EP3772861A1 - Procédé de traitement directionnel du signal pour un appareil auditif - Google Patents

Procédé de traitement directionnel du signal pour un appareil auditif Download PDF

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Publication number
EP3772861A1
EP3772861A1 EP20185489.0A EP20185489A EP3772861A1 EP 3772861 A1 EP3772861 A1 EP 3772861A1 EP 20185489 A EP20185489 A EP 20185489A EP 3772861 A1 EP3772861 A1 EP 3772861A1
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Prior art keywords
signal
directional
parameter
generated
input
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EP20185489.0A
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German (de)
English (en)
Inventor
Eghart Fischer
Homayoun KAMKAR-PARSI
Jens Hain
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Sivantos Pte Ltd
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Sivantos Pte Ltd
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Publication of EP3772861A1 publication Critical patent/EP3772861A1/fr
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    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/40—Arrangements for obtaining a desired directivity characteristic
    • H04R25/407—Circuits for combining signals of a plurality of transducers
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • 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
    • H04R1/00—Details of transducers, loudspeakers or microphones
    • H04R1/20—Arrangements for obtaining desired frequency or directional characteristics
    • H04R1/32—Arrangements for obtaining desired frequency or directional characteristics for obtaining desired directional characteristic only
    • 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
    • H04R25/45—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback
    • 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

Definitions

  • the invention relates to a method for directional signal processing for a hearing aid, a first input signal being generated from a sound signal of the surroundings by a first input transducer of the hearing aid, a second input signal being generated from the sound signal of the surroundings by a second input transducer of the hearing aid of the first input signal and a first directional signal is generated based on the second input signal, which has a maximum attenuation in a first direction, and an output signal of the hearing aid is generated based on the first directional signal.
  • ambient sound is converted into at least one input signal by means of at least one input transducer, which is processed depending on a hearing impairment of the wearer to be corrected in a frequency band-specific manner and in particular individually tailored to the wearer and is also amplified.
  • the processed signal is converted into an output sound signal via an output transducer of the hearing aid, which is sent to the wearer's hearing.
  • Hearing aids with two or more input transducers in which two or more corresponding input signals for further processing are generated from the ambient sound, represent an advantageous development.
  • This further processing of the input signals generally includes directional signal processing, ie the formation of directional signals from the input signals, the different directional effects mostly being used to produce a Useful signal source - usually a speaker in the vicinity of the hearing aid wearer - to highlight and / or to suppress background noise.
  • the so-called adaptive directional microphone in which a directional signal is generated in such a way that it has a maximum attenuation in the direction of an assumed, localizable interference signal source, is of particular importance.
  • the assumption used for this is mostly that noises occurring from the area behind the wearer of the hearing aid, that is to say in his / her rear half-space, are basically to be treated as interfering noises.
  • conventional directional microphone algorithms usually minimize the signal energy from the rear half-space in order to generate the directional signal with the desired attenuation properties.
  • the directional signal In the direction of the maximum attenuation, the directional signal has in particular a so-called "notch", i.e. a total ("infinite") attenuation. In the ideal case, the sound of the localized noise source is thus completely masked out of the directional signal.
  • the invention is based on the object of specifying a method for signal processing for a hearing aid, by means of which, when directional microphones are used, potentially relevant sound signals from a non-frontal direction and in particular from the rear half-space are not completely eliminated.
  • the stated object is achieved by a method for directional signal processing for a hearing aid, with a first input transducer of the hearing aid from a sound signal from the environment Input signal is generated, a second input signal is generated from the sound signal of the environment by a second input transducer of the hearing aid, a forward signal and a backward signal are generated from the first input signal and the second input signal, and a first directional parameter as a linear factor of a linear combination of the forward signal and the backward signal is determined in such a way that a first directional signal resulting from this linear combination has a maximum attenuation in a first direction.
  • a correction parameter is determined in such a way that a second directional signal as a linear combination formed from the first directional signal and an omnidirectional signal with the correction parameter as a linear factor has a defined attenuation in the first direction, the second directional signal consisting of the forward signal and the The backward signal is generated based on the first directional parameter and the correction parameter or from the first directional signal and the omnidirectional signal based on the correction parameter, and an output signal of the hearing aid is generated based on the second directional signal, which is preferably converted into an output sound signal by an output transducer of the hearing aid.
  • An input transducer in this case includes in particular an electroacoustic transducer which is set up to generate a corresponding electrical signal from a sound signal.
  • Preprocessing e.g. in the form of a linear pre-amplification and / or an A / D conversion, preferably also takes place when the first or second input signal is generated by the respective input converter.
  • the generation of the forward signal or the backward signal from the first and the second input signal preferably includes that the signal components of the first and the second input signal are included in the forward signal and in the backward signal, and thus in particular the first and the second input signal not both at the same time for generating control parameters etc., which are applied to signal components of other signals.
  • the signal components of the first input signal, and particularly preferably also the signal components of the second input signal are included linearly in the forward signal or in the reverse signal. The same applies to a generation of the second directional signal based on the forward signal and the backward signal, and possibly for further signals and their corresponding generation.
  • the generation of a signal can also take place from the generating signals, such as the forward signal and the backward signal, in such a way that one or more intermediate signals are initially formed from the said generating signals in the course of signal processing, from which then the generated signal (e.g. the second directional signal) is formed.
  • the signal components of the generating signals i.e. the forward and backward signals in the present example, are then initially included in the respective intermediate signal, and the signal components of the respective intermediate signal are then included in the generated signal, i.e. in the present case in the second directional signal, so that the signal components the generating signals (e.g.
  • the forward and backward signal are "passed through” via the respective intermediate signal to the generated signal (e.g. the second directional signal), and if necessary, amplified in frequency bands, partially delayed against each other or weighted differently from each other, etc. .
  • a forward signal here includes in particular a directional signal with a non-trivial directional characteristic which, on average, has a higher sensitivity to a standardized test sound of a predetermined level in a front half space of the hearing aid than in a rear half space.
  • the direction of maximum sensitivity of the forward signal is preferably also in the front half space, in particular in the forward direction (i.e. at 0 ° with respect to a preferred direction of the hearing aid), while a direction of minimum sensitivity of the forward signal is in the rear half space, in particular in the backward direction (i.e. at 180 ° with respect to a preferred direction of the hearing aid).
  • the reverse signal Preferably, the same applies to the reverse signal, with interchangeability of the front and rear half-spaces or the forward and backward directions.
  • the front and rear half-spaces and the forward and backward directions of the hearing aid are preferably defined by a preferred direction of the hearing aid which, when the hearing aid is worn by the wearer as intended, preferably coincides with its frontal direction. Deviations from this due to inaccurate adjustment when wearing should remain unaffected.
  • the forward and reverse signals are symmetrical to one another with respect to a plane of symmetry perpendicular to said preferred direction.
  • the directional characteristic of the forward signal is given, for example, in an advantageous embodiment by a cardioid, while in this embodiment the directional characteristic of the backward signal is given by an anti-cardioid.
  • the first directional parameter a1 can be determined, for example by minimizing the signal energy of the linear combination Z1 + a1 ⁇ Z2 (with Z1 as the forward signal and Z2 as the backward signal) or by other methods of optimization or adaptive directional microphone, without this from the linear combination resulting signal, which corresponds to the first directional signal, would experience further use in the course of the further process.
  • the second directional signal is generated directly from the forward signal and the reverse signal.
  • the first directional parameter is set by the aforementioned minimization of the signal energy or by other methods of optimization such that the resulting first directional signal, even if it is not used any further, has the maximum attenuation in the first direction as required, in particular if this is due to the Direction of a dominant sound source is given.
  • a maximum attenuation of the first directional signal is to be understood here in particular as meaning that the relevant directional characteristic has a sensitivity in the respective direction which is local, preferably global Has minimum.
  • the first directional signal thus has a non-trivial directional characteristic and thus a sensitivity that is variable across the room to a normalized test sound predetermined level.
  • the first directional signal preferably has a “notch” in the first direction with a total or quasi-total attenuation, that is to say by at least 15 dB, preferably by at least 20 dB.
  • the omnidirectional signal preferably has an angle-independent sensitivity to a standardized test sound.
  • the second directional signal is actually formed as a linear combination, in particular a convex superimposition of the first directional signal and the omnidirectional signal with the correction parameter as a linear factor or convexity parameter. Rather, the correction parameter is selected such that a second directional signal generated as required has the required, defined relative attenuation in the first direction.
  • the actual generation of the second directional signal takes place in particular by the described linear combination or convex superimposition of the omnidirectional signal with the first directional signal using the correction parameter, or alternatively by a linear combination of the forward signal and the reverse signal.
  • the dependence of the second directional signal on the first directional parameter takes place implicitly in this case via the first directional signal.
  • the defined relative attenuation that the second directional signal has in the first direction is to be understood here in particular as meaning that the second directional signal has a sensitivity in the first direction that is around a factor determined in particular by the correction parameter is lower than the maximum sensitivity.
  • the defined relative attenuation thus means, in particular, an attenuation by a factor or in dB, which can preferably be specified immediately if the correction parameter is known.
  • the value of the relative attenuation of the second directional signal is also 120 ° - so the first direction - set towards a maximum sensitivity of the signals.
  • the correction parameter e directly indicates the arithmetical component of the first directional signal in the second directional signal. Since its attenuation in the first direction is in the ideal case total, i.e. infinite, the sensitivity of the second directional signal in the first direction is in the ideal case completely determined by the component (1-e) of the omnidirectional signal om.
  • the correction parameter is determined in particular as a function of acoustic parameters, which can be monitored using the two input signals or signals derived from the input signals, such as the forward and backward signals, and generally using a signal that characterizes the sound signal of the environment , and which have, in particular, quantifiable information about the background noise character of a non-frontal sound signal, that is to say in particular also for a sound signal from the rear half-space.
  • Such a meaningfulness can be given, for example, by a background noise level, by a signal-to-noise ratio (SNR), or by a stationarity of the noise to be examined, with an examination
  • SNR signal-to-noise ratio
  • Stationarity is preferably accompanied by an examination of the half-space in which a dominant, non-frontal sound source is located.
  • the method can be used to mix take place with the omnidirectional signal in such a way that the resulting second directional signal is weakened by a defined factor in the first direction, and thus the sound of the sound source is no longer maximally or completely suppressed, but remains audible to the wearer of the hearing aid.
  • the mixing of the omnidirectional signal with the first directional signal can be configured in such a way that a particularly high proportion of the former is included in the second directional signal in order not to suppress the signal contributions of this speaker speaking behind the wearer by the first directional signal. This applies in particular when the first directional signal is designed for dynamic or adaptive adaptation of the first direction to the direction of such a dominant sound source.
  • the SNR is rather low, it can nevertheless be advantageous not to allow too high a proportion of such a signal to enter the second directional signal, since this could otherwise worsen the SNR of the second directional signal in an undesirable manner. If, on the other hand, there is a significantly stationary signal with a high SNR and a comparatively high level in the rear half-space, it can be assumed that the noise is localized. The proportion of the Omnidirectional signal at the second directional signal in favor of a better suppression of the background noise, as it occurs in the first directional signal, reduced.
  • the second directional signal can also be generated entirely without the additional addition of signal components of the first directional signal in order to prevent a strongly directional sound source in the rear half-space from being extinguished.
  • the second directional signal can also emerge completely from the first directional signal, that is to say without an additional addition of signal components of the omnidirectional signal, if it is decided to suppress a directional sound signal from the rear half-space as far as possible.
  • the second directional signal can in particular be represented by a mixture of the omnidirectional signal with the first directional signal (even if the specific signal generation may possibly take place in a different but equivalent manner), the mixture also including the borderline cases that the signal components of one of the two generating signals are completely hidden.
  • the second directional signal is advantageously generated by a linear combination of the forward signal and the backward signal with a second directional parameter as a linear factor, the second directional parameter being determined by a predetermined functional relationship from the first directional parameter and the correction parameter in such a way that the second directional signal in the first direction has the defined relative attenuation.
  • Z1 is given by a cardioid and Z2 by an anti-cardioid.
  • the second straightening parameter is expediently derived from the first straightening parameter by scaling by the correction parameter and by a predetermined offset.
  • the offset d to e ⁇ 1 is preferably selected for the case that the forward and backward signals are given by a cardioid or anti-cardioid signal.
  • the second directional signal is generated as a convexity parameter by convex superimposition of the first directional signal and the omnidirectional signal with the correction parameter.
  • This is preferably determined as a function of a background noise level and / or an SNR and / or a stationarity of the sound signal of the environment.
  • the first straightening parameter a1 is scaled by the factor e ⁇ 1 and shifted by an offset of e ⁇ 1.
  • the forward signal Z1 is preferably given by a cardioid signal, and the backward signal Z2 by an anti-cardioid signal.
  • a second direction is generated by pivoting the first direction by an angle tabulated as a function of the correction parameter, the second directional signal being generated by a linear combination of the forward signal and the backward signal with a second directional parameter as a linear factor, and wherein the second directional parameter is determined in such a way that the second directional signal has a maximum attenuation in the second direction.
  • the first direction is determined in which the first directional signal, from the forward and the Backward signal preferably formed by means of adaptive directional microphone, has a maximum attenuation.
  • the correction parameter is then determined, for example as a function of a background noise level, an SNR or a stationarity of the sound signal in the environment.
  • the first direction is then shifted depending on the correction parameter and possibly the first direction itself by a tabulated angle in such a way that the second directional signal, which is generated analogously to the first directional signal, in the second directional signal resulting from the shifting of the first direction by the said angle Direction has the maximum attenuation, and in the first direction the defined relative attenuation.
  • the second directional signal is generated by means of a preferably tabulated second directional parameter which, with the linear combination of the forward and backward signals, results in precisely the required attenuation properties for the second directional signal.
  • the first directional parameter is advantageously generated by means of adaptive directional microphones of the linear combination of the forward signal and the reverse signal, in particular by minimizing the signal energy. In this way it can be ensured in a particularly simple manner that the first direction lies in the direction of a dominant sound source.
  • a first directional signal generated in this way is used in many methods for directional noise suppression in hearing aids, so that the method described here is particularly suitable for preventing excessive or even complete extinction of non-stationary sound sources, especially in the rear hemisphere of the wearer of the hearing aid.
  • the correction parameter is advantageously determined as a function of at least one of the following variables characterizing the sound signal: a background noise level and / or an SNR and / or a stationarity parameter and / or direction information.
  • the correction parameter is preferably determined in such a way that, for a comparatively high background noise level or a comparatively low SNR, the second directional signal is from a comparatively low one Correction of the first directional signal results, and for a comparatively low background noise level or a comparatively high SNR, the second directional signal has a comparatively low directivity.
  • the criteria mentioned can also be applied in stages, so that, for example, for a high SNR even with a high background noise level, the second directional signal still has a considerable difference from the first directional signal.
  • the noise floor level, the SNR and the stationarity parameter can in particular be determined using at least one of the two input signals or using the forward signal and / or the backward signal.
  • the correction parameter is advantageously formed by a monotonic function of the background noise level characterizing the sound signal, the monotonic function above an upper limit value mapping the background noise level to a first end point of the value range of the correction parameter for which the second directional signal changes into the first directional signal.
  • Th Lo ⁇ NP ⁇ Th Hi e (NP - Th Lo ) / (Th Hi - Th Lo ).
  • the monotonic function of the background noise level characterizing the sound signal is preferably corrected as a function of the SNR and / or as a function of the stationarity parameter in conjunction with the directional information.
  • a function defined according to equation (vii) possibly with a different functional, monotonic dependency for the range NP ⁇ Th Hi than the linear one specified there - at a sufficiently high SNR, e.g. for SNR ⁇ Th SNR with a correspondingly defined limit value Th SNR for the SNR, in its range of values for e is reduced, for example (viii) for SNR ⁇ Th SNR : e ⁇ e Max with e max e.g.
  • a stationarity parameter is used in particular in the context of a suppression of stationary interfering noises and can thus be taken from such a parameter and can alternatively also be determined via an autocorrelation function.
  • Such a parameter usually has a value range between zero (completely non-stationary) and one (completely stationary). If such a stationarity parameter S1 is below a corresponding limit value, i.e.
  • a correction of the monotonous function that changes the background noise level to the Correction parameters maps in a middle range for the latter, that is, for example for 0.4 e 0.6, preferably also for 0.25 e 0.27, the slope of the monotonic function can be chosen to be flatter.
  • such a correction can be combined with a correction according to equation (viii), as continuously as possible in e.
  • the second end point of the value range of the correction parameter is in a defined vicinity of a second end point
  • Directional signal is superimposed with a third directional signal, which is designed to simulate a natural directional effect of a human ear, and the superimposition merges into the third directional signal when the correction parameter takes the second end point of its value range.
  • M 0.1 (another value, e.g. 0.05, is possible)
  • the second directional signal is thus increasingly superimposed with the third directional signal, and preferably completely changes into the third directional signal at the second end point for the correction parameter.
  • the wearer of the hearing aid has the natural spatial hearing impression that a pinna produces in a person with normal hearing. This can be done in particular because in this area it is assumed for the correction parameter that the noise floor level is sufficiently low and / or the SNR is sufficiently high.
  • the forward signal is preferably generated on the basis of a time-delayed superposition of the first input signal with the second input signal implemented by means of a first delay parameter, and / or the backward signal is generated on the basis of a time-delayed superposition of the second input signal with the first input signal implemented by means of a second delay parameter.
  • the first and second delay parameters can be selected to be identical to one another, and in particular the forward signal with respect to a preferred plane of the hearing aid can be generated symmetrically to the backward signal, the preferred plane being preferably assigned to the frontal plane of the wearer when the hearing aid is worn. Aligning the first directional signal to the frontal direction of the wearer facilitates signal processing, since this takes into account the wearer's natural line of sight.
  • the forward signal is generated as a forward cardioid directional signal and the backward signal is generated as a backward cardioid directional signal (anti-cardioid).
  • a cardioid directional signal can be generated by superimposing the two input signals on one another with the acoustic transit time delay corresponding to the distance between the input transducers. As a result - depending on the sign of this transit time delay at the superposition - the direction of the maximum attenuation lies in the frontal direction (backward cardioid directional signal) or in the opposite direction (forward cardioid directional signal).
  • the direction of maximum sensitivity is opposite to the direction of maximum attenuation. This facilitates further signal processing, since such an intermediate signal is particularly suitable for adaptive directional microphones due to the maximum attenuation in or against the frontal direction.
  • the omnidirectional signal can be represented or reproduced through a difference between the forward cardioid directional signal and the backward cardioid directional signal, so that the method can run on the level of the cardoid and anti-cardioid signals, and the first directional signal only for the determination of the corresponding adaptive directional parameter is generated.
  • the first directional signal is expediently generated by means of adaptive directional microphones. In this way it can be achieved in a particularly simple manner that the first direction, in which the first directional signal has the maximum attenuation, coincides with a direction of a dominant sound source located in the rear half-space.
  • a first directional parameter is determined which characterizes a superposition of the first intermediate signal with the second intermediate signal for generating the first directional signal, the second directional signal being generated by superimposing the first intermediate signal with the second intermediate signal, Which is characterized by a second directional parameter, and wherein the second directional parameter is determined on the basis of the first directional parameter in such a way that the second directional signal has a relative attenuation defined with respect to the maximum sensitivity in the first direction.
  • the invention also calls a hearing system with a hearing aid, which has a first input transducer for generating a first input signal from a sound signal of the environment and a second input transducer for generating a second input signal from the sound signal of the environment, and a control unit which is configured to do the Carry out method according to one of the preceding claims.
  • the control unit can be integrated in the hearing aid.
  • the hearing system is given directly by the hearing aid.
  • the hearing system shares the advantages of the method according to the invention. The advantages mentioned for the method and for its further developments can be applied analogously to the hearing system.
  • a method for directional signal processing in a hearing aid 1 is shown schematically in a block diagram.
  • the hearing aid 1 has a first input transducer 2 and a second input transducer 4, which generate a first input signal E1 and a second input signal E2 from a sound signal 6 from the surroundings, and can each be given, for example, by a microphone.
  • the first input transducer 2 is arranged further forward than the second input transducer 4 with respect to a frontal direction 7 of the hearing aid 1 (which is defined by the intended wearing during operation).
  • the second input signal E2 is now delayed by a first delay parameter T1, and the second input signal delayed in this way is subtracted from the first input signal E1 in order to generate a forward signal Z1.
  • the first input signal E1 is delayed by a second delay parameter T2, and the second input signal E2 is subtracted from the first input signal thus delayed in order to generate a reverse signal Z2.
  • the first delay parameter T1 and the second delay parameter T2 are given by the transit time T, which corresponds exactly to the spatial sound path d between the first input transducer 2 and the second input transducer 4, except for possible quantification errors during digitization.
  • the forward signal Z1 is thus given by a forward cardioid signal 16, and the backward signal Z2 is given by a backward cardioid signal 18 (that is, an anti-cardioid).
  • a first directional signal R1 is now obtained from the forward signal Z1 and the backward signal Z2 by minimizing the signal energy of the signal Z1 + a1 ⁇ Z2 via a first directional parameter a1.
  • the first directional signal R1 has a directional characteristic 22 with a maximum attenuation in a first direction 24.
  • the first direction 24 falls in the direction of a dominant, localized sound source 25 in the rear half-space 26. In the in FIG Fig. 1 In the example shown, the first direction is rotated by approx.
  • a maximum attenuation here means that the sound coming from the first direction 24 is ideally completely extinguished (ie “infinitely” attenuated).
  • the first directional signal 1 has a so-called “notch” in the first direction 24.
  • An output signal out is now generated from the signal contributions of the first directional signal R1, possibly also by further, non-directional signal processing 29, which is converted into an output sound signal 34 by an output transducer 32 of the hearing aid 1.
  • the output transducer 32 can be provided by a loudspeaker or also by a bone conduction receiver.
  • the dominant sound source 25 in the rear half-space 26 is given by a speaker, for example, the maximum attenuation of his speech contributions that occurs in the present case may often not be desirable for the wearer of the hearing aid 1. In this case it would be advantageous to use an output signal out with a directional characteristic which does not have a maximum attenuation in the first direction 24.
  • a hearing aid 1 is shown in a block diagram, which follows the hearing aid up to the generation of the first directional signal R1 Fig. 1 equal is.
  • the example according to FIG Fig. 2 an omnidirectional signal om is formed, which is superimposed on the first directional signal R1 in accordance with a rule to be described.
  • This superimposition takes place in accordance with a correction parameter e, which can be determined as a function of the background noise level NP and the SNR of the sound signal 6, but can also be determined for the sound signal 6 using a stationarity parameter S1 and directional information IR.
  • the said variables can be determined either from the input signals E1 and E2 or from the forward and backward signals Z1, Z2.
  • non-directional signal processing 29 which can include, among other things, a frequency band-dependent amplification and / or compression, analogous to FIG Fig. 1
  • the illustrated procedure generates the output signal out, which is converted by the output transducer 32 into the output sound signal 34.
  • the directional characteristic 38 of the second directional signal R2 now exhibits its maximum attenuation in a second direction 40, while a relative attenuation 42 is present in the first direction 24.
  • a function f is shown, which the background noise level NP to the correction parameter e des based on Fig. 2 illustrated procedure (solid line).
  • Th Lo the upper limit value
  • the illustrated method is always completely converted into the second directional signal R2.
  • Another characteristic than the linear relationship shown here is also conceivable, as long as the monotonic increase for f (NP) between Th Lo and Th Hi is maintained.
  • FIG. 2 One based on Fig. 2 The procedure is analogous to the procedure described in Fig. 4 shown.
  • This shows in a block diagram a hearing aid 1, which is similar to that shown in FIG Fig. 2 shown hearing aid 1 is modeled.
  • the second directional signal R2 is not formed as a superposition of the first directional signal R1 with the omnidirectional signal om according to the correction parameter e as a convexity parameter.
  • Equation vi mapped onto a second directional parameter a2, which by scaling the first directional parameter a1 by the factor e (the convexity parameter according to FIG Fig. 2 ) and a shift by the offset e - 1 is formed.
  • the directional characteristic 38 is, since the in Fig. 4 procedure for in Fig. 2
  • the procedure shown is analogous under the same conditions, with the exception of an expansion described below for e 0.1, corresponding to the directional characteristic of the second directional signal R2 after Fig. 2 .
  • the maximum weakening now takes place in a second direction 40, while a defined relative weakening 42 is present in the first direction 24.
  • the third directional signal R3 is generated with a fixed directional characteristic from the forward signal Z1 and the backward signal Z2. Alternative transitions between R2 and R3 that do not have the above linear relationship in e are also conceivable.
  • Fig. 5 is a diagram schematically showing the relationship between the first directional parameter a1, which characterizes the first directional signal R1, and the second directional parameter a2 of the second directional signal R2 Fig. 4 shown.
  • the symbols below are used in the in Fig. 5 shown example formed by the respective first direction 24 to the parameter value of the first directional parameter a1, while the symbols above are given by the second direction to the given parameter value for a1, i.e. by the angle at which the second direction 40, i.e. sets the direction of maximum attenuation after applying the mapping of the first directional parameter R1 to the second directional parameter a2.

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  • Health & Medical Sciences (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Circuit For Audible Band Transducer (AREA)
EP20185489.0A 2019-08-08 2020-07-13 Procédé de traitement directionnel du signal pour un appareil auditif Pending EP3772861A1 (fr)

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CN112351365B (zh) 2023-02-24
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