Download PDF

Info

Publication number
WO2019086433A1
WO2019086433A1 PCT/EP2018/079674 EP2018079674W WO2019086433A1 WO 2019086433 A1 WO2019086433 A1 WO 2019086433A1 EP 2018079674 W EP2018079674 W EP 2018079674W WO 2019086433 A1 WO2019086433 A1 WO 2019086433A1
Authority
WO
WIPO (PCT)
Prior art keywords
phase
microphone
resultant length
frequency
unbiased mean
Prior art date
Application number
PCT/EP2018/079674
Other languages
English (en)
Inventor
Lars Dalskov Mosgaard
Thomas Bo Elmedyb
Adam Westermann
Michael Johannes Pihl
Jakob Nielsen
Georg Stiefenhofer
Original Assignee
Widex A/S
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from DKPA201800462A external-priority patent/DK201800462A1/en
Application filed by Widex A/S filed Critical Widex A/S
Priority to US16/760,164 priority Critical patent/US11109164B2/en
Priority to DK18796003.4T priority patent/DK3704872T3/da
Priority to EP18796003.4A priority patent/EP3704872B1/fr
Publication of WO2019086433A1 publication Critical patent/WO2019086433A1/fr

Links

Classifications

    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/40—Arrangements for obtaining a desired directivity characteristic
    • H04R25/407—Circuits for combining signals of a plurality of transducers
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/41—Detection or adaptation of hearing aid parameters or programs to listening situation, e.g. pub, forest
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/43—Signal processing in hearing aids to enhance the speech intelligibility
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2460/00—Details of hearing devices, i.e. of ear- or headphones covered by H04R1/10 or H04R5/033 but not provided for in any of their subgroups, or of hearing aids covered by H04R25/00 but not provided for in any of its subgroups
    • H04R2460/01—Hearing devices using active noise cancellation
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • 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
    • 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
    • H04R25/554—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 using a wireless connection, e.g. between microphone and amplifier or using Tcoils
    • 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
    • H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04S—STEREOPHONIC SYSTEMS 
    • H04S1/00—Two-channel systems
    • H04S1/002—Non-adaptive circuits, e.g. manually adjustable or static, for enhancing the sound image or the spatial distribution
    • H04S1/005—For headphones
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04S—STEREOPHONIC SYSTEMS 
    • H04S2420/00—Techniques used stereophonic systems covered by H04S but not provided for in its groups
    • H04S2420/01—Enhancing the perception of the sound image or of the spatial distribution using head related transfer functions [HRTF's] or equivalents thereof, e.g. interaural time difference [ITD] or interaural level difference [ILD]

Definitions

  • the present invention relates to a method of operating a hearing aid system.
  • the present invention also relates to a hearing aid system adapted to carry out said method.
  • a hearing aid system is understood as meaning any device which provides an output signal that can be perceived as an acoustic signal by a user or contributes to providing such an output signal, and which has means which are customized to compensate for an individual hearing loss of the user or contribute to compensating for the hearing loss of the user.
  • They are, in particular, hearing aids which can be worn on the body or by the ear, in particular on or in the ear, and which can be fully or partially implanted.
  • some devices whose main aim is not to compensate for a hearing loss may also be regarded as hearing aid systems, for example consumer electronic devices (televisions, hi-fi systems, mobile phones, MP3 players etc.) provided they have, however, measures for compensating for an individual hearing loss.
  • a traditional hearing aid can be understood as a small, battery-powered, microelectronic device designed to be worn behind or in the human ear by a hearing-impaired user.
  • the hearing aid Prior to use, the hearing aid is adjusted by a hearing aid fitter according to a prescription.
  • the prescription is based on a hearing test, resulting in a so-called audiogram, of the performance of the hearing-impaired user's unaided hearing.
  • the prescription is developed to reach a setting where the hearing aid will alleviate a hearing loss by amplifying sound at frequencies in those parts of the audible frequency range where the user suffers a hearing deficit.
  • a hearing aid comprises one or more microphones, a battery, a microelectronic circuit comprising a signal processor, and an acoustic output transducer.
  • the signal processor is preferably a digital signal processor.
  • the hearing aid is enclosed in a casing suitable for fitting behind or in a human ear.
  • a hearing aid system may comprise a single hearing aid (a so called monaural hearing aid system) or comprise two hearing aids, one for each ear of the hearing aid user (a so called binaural hearing aid system).
  • the hearing aid system may comprise an external device, such as a smart phone having software applications adapted to interact with other devices of the hearing aid system.
  • hearing aid system device may denote a hearing aid or an external device.
  • BTE Behind-The-Ear
  • an electronics unit comprising a housing containing the major electronics parts thereof is worn behind the ear.
  • An earpiece for emitting sound to the hearing aid user is worn in the ear, e.g. in the concha or the ear canal.
  • a sound tube is used to convey sound from the output transducer, which in hearing aid terminology is normally referred to as the receiver, located in the housing of the electronics unit and to the ear canal.
  • a conducting member comprising electrical conductors conveys an electric signal from the housing and to a receiver placed in the earpiece in the ear.
  • Such hearing aids are commonly referred to as Receiver-In-The-Ear (RITE) hearing aids.
  • RITE Receiver-In-The-Ear
  • RIC Receiver-In-Canal
  • In-The-Ear (ITE) hearing aids are designed for arrangement in the ear, normally in the funnel-shaped outer part of the ear canal.
  • ITE hearing aids In a specific type of ITE hearing aids the hearing aid is placed substantially inside the ear canal. This category is sometimes referred to as Completely-In-Canal (CIC) hearing aids.
  • CIC Completely-In-Canal
  • This type of hearing aid requires an especially compact design in order to allow it to be arranged in the ear canal, while accommodating the components necessary for operation of the hearing aid.
  • Hearing loss of a hearing impaired person is quite often frequency-dependent. This means that the hearing loss of the person varies depending on the frequency. Therefore, when compensating for hearing losses, it can be advantageous to utilize frequency- dependent amplification.
  • Hearing aids therefore often provide to split an input sound signal received by an input transducer of the hearing aid, into various frequency intervals, also called frequency bands, which are independently processed. In this way, it is possible to adjust the input sound signal of each frequency band individually to account for the hearing loss in respective frequency bands.
  • a number of hearing aid features such as beamforming, noise reduction schemes and compressor settings are not universally beneficial and preferred by all hearing aid users. Therefore detailed knowledge about a present acoustic situation is required to obtain maximum benefit for the individual user. Especially, knowledge about the number of talkers (or other target sources) present and their position relative to the hearing aid user and knowledge about the diffuse noise are relevant. Having access to this knowledge in real-time can be used to classify the general sound environment but can also be used to classify specific parts of the sound environment, both of which can be used to effectively help the user by improving performance of at least the above mentioned hearing aid features.
  • the invention in a first aspect, provides a method of operating a hearing aid system comprising the steps of:
  • This provides an improved method of operating a hearing aid system with respect to sound classification.
  • the invention in a second aspect, provides a hearing aid comprising a first and a second microphone, a digital signal processor and an electrical-acoustical output transducer;
  • the digital signal processor is configured to apply a frequency dependent gain that is adapted to at least one of suppressing noise and alleviating a hearing deficit of an individual wearing the hearing aid system, and;
  • the digital signal processor is adapted to determine a multitude of samples of the inter-microphone phase difference between the first and the second acoustical- electrical input transducers, and;
  • the digital signal processor is adapted to determine at least one of an unbiased mean phase and a resultant length from the multitude of samples of the inter- microphone phase difference, and;
  • the digital signal processor is further adapted to use at least one of the unbiased mean phase and the resultant length to classify a sound environment.
  • This provides a hearing aid system with improved means for operating a hearing aid system with respect to sound classification.
  • the invention in a third aspect, provides a non-transitory computer readable medium carrying instructions which, when executed by a computer, cause the following method to be performed:
  • the invention in a fourth aspect provides an internet server comprising a downloadable application that may be executed by a personal communication device, wherein the downloadable application is adapted to cause the following method to be performed:
  • Fig. 1 illustrates highly schematically a directional system according to an
  • Fig. 2 illustrates highly schematically a hearing aid system according to an
  • Fig. 3 illustrates highly schematically a phase versus frequency plot.
  • signal processing is to be understood as any type of hearing aid system related signal processing that includes at least: beam forming, noise reduction, speech enhancement and hearing compensation.
  • beam former and directional system may be used interchangeably.
  • Fig. 1 illustrates highly schematically a directional system 100 suitable for implementation in a hearing aid system according to an embodiment of the invention.
  • the directional system 100 takes as input, the digital output signals, at least, derived from the two acoustical-electrical input transducers 101a-b.
  • the acoustical-electrical input transducers 101a-b which in the following may also be denoted microphones, provide analog output signals that are converted into digital output signals by analog-digital converters (ADC) and subsequently provided to a filter bank 102 adapted to transform the signals into the time-frequency domain.
  • ADC analog-digital converters
  • One specific advantage of transforming the input signals into the time-frequency domain is that both the amplitude and phase of the signals become directly available in the provided individual time-frequency bins.
  • a Fast Fourier Transform may be used for the transformation and in variations other time-frequency domain transformations can be used such as a Discrete Fourier Transform (DTF), a polyphase filterbank or a Discrete Cosine Transformation.
  • DTF Discrete Fourier Transform
  • DTF Discrete Fourier Transform
  • polyphase filterbank a polyphase filterbank
  • Discrete Cosine Transformation a Discrete Cosine Transformation
  • the output signals from the filter bank 102 will primarily be denoted input signals because these signals represent the primary input signals to the directional system 100.
  • digital input signal may be used interchangeably with the term input signal.
  • all other signals referred to in the present disclosure may or may not be specifically denoted as digital signals.
  • input signal, digital input signal, frequency band input signal, sub-band signal and frequency band signal may be used interchangeably in the following and unless otherwise noted the input signals can generally be assumed to be frequency band signals independent on whether the filter bank 102 provide frequency band signals in the time domain or in the time-frequency domain.
  • the microphones 101a-b are omni-directional unless otherwise mentioned.
  • the input signals are not transformed into the time-frequency domain. Instead the input signals are first transformed into a number of frequency band signals by a time-domain filter bank comprising a multitude of time-domain bandpass filters, such as Finite Impulse Response bandpass filters and subsequently the frequency band signals are compared using correlation analysis wherefrom the phase is derived. Both the digital input signals are branched, whereby the input signals, in a first branch, is provided to a Fixed Beam Former (FBF) unit 103, and, in a second branch, is provided to a blocking matrix 104.
  • BMF Fixed Beam Former
  • the digital input signals are provided to the blocking matrix 104 wherein an assumed or estimated target signal is removed and whereby an estimated noise signal that in the following will be denoted U may be determined from the equation:
  • the blocking matrix may be given by:
  • D is the Inter-Microphone Transfer Function (which in the following may be abbreviated IMTF) that represents the transfer function between the two microphones with respect to a specific source.
  • IMTF Inter-Microphone Transfer Function
  • the IMTF may interchangeably also be denoted the steering vector.
  • the digital input signals are provided to the FBF unit 103 that provides an omni signal Q given by the equation:
  • the vector represents the FBF unit 103 that may be given by:
  • the estimated noise signal U provided by the blocking matrix 104 is filtered by the adaptive filter 105 and the resulting filtered estimated noise signal is subtracted, using the subtraction unit 106, from the omni-signal Q provided in the first branch in order to remove the noise, and the resulting beam formed signal E is provided to further processing in the hearing aid system, wherein the further processing may comprise application of a frequency dependent gain in order to alleviate a hearing loss of a specific hearing aid system user and/or processing directed at reducing noise or improving speech intelligibility.
  • the resulting beam formed signal E may therefore be expressed using the equation:
  • H represents the adaptive filter 105, which in the following may also interchangeably be denoted the active noise cancellation filter.
  • the input signal vector and the output signal E of the directional system 100 may be expressed as:
  • subscript n represents noise and subscript t represents the target signal. It follows that the second branch perfectly cancels the target signal and consequently the target signal is, under ideal conditions, fully preserved in the output signal E of the directional system 100.
  • the directional system 100 under ideal conditions, in the LMS sense will cancel all the noise without compromising the target signal.
  • the blocking matrix 104 needs to also take into account not only the direct sound from a target source but also the early reflections from the target source, in order to ensure optimum
  • this may be achieved by considering the IMTF for a given target sound source.
  • the properties of periodic variables need to be considered.
  • periodic variables will due to mathematically convenience be described as complex numbers.
  • An estimate of the IMTF for a given target sound source may therefore be given as a complex number that in polar representation has an amplitude A and a phase ⁇ .
  • the average of a multitude of IMTF estimates may be given by:
  • ( ) is the average operator
  • n represents the number of IMTF estimates used for the averaging
  • R A is an averaged amplitude that depends on the phase and that may assume values in the interval [0, (A)]
  • R A is an averaged amplitude that depends on the phase and that may assume values in the interval [0, (A)]
  • R A is an averaged amplitude that depends on the phase and that may assume values in the interval [0, (A)]
  • R A is an averaged amplitude that depends on the phase and that may assume values in the interval [0, (A)]
  • the amplitude weighting providing the weighted mean phase will generally result in the weighted mean phase being different from the unbiased mean phase that is defined by:
  • Equation (8) ( ) is the average operator and n represents the number of inter- microphone phase difference samples used for the averaging. It follows that the unbiased mean phase can be estimated by averaging a multitude of inter-microphone phase difference samples.
  • R is denoted the resultant length and the resultant length R provides information on how closely the individual phase estimates ⁇ i are grouped together and the circular variance V and the resultant length R are related by:
  • the inventors have found that the information regarding the amplitude relation, which is lost in the determination of the unbiased mean phase the resultant length R and the circular variance V turns out to be advantageous because more direct access to the underlying phase probability distribution is provided.
  • the present invention provides an alternative method of estimating the phase of the steering vector which is optimal in the LMS sense, when the normalized input signals are considered as opposed to the input signals considered alone.
  • this optimal steering vector based on normalized input signals will be denoted D N (f):
  • the amplitude part is estimated simply by selecting at least one set of input signals that has contributed to providing a high value of the resultant length, wherefrom it may be assumed that the input signals are not primarily noise and that therefore the biased mean amplitude corresponding to said set of input signals is relatively accurate. Furthermore the value of unbiased mean phase can be used to select between different target sources.
  • the biased mean amplitude is used to control the directional system without considering the corresponding resultant length.
  • the amplitude part is determined by transforming the unbiased mean phase using a transformation selected from a group comprising the Hilbert transformation.
  • a directional system with improved performance is obtained.
  • the method has been disclosed in connection with a Generalized Sidelobe Canceller (GSC) design, but may in variations also be applied to improve performance of other types of directional systems such as a multi-channel Wiener filter, a Minimum Mean Squared Error (MMSE) system and a Linearly Constrained Minimum Variance (LCMV) system.
  • GSC Generalized Sidelobe Canceller
  • MMSE Minimum Mean Squared Error
  • LCMV Linearly Constrained Minimum Variance
  • the method may also be applied for directional system that is not based on energy minimization.
  • the determination of the amplitude and phase of the IMTF according to the present invention can be determined purely based on input signals and as such is highly flexible with respect to its use in various different directional systems.
  • the input signals i.e. the sound environment
  • the two main sources of dynamics are the temporal and spatial dynamics of the sound environment.
  • speech the duration of a short consonant may be as short as only 5 milliseconds, while long vowels may have a duration of up to 200 milliseconds depending on the specific sound.
  • the spatial dynamics is a consequence of relative movement between the hearing aid user and surrounding sound sources.
  • speech is considered quasi stationary for a duration in the range between say 20 and 40 milliseconds and this includes the impact from spatial dynamics.
  • the duration of the involved time windows are as long as possible, but it is, on the other hand, detrimental if the duration is so long that it covers natural speech variations or spatial variations and therefore cannot be considered quasi-stationary.
  • a first time window is defined by the transformation of the digital input signals into the time-frequency domain and the longer the duration of the first time window the higher the frequency resolution in the time-frequency domain, which obviously is advantageous. Additionally, the present invention requires that the determination of an unbiased mean phase or the resultant length of the IMTF for a particular angular direction or the final estimate of an inter- microphone phase difference is based on a calculation of an expectation value and it has been found that the number of individual samples used for calculation of the expectation value preferably exceeds at least 5.
  • the combined effect of the first time window and the calculation of the expectation value provides an effective time window that is shorter than 40 milliseconds or in the range between 5 and 200 milliseconds such that the sound environment in most cases can be considered quasi-stationary.
  • improved accuracy of the unbiased mean phase or the resultant length may be provided by obtaining a multitude of successive samples of the unbiased mean phase and the resultant length, in the form of a complex number using the methods according to the present invention and subsequently adding these successive estimates (i.e. the complex numbers) and normalizing the result of the addition with the number of added estimates.
  • This embodiment is particularly advantageous in that the resultant length effectively weights the samples that have a high probability of comprising a target source, while estimates with a high probability of mainly comprising noise will have a negligible impact on the final value of the unbiased mean phase of the IMTF or inter-microphone phase difference because the samples are characterized by having a low value of the resultant length.
  • this method it therefore becomes possible to achieve pseudo time windows with a duration up to say several seconds or even longer and the improvements that follows therefrom, despite the fact that neither the temporal nor the spatial variations can be considered quasi- stationary.
  • At least one or at least not all of the successive complex numbers representing the unbiased mean phase and the resultant length are used for improving the estimation of the unbiased mean phase of the IMTF or inter-microphone phase difference, wherein the selection of the complex numbers to be used are based on an evaluation of the corresponding resultant length (i.e. the variance) such that only complex numbers representing a high resultant length are considered.
  • the estimation of the unbiased mean phase of the IMTF or inter-microphone phase difference is additionally based on an evaluation of the value of the individual samples of the unbiased mean phase such that only samples representing the same target source are combined.
  • speech detection may be used as input to determine a preferred unbiased mean phase for controlling a directional system, e.g. by giving preference to target sources positioned at least approximately in front of the hearing aid system user, when speech is detected. In this way it may be avoided that a directional system enhances the direct sound from from an undesired source.
  • the angular direction of a target source which may also be denoted the direction of arrival (DOA) is derived from the unbiased mean phase and used for various types of signal processing.
  • DOA direction of arrival
  • the resultant length can be used to determine how to weight information, such as a determined DOA of a target source, from each hearing aid of a binaural hearing aid system.
  • the resultant length can be used to compare or weight information obtained from a multitude of microphone pairs, such as the multitude of microphone pairs that are available in e.g. a binaural hearing aid system comprising two hearing aids each having two microphones.
  • the determination of a an angular direction of a target source is provided by combining a monaurally determined unbiased mean phase with a binaurally determined unbiased mean phase, whereby the symmetry ambiguity that results when translating an estimated phase to a target direction may be resolved.
  • Fig. 2 illustrates highly schematically a hearing aid system 200 according to an embodiment of the invention. The components that have already been described with reference to Fig. 1 are given the same numbering as in Fig. 1.
  • the hearing aid system 200 comprises a first and a second acoustical-electrical input transducers 101a-b, a filter bank 102, a digital signal processor 201, an electrical- acoustical output transducer 202 and a sound classifier 203.
  • the acoustical-electrical input transducers 101a-b which in the following may also be denoted microphones, provide analog output signals that are converted into digital output signals by analog-digital converters (ADC) and subsequently provided to a filter bank 102 adapted to transform the signals into the time-frequency domain.
  • ADC analog-digital converters
  • One specific advantage of transforming the input signals into the time-frequency domain is that both the amplitude and phase of the signals become directly available in the provided individual time-frequency bins.
  • the input signals 101-a and 101-b are branched and provided both to the digital signal processor 201 and to a sound classifier 203.
  • the digital signal processor 201 may be adapted to provide various forms of signal processing including at least: beam forming, noise reduction, speech enhancement and hearing compensation.
  • the sound classifier 203 is configured to classify the current sound environment of the hearing aid system 200 and provide sound classification information to the digital signal processor such that the digital signal processor can operate dependent on the current sound environment.
  • Fig. 3 illustrates highly schematically a map of values of the unbiased mean phase as a function of frequency in order to provide a phase versus frequency plot.
  • the phase versus frequency plot can be used to identify a direct sound if said mapping provides a straight line or at least a continuous curve in the phase versus frequency plot.
  • the curve 301 -A represents direct sound from a target positioned directly in front of the hearing aid system user assuming a contemporary standard hearing aid having two microphones positioned along the direction of the hearing aid system users nose.
  • the curve 301-B represents direct sound from a target directly behind the hearing aid system user.
  • the angular direction of the direct sound from a given target source may be determined from the fact that the slope of the interpolated straight line representing the direct sound is given as:
  • the phase versus frequency plot can be used to identify a diffuse noise field if said mapping provides a uniform distribution, for a given frequency, within a coherent region, wherein the coherent region 303 is defined as the area in the phase versus frequency plot that is bounded by the at least continuous curves defining direct sounds coming directly from the front and the back direction respectively and the curves defining a constant phase of + ⁇ and - ⁇ respectively.
  • the phase versus frequency plot can be used to identify a random or incoherent noise field if said mapping provides a uniform distribution, for a given frequency, within a full phase region defined as the area in the phase versus frequency plot that is bounded by the two straight lines defining a constant phase of + ⁇ and - ⁇ respectively.
  • any data points outside the coherent region, i.e. inside the incoherent regions 302-a and 302-b will represent a random or incoherent noise field.
  • a diffuse noise can be identified by in a first step transforming a value of the resultant length to reflect a transformation of the unbiased mean phase from inside the coherent region and onto the full phase region, and in a second step identifying a diffuse noise field if the transformed value of the resultant length, for at least one frequency range, is below a transformed resultant length diffuse noise trigger level. More specifically the step of transforming the values of the resultant length to reflect a transformation of the unbiased mean phase from inside the coherent region and onto the full phase region comprises the step of determining the values in accordance with the formula:
  • ⁇ 1 (f) and M 2 (f) represent the frequency dependent first and second input signals respectively.
  • identification of a diffuse, random or incoherent noise field can be made if a value of the resultant length, for at least one frequency range, is below a resultant length noise trigger level.
  • identification of a direct sound can be made if a value of the resultant length, for at least one frequency range, is above a resultant length direct sound trigger level.
  • the trigger levels are replaced by a continuous function, which maps the resultant length or the unwrapped resultant length to a signal-to-noise-ratio, wherein the noise may be diffuse or incoherent.
  • improved accuracy of the determined unbiased mean phase is achieved by at least one of averaging and fitting a multitude of determined unbiased mean phases across at least one of time and frequency by weighting the determined unbiased mean phases with the correspondingly determined resultant length.
  • the resultant length may be used to perform hypothesis testing of probability distributions for a correspondingly determined unbiased mean phase.
  • corresponding values, in time and frequency, of the unbiased mean phase and the resultant length can be used to identify and distinguish between at least two target sources, based on identification of direct sound comprising at least two different values of the unbiased mean phase.
  • corresponding values, in time and frequency, of the unbiased mean phase and the resultant length can be used to estimate whether a distance to a target source is increasing or decreasing based on whether the value of the resultant length is decreasing or increasing respectively. This can be done because the reflections, at least while being indoors in say some sort of room will tend to dominate the direct sound, when the target source moves away from the hearing aid system user. This can be very advantageous in the context of beam former control because speech intelligibility can be improved by allowing at least the early reflections to pass through the beam former.
  • the methods and selected parts of the hearing aid according to the disclosed embodiments may also be implemented in systems and devices that are not hearing aid systems (i.e.
  • the hearing aid system needs not comprise a traditional loudspeaker as output transducer.
  • hearing aid systems that do not comprise a traditional loudspeaker are cochlear implants, implantable middle ear hearing devices (IMEHD), bone-anchored hearing aids (BAHA) and various other electro-mechanical transducer based solutions including e.g. systems based on using a laser diode for directly inducing vibration of the eardrum.
  • IMEHD implantable middle ear hearing devices
  • BAHA bone-anchored hearing aids
  • various other electro-mechanical transducer based solutions including e.g. systems based on using a laser diode for directly inducing vibration of the eardrum.
  • the various embodiments of the present embodiment may be combined unless it is explicitly stated that they cannot be combined.
  • a non-transitory computer readable medium carrying instructions which, when executed by a computer, cause the methods of the disclosed embodiments to be performed.

Landscapes

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

Abstract

L'invention concerne un procédé de fonctionnement d'un système d'aide auditive afin de fournir une classification d'environnement sonore améliorée et un système d'aide auditive (200) de mise en œuvre du procédé.
PCT/EP2018/079674 2017-10-31 2018-10-30 Procédé de fonctionnement d'un système d'aide auditive et système d'aide auditive WO2019086433A1 (fr)

Priority Applications (3)

Application Number Priority Date Filing Date Title
US16/760,164 US11109164B2 (en) 2017-10-31 2018-10-30 Method of operating a hearing aid system and a hearing aid system
DK18796003.4T DK3704872T3 (da) 2017-10-31 2018-10-30 Fremgangsmåde til betjening af et høreapparatsystem og et høreapparatsystem
EP18796003.4A EP3704872B1 (fr) 2017-10-31 2018-10-30 Procédé de fonctionnement d'un système de prothèse auditive

Applications Claiming Priority (8)

Application Number Priority Date Filing Date Title
DKPA201700611 2017-10-31
DKPA201700611 2017-10-31
DKPA201700612 2017-10-31
DKPA201700612 2017-10-31
DKPA201800462 2018-08-15
DKPA201800465 2018-08-15
DKPA201800462A DK201800462A1 (en) 2017-10-31 2018-08-15 METHOD OF OPERATING A HEARING AID SYSTEM AND A HEARING AID SYSTEM
DKPA201800465 2018-08-15

Publications (1)

Publication Number Publication Date
WO2019086433A1 true WO2019086433A1 (fr) 2019-05-09

Family

ID=64051569

Family Applications (4)

Application Number Title Priority Date Filing Date
PCT/EP2018/079671 WO2019086432A1 (fr) 2017-10-31 2018-10-30 Procédé de fonctionnement d'un système d'aide auditive et système d'aide auditive
PCT/EP2018/079681 WO2019086439A1 (fr) 2017-10-31 2018-10-30 Procédé de fonctionnement d'un système d'aide auditive et système d'aide auditive
PCT/EP2018/079676 WO2019086435A1 (fr) 2017-10-31 2018-10-30 Procédé de fonctionnement d'un système d'aide auditive et système d'aide auditive
PCT/EP2018/079674 WO2019086433A1 (fr) 2017-10-31 2018-10-30 Procédé de fonctionnement d'un système d'aide auditive et système d'aide auditive

Family Applications Before (3)

Application Number Title Priority Date Filing Date
PCT/EP2018/079671 WO2019086432A1 (fr) 2017-10-31 2018-10-30 Procédé de fonctionnement d'un système d'aide auditive et système d'aide auditive
PCT/EP2018/079681 WO2019086439A1 (fr) 2017-10-31 2018-10-30 Procédé de fonctionnement d'un système d'aide auditive et système d'aide auditive
PCT/EP2018/079676 WO2019086435A1 (fr) 2017-10-31 2018-10-30 Procédé de fonctionnement d'un système d'aide auditive et système d'aide auditive

Country Status (1)

Country Link
WO (4) WO2019086432A1 (fr)

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
KR102093366B1 (ko) * 2020-01-16 2020-03-25 한림국제대학원대학교 산학협력단 귀 인상 정보를 바탕으로 관리되는 보청기 적합관리 시스템의 제어 방법, 장치 및 프로그램
KR102093369B1 (ko) * 2020-01-16 2020-05-13 한림국제대학원대학교 산학협력단 확장역치레벨에 대한 최적증폭을 위한 보청기 시스템의 제어 방법, 장치 및 프로그램

Families Citing this family (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US11818548B2 (en) 2019-09-30 2023-11-14 Widex A/S Method of operating a binaural ear level audio system and a binaural ear level audio system
DE102022201706B3 (de) 2022-02-18 2023-03-30 Sivantos Pte. Ltd. Verfahren zum Betrieb eines binauralen Hörvorrichtungssystems und binaurales Hörvorrichtungssystem

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2009034524A1 (fr) * 2007-09-13 2009-03-19 Koninklijke Philips Electronics N.V. Appareil et procede de formation de faisceau audio
US20090202091A1 (en) * 2008-02-07 2009-08-13 Oticon A/S Method of estimating weighting function of audio signals in a hearing aid
US20150289064A1 (en) * 2014-04-04 2015-10-08 Oticon A/S Self-calibration of multi-microphone noise reduction system for hearing assistance devices using an auxiliary device

Family Cites Families (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB0720473D0 (en) * 2007-10-19 2007-11-28 Univ Surrey Accoustic source separation
DK2449798T4 (da) * 2009-08-11 2020-12-21 Sivantos Pte Ltd System og fremgangsmåde til estimering af en lyds ankomstretning
EP2882203A1 (fr) * 2013-12-06 2015-06-10 Oticon A/s Dispositif d'aide auditive pour communication mains libres
DK3148213T3 (en) * 2015-09-25 2018-11-05 Starkey Labs Inc DYNAMIC RELATIVE TRANSFER FUNCTION ESTIMATION USING STRUCTURED "SAVING BAYESIAN LEARNING"

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2009034524A1 (fr) * 2007-09-13 2009-03-19 Koninklijke Philips Electronics N.V. Appareil et procede de formation de faisceau audio
US20090202091A1 (en) * 2008-02-07 2009-08-13 Oticon A/S Method of estimating weighting function of audio signals in a hearing aid
US20150289064A1 (en) * 2014-04-04 2015-10-08 Oticon A/S Self-calibration of multi-microphone noise reduction system for hearing assistance devices using an auxiliary device

Non-Patent Citations (2)

* Cited by examiner, † Cited by third party
Title
CABOT: "AN INTRODUCTION TO CIRCULAR STATISTICS AND ITS APPLICATION TO SOUND LOCALIZATION EXPERIMENTS", AES, November 1977 (1977-11-01), XP002788240, Retrieved from the Internet <URL:http://www.aes.org/tmpFiles/elib/20190109/3062.pdf> [retrieved on 201901] *
R. KUTIL: "Biased and unbiased estimation of the circular mean resultant length and its variance", STATISTICS, vol. 46, no. 4, August 2012 (2012-08-01), pages 549 - 561, XP002788241, Retrieved from the Internet <URL:https://www.tandfonline.com/doi/pdf/10.1080/02331888.2010.543463?needAccess=true> [retrieved on 201901] *

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
KR102093366B1 (ko) * 2020-01-16 2020-03-25 한림국제대학원대학교 산학협력단 귀 인상 정보를 바탕으로 관리되는 보청기 적합관리 시스템의 제어 방법, 장치 및 프로그램
KR102093369B1 (ko) * 2020-01-16 2020-05-13 한림국제대학원대학교 산학협력단 확장역치레벨에 대한 최적증폭을 위한 보청기 시스템의 제어 방법, 장치 및 프로그램

Also Published As

Publication number Publication date
WO2019086439A1 (fr) 2019-05-09
WO2019086432A1 (fr) 2019-05-09
WO2019086435A1 (fr) 2019-05-09

Similar Documents

Publication Publication Date Title
US11109164B2 (en) Method of operating a hearing aid system and a hearing aid system
CN104902418B (zh) 用于估计目标和噪声谱方差的多传声器方法
CN110035367B (zh) 反馈检测器及包括反馈检测器的听力装置
EP2899996B1 (fr) Amélioration du signal à l&#39;aide de diffusion en continu sans fil
US10631105B2 (en) Hearing aid system and a method of operating a hearing aid system
CN107431867B (zh) 用于快速识别自身语音的方法和设备
WO2019086433A1 (fr) Procédé de fonctionnement d&#39;un système d&#39;aide auditive et système d&#39;aide auditive
EP2999235B1 (fr) Dispositif auditif comprenant un formeur de faisceaux gsc
WO2020035158A1 (fr) Procédé de fonctionnement d&#39;un système d&#39;aide auditive et système d&#39;aide auditive
EP3837861B1 (fr) Procédé de fonctionnement d&#39;un système de prothèse auditive
JP2018501727A (ja) 補聴器システムの動作方法および補聴器システム
DK201800462A1 (en) METHOD OF OPERATING A HEARING AID SYSTEM AND A HEARING AID SYSTEM

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 18796003

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE

ENP Entry into the national phase

Ref document number: 2018796003

Country of ref document: EP

Effective date: 20200602