EP3945733B1 - Verfahren zur direktionalen signalverarbeitung für ein hörgerät - Google Patents

Verfahren zur direktionalen signalverarbeitung für ein hörgerät Download PDF

Info

Publication number
EP3945733B1
EP3945733B1 EP21183901.4A EP21183901A EP3945733B1 EP 3945733 B1 EP3945733 B1 EP 3945733B1 EP 21183901 A EP21183901 A EP 21183901A EP 3945733 B1 EP3945733 B1 EP 3945733B1
Authority
EP
European Patent Office
Prior art keywords
signal
directional
parameter
superposition
gain parameter
Prior art date
Legal status (The legal status 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 status listed.)
Active
Application number
EP21183901.4A
Other languages
German (de)
English (en)
French (fr)
Other versions
EP3945733C0 (de
EP3945733A1 (de
Inventor
Tobias Daniel Rosenkranz
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Sivantos Pte Ltd
Original Assignee
Sivantos Pte Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Sivantos Pte Ltd filed Critical Sivantos Pte Ltd
Publication of EP3945733A1 publication Critical patent/EP3945733A1/de
Application granted granted Critical
Publication of EP3945733B1 publication Critical patent/EP3945733B1/de
Publication of EP3945733C0 publication Critical patent/EP3945733C0/de
Active legal-status Critical Current
Anticipated expiration legal-status Critical

Links

Images

Classifications

    • 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
    • H04R1/323—Arrangements for obtaining desired frequency or directional characteristics for obtaining desired directional characteristic only for loudspeakers
    • 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
    • H04R25/35—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using translation techniques
    • H04R25/356—Amplitude, e.g. amplitude shift or compression
    • 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
    • H04R25/50—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
    • H04R3/00—Circuits for transducers, loudspeakers or microphones
    • 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 device, with a first input converter of the hearing device generating a first input signal from a sound signal from the environment, with a second input converter of the hearing device generating a second input signal from the sound signal of the environment, with of the first input signal and the second input signal, a first directional signal and a second directional signal are formed, the second directional signal exhibiting a relative attenuation in the direction of a first useful signal source, the first directional signal exhibiting a relative attenuation in the direction of a second useful signal source, and a first Gain parameters for gaining a first useful signal from the first useful signal source and a second gain parameter for gaining a second useful signal from the second useful signal source are determined.
  • ambient sound is converted by means of at least one input converter into an input signal which, depending on the wearer's hearing impairment to be corrected, is processed in a frequency band-specific manner and in particular individually tailored to the wearer and is also amplified.
  • the processed signal is converted via an output transducer of the hearing aid into an output sound signal which is routed to the wearer's hearing.
  • an automatic volume control (“automatic gain control", AGC) and often also a dynamic compression are applied to the input signal or to an already pre-processed intermediate signal, in which the input signal is usually only linearly amplified up to a certain limit value becomes, and above the limit a lower gain is applied, thereby smoothing out peak levels in the input signal. This is intended in particular to prevent sudden, loud sound events from leading to an output sound signal that is too loud for the wearer due to the additional amplification in the hearing device.
  • an AGC with integrated dynamic compression initially reacts to sound events regardless of their direction. If the wearer of a hearing aid is in a complex hearing situation, e.g. in a conversation with several conversation partners, one conversation partner can trigger the compression, e.g. with a brief outcry or loud laughter, whereby the conversation contributions of another conversation participant are noticeably reduced, which means that the intelligibility suffers for the wearer can.
  • the pamphlet DE 10 2019 205709 B3 discloses a hearing aid having two microphones whose forward and reverse cardioid directivities are combined using a weighted linear combination to direct a maximum of one direction of reception to a first desired sound source and a corresponding minimum to a second unwanted sound source.
  • the invention is based on the object of specifying a method for directional signal processing in a hearing device which, in particular in connection with AGC and/or dynamic compression, is also suitable for complex hearing situations with more than one useful signal source.
  • a method for directional signal processing for a hearing device a first input signal being generated from a sound signal of the environment by a first input converter of the hearing device, a second input signal being generated from the sound signal of the environment by a second input converter of the hearing device a first directional signal and a second directional signal are formed on the basis of the first input signal and the second input signal, the second directional signal having a relative attenuation in the direction of a first useful signal source, the first directional signal having a relative attenuation in the direction of a second useful signal source, and wherein a first amplification parameter for an amplification of a first useful signal from the first useful signal source and a second amplification parameter for an amplification of a second useful signal from the second useful signal source are determined.
  • a reference directional characteristic for a reference directional signal which can be represented in particular as a superimposition of the first directional signal and the second directional signal, is defined, with the first gain parameter and/or the second gain parameter depending on the reference Directional characteristics, a corrected first gain parameter and a corrected second gain parameter are determined in such a way that an output directional signal, which is the sum of the first directional signal weighted with the corrected first gain parameter and the second directional signal weighted with the corrected second gain parameter, is formed into a linearly scaled reference -directional signal transitions when the first gain parameter is equal to the second gain parameter and at least one of said two corrected gain parameters is different from the corresponding underlying gain parameter.
  • Advantageous and partly inventive configurations are the subject matter of the subclaims and the following description.
  • the directional output signal with the required property can be formed either as the correspondingly described superimposition, or using at least one suitable intermediate signal, the directional output signal being formed in such a way that the required property is met when the two amplification parameters are equal.
  • the first directional signal can be formed for further signal processing, so that in particular the signal components of the first directional signal are included in the output directional signal.
  • the output directional signal is formed from the signal components of at least one suitable intermediate signal - e.g. a formation of the first and second directional signal as well as the output directional signal based on forward and backward cardioid signals - the first directional signal is used in particular formed to determine the corrected first and / or corrected second gain parameter, since the directional information in particular about the second useful signal source, which can be removed from the first directional signal, is of decisive advantage for this.
  • An output signal is preferably generated on the basis of the output directional signal, which output signal is converted into an output sound signal by an output converter of the hearing device.
  • interference noise and/or feedback and/or further signal processing steps can also be suppressed, in particular as a function of the frequency band, when the output signal is generated from the output directional signal.
  • the method can be carried out by frequency band, so that the first and the second gain parameter, the first and the second directional signal and the reference directional signal and finally the corrected first and second gain parameter and the output directional signal are determined separately for each frequency band or for groups of individual frequency bands or be defined.
  • an input transducer includes in particular an electroacoustic transducer which is set up to generate a corresponding electrical signal from a sound signal.
  • pre-processing can also take place, e.g. in the form of linear pre-amplification and/or A/D conversion.
  • the correspondingly generated input signal is given in particular by an electrical signal whose current and/or voltage fluctuations essentially represent the sound pressure fluctuations of the air.
  • the direction of the first useful signal source is preferably directed into the front hemisphere with respect to a frontal direction of a user of the hearing device defined by the intended use of the hearing device.
  • the first useful signal source is particularly preferably located at least approximately in the frontal direction, so that in particular corresponding approximations of a frontal source can be made for the signal processing.
  • the direction of the second useful signal source is preferably directed outside an angular range of +/-45°, particularly preferably +/-60°, around the frontal direction.
  • the direction of the second useful signal source is directed towards the rear hemisphere.
  • a relative weakening of the first directional signal is to be understood here in particular as meaning that the directional characteristic in question has a sensitivity in the direction of the second useful signal which is reduced compared to the sensitivity averaged over all directions, and in particular has a local, preferably a global minimum.
  • the first and the second directional signal have as complete an attenuation as possible in the direction of the second or the first useful signal source.
  • the present invention solves the following problem in particular: If an output directional signal is formed using two directional signals, each of which has a relative, preferably complete, attenuation in the direction of another useful signal source, the amplification of the second useful signal, for example, does not depend on the resulting output directional signal depends only on the corresponding amplification parameter with which the second directional signal is weighted, but also on the direction of the second useful signal source, since the second directional signal has a non-trivial directional dependency in this regard. If the first directional signal then has a complete or almost complete weakening in the direction of the second useful signal source, said directional dependency cannot be compensated for by a correction term of the first directional signal. The same can apply to an amplification of the first useful signal by the first directional signal.
  • a corresponding correction must therefore be made via the contributions of the respective directional signal itself.
  • this is solved by correcting the "scaling" of the respective directional signal, ie adjusting the respective gain parameter, so that the corrected gain parameter allows this directional dependency of the corresponding directional signal to be taken into account.
  • the reference directional characteristic is specified as the "normal state" which should be achieved if both useful signals are to be amplified with the same amplification parameters (the assumption here is that this applies in particular to identical useful signals, which only arrive from different directions).
  • the amplification of the individual, "equally loud" useful signals should lead to the reference state, ie, for example, to an omnidirectional directional characteristic or a directional characteristic that models filtering by a pinna.
  • the reference directional signal is preferably represented on the basis of the two directional signals, so that the corrected gain parameters can be determined using the corresponding coefficients in this representation. It is particularly possible here that, for example, only the second corrected gain parameter has a real non-trivial correction to the second gain parameter, while the first corrected gain parameter is identical to the first gain parameter. However, both corrected gain parameters, that is to say the first and the second, can each differ from their underlying first or second gain parameter. This can be the case in particular if neither of the two useful signal sources is occupied in a preferred direction (e.g. the frontal direction) with respect to the hearing aid.
  • a preferred direction e.g. the frontal direction
  • the corrected second amplification parameter is advantageously determined in such a way that the second useful signal is amplified by the second amplification parameter compared to the reference directional characteristic by the output directional signal, and/or the corrected first amplification parameter is determined in such a way that that the first useful signal is amplified by the output directional signal compared to the reference directional characteristic by the first amplification parameter.
  • each of the two useful signals is amplified by the output directional signal, depending on the direction of the respective useful signal source, with the "correct" amplification parameter for the individual useful signal.
  • the second useful signal - e.g. a corresponding second directional signal -
  • the corrected second gain parameter can be identical to the first gain parameter.
  • the corrected second gain parameter is expediently formed as a product of the second gain factor and a correction factor, the correction factor corresponding to a linear coefficient of the second directional signal in a representation of the reference directional signal as a linear combination of the first directional signal and the second directional signal.
  • a value of a can be determined (the two scalar products can be tabulated in particular for different values of w1, w2 and ⁇ ).
  • the value of a can also be used to determine a value for b in one of the two components of (ii ⁇ ).
  • a first intermediate signal and a second intermediate signal are preferably formed on the basis of the first input signal and the second input signal, the first directional signal being formed as a superimposition of the first intermediate signal and the second intermediate signal, and an associated first superimposition parameter being determined and/or the second directional signal is formed as a superimposition of the second intermediate signal with the first intermediate signal, and an associated second superimposition parameter is determined in the process.
  • a forward-pointing and a backward-pointing cardioid signal Xc, Xa are used as the first intermediate signal and the second intermediate signal.
  • a2 0, ie the second directional signal Xr2 is given by the backward-directed cardioid signal Xa, and thus by the second intermediate signal Z2. This is the case, for example, when the first useful signal source, for which the second directional signal has a relative, preferably maximum, and particularly preferably total attenuation, is in the region of the notch of the backward-directed cardioid signal or is accepted there.
  • the corrected first gain parameter G1' is formed as a product of the first gain factor G1 and a first correction factor a
  • the corrected second gain parameter G2' is formed as a product of the second gain factor G2 and a second correction factor b.
  • first and second superimposition parameters a1, a2 using the first and second reference superimposition parameters aref1, aref2 and using the first amplification parameter G1 and based on the second gain parameter G2, an effective first superimposition parameter aeff1 and an effective second superimposition parameter aeff2 are determined, with the output directional signal Xout based on a superimposition of the first intermediate signal Z1 weighted with the first effective superimposition parameter aeff1 and the second intermediate signal weighted with the second effective superimposition parameter aeff2 Intermediate signal Z2 is formed, ie in particular as Xout ⁇ aeff1 Z1 + aeff2 ⁇ Z2.
  • the first and second effective overlay parameters aeff1, aeff2 merge into the first and second reference overlay parameters aref1, aref2, respectively, according to equation (vi).
  • This can now be used to first calculate the two correction parameters a, b, which according to equation (iii) correspond to the two amplification parameters G1, G2 are assigned, and finally the two effective overlay parameters aeff1, aeff2 as a function of the reference overlay parameters aref1, aref2.
  • the second effective superimposition parameter is advantageously formed from the first superimposition parameter a1 and a ratio of the corrected second gain parameter G2 ⁇ and the first gain parameter G2 ⁇ /G1.
  • the reference directional characteristic of the reference directional signal is chosen as an omnidirectional directional characteristic, or is chosen in such a way that a shadowing effect of human ears is simulated.
  • aref1, aref2 can be determined on a generic ear model (e.g. a KEMAR), or can also be individually adjusted to the wearer of the hearing aid by appropriate measurements.
  • the first directional signal preferably has a maximum attenuation in the direction of the first useful signal source and/or the second directional signal has a maximum, in particular total, weakening in the direction of the second useful signal source.
  • the first directional signal is generated using adaptive directional microphones, in particular using a first intermediate signal and a second intermediate signal
  • the second directional signal is generated using adaptive directional microphones, in particular using the first and second intermediate signals.
  • the first intermediate signal is generated using a time-delayed superimposition of the first input signal with the second input signal, implemented using a first delay parameter
  • the second intermediate signal is generated using a time-delayed superimposition of the second input signal with the second input signal, implemented using a second delay parameter first input signal is generated.
  • the first and second delay parameters can be chosen to be identical to one another, and in particular the first intermediate signal can be generated symmetrically to the second intermediate signal with respect to a preferred plane of the hearing aid, with the preferred plane being assigned to the frontal plane of the wearer, preferably when wearing the hearing aid. Alignment of the directional signals to the wearer's frontal direction facilitates signal processing, since this takes into account the wearer's natural viewing direction.
  • the first intermediate signal is preferably generated as a forward-directed cardioid directional signal and/or the second intermediate signal is generated as a backward-directed cardioid directional signal.
  • a directional cardioid signal can be formed by superimposing the two input signals on one another with the acoustic propagation delay corresponding to the distance between the input transducers.
  • the direction of the maximum attenuation is in the frontal direction (backward directional cardioid signal) or in the opposite direction (forward cardioid directional signal).
  • the direction of maximum sensitivity is the direction of maximum opposite weakening. This facilitates further signal processing, since such an intermediate signal is particularly suitable for adaptive directional microphony.
  • the invention also mentions a hearing system with a hearing aid, which has a first input converter for generating a first input signal from a sound signal from the environment and a second input converter for generating a second input signal from the sound signal from the environment, and a control unit which is set up to carry out the procedures described above.
  • the control unit can be integrated in the hearing aid.
  • the hearing system is given directly by the hearing aid.
  • a wearer 1 of a hearing aid 2 is shown schematically in a top view, which is in a conversation situation with a first conversation partner 4 and a second conversation partner 8 .
  • the first interlocutor 4 is positioned in a first direction 6 with respect to the carrier 1, the second interlocutor 8 in a second direction 10 relative to the carrier 1.
  • the first interlocutor 4 is the main interlocutor of the carrier 1, the second interlocutor 8 takes part in this conversation only through isolated voice contributions.
  • the conversation situation described here is for the upper and the lower picture of figure 1 identical.
  • the voice contributions of the first conversation partner 4 form the first useful signal S1, the voice contributions of the second conversation partner 8 the second useful signal S2.
  • a first directional signal Xr1 is generated by means of adaptive directional microphony in such a way that the same has a maximum and preferably complete attenuation in the second direction 10, in which the second interlocutor 8 is positioned.
  • a compression factor which is calculated based on the first directional signal Xr1, consequently only reacts to the first and second call partners 4 and 8 with regard to the two useful signal sources 14, 18.
  • a first amplification parameter G1 is determined, which with regard to the first useful signal S1 of the first useful signal source 14 (ie the first conversation partner 4) for each moment determines the optimal signal amplification and thus implicitly also a corresponding compression ratio.
  • FIG. 1 1 shows, analogously to the top image, a second directional signal Xr2 in the same hearing situation, which has a maximum and preferably complete attenuation in the first direction 6, ie the direction of the first conversation partner 4. Since the first direction 6 coincides with the frontal direction of the carrier 1, the second directional signal Xr2 is as a rearward one Designed cardioid directional signal Xa.
  • the second amplification parameter G2 which is determined based on the second directional signal Xr2 and is assigned to it, therefore represents the optimal amplification with regard to the second useful signal S2 and in particular an associated compression ratio at any moment.
  • an output sound signal could now be formed from a linear combination of the first and the second directional signal Xr1, Xr2, which are each weighted with their respective gain parameters G1, G2.
  • the first directional signal Xr1 is also formed by means of adaptive directional microphony based on a forward-directed cardioid directional signal and based on the backward-directed cardioid directional signal Xa, such a linear combination would lead to an output sound signal whose directional characteristic is similar in shape to that of the first directional signal Xr1, although the notch 22 of maximum attenuation is shifted away from the second direction 10. On the one hand, this leads to a possibly undesirable, completely "deaf" area away from the second useful signal source 18, which on the other hand can also fluctuate in its orientation due to the dependence of such a linear combination on the speech contributions of the first conversation partner 4.
  • FIG 2 1 is a schematic block diagram of a method for directional signal processing for the hearing aid 2 figure 1 in the situation described there, which is intended to mitigate in particular the level peaks of the two useful signals S1, S2 of the useful signal sources 14, 18 given by the respective conversation partners 4, 8.
  • a first input transducer 24 and a second input transducer 26 are arranged in the hearing device 2 and each of these generates a first input signal E1 and a second input signal E2 from a sound signal 28 .
  • the sound signal 28 is the ambient sound, which therefore also contains the first and the second useful signal S1, S2.
  • a possible pre-processing such as an A/D conversion or something similar should already be in be included in the input transducers 24, 26, which also each have a preferably omnidirectional microphone.
  • the first input signal E1 is now superimposed with the second input signal E2, which was delayed by a first delay parameter T1, and a first intermediate signal Z1 is formed from this.
  • the first input signal E1, which was delayed by a second delay parameter T2 is superimposed on the second input signal E2, and a second intermediate signal Z2 is thereby formed.
  • the first amplification parameter G1 is determined for the first useful signal S1 on the basis of the first directional signal Xr1.
  • the determined first gain parameter G1 thus represents the optimal gain and compression of the signal contributions of the first conversation partner 4 through the first directional signal Xr1.
  • the second directional signal Xr2 can be generated from the first intermediate signal Z1 and the second intermediate signal Z2, which maximum suppresses the contributions of the first conversation partner 4, ie the second useful signal S2. Since the carrier 1 is in the frontal direction in the present case, the second directional signal Xr2 is, as already mentioned, given by the backward-directed cardioid directional signal Xa. On the one hand, the second directional signal Xr2 can be permanently assumed as the backward-directed cardioid directional signal Xa. On the other hand, by means of the adaptive directional microphone 42 and a change in position of the first interlocutor 4 for the formation of the second Directional signal Xr2 from the first and the second intermediate signal Z1, Z2 are taken into account.
  • the second gain parameter G2 is also determined using the second directional signal Xr2. This represents the optimal amplification and compression of the second useful signal S2 by the second directional signal Xr2.
  • a reference directional characteristic 63 is defined for a reference directional signal Xref.
  • An omnidirectional directional characteristic for the reference directional signal Xref can also be selected for some or all frequency bands (which loses its directivity as a result).
  • the reference directional signal Xref is used to define the reference directional characteristic 63 and the reference superimposition parameters aref1, aref2, and in the present case does not necessarily have to be generated as an independent signal from the two intermediate signals Z1 and Z2 (correspondingly represented by dashed lines); rather, the reference overlay parameters aref1, aref2 can be predetermined.
  • the output directional signal Xout has a directional characteristic which is amplified or weakened by a factor G1 in the direction of the first useful signal source 14 (i.e.
  • an output signal Yout is finally generated via signal processing steps 50, which can in particular include additional frequency band-dependent noise suppression, which output signal Yout is converted into an output sound signal 54 by an output converter 52 of the hearing aid 2.
  • FIG 3a is for the in 1 illustrated hearing situation of the wearer 1 has a directional characteristic 60 of the as in 2 described generated output directional signal Xout shown.
  • the reference directional characteristic 62 (dashed line) is given here as an onmidirectional directional characteristic.
  • the first gain parameter G1 is selected as 0 dB
  • the second gain parameter G2 is selected as -6 dB.
  • the resulting directional characteristic 60 of the output directional signal Xout has a noticeable deviation from the omnidirectional reference directional characteristic 62 in the second direction 10 (ie the direction of the second useful signal source 18).
  • a reference directional signal Xref with a reference directional characteristic 64 is selected (dashed line), which models the filtering of the ambient sound by the pinna and corresponding shadowing effects.
  • the first gain parameter G1 is here chosen as 0 dB
  • the second gain parameter G2 is chosen as -6 dB.
  • the resulting directional characteristic 66 of the output directional signal Xout again shows a noticeable deviation from the omnidirectional reference directional characteristic 64 in the direction of the second useful signal source 18, with an additional weakening now taking place in this direction due to the definition of the reference directional signal Xref, which as a result of the Shading effects of the pinna go into the reference directional characteristic 64.

Landscapes

  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Health & Medical Sciences (AREA)
  • Otolaryngology (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Circuit For Audible Band Transducer (AREA)
EP21183901.4A 2020-07-29 2021-07-06 Verfahren zur direktionalen signalverarbeitung für ein hörgerät Active EP3945733B1 (de)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102020209555.8A DE102020209555A1 (de) 2020-07-29 2020-07-29 Verfahren zur direktionalen Signalverarbeitung für ein Hörgerät

Publications (3)

Publication Number Publication Date
EP3945733A1 EP3945733A1 (de) 2022-02-02
EP3945733B1 true EP3945733B1 (de) 2023-06-07
EP3945733C0 EP3945733C0 (de) 2023-06-07

Family

ID=76807557

Family Applications (1)

Application Number Title Priority Date Filing Date
EP21183901.4A Active EP3945733B1 (de) 2020-07-29 2021-07-06 Verfahren zur direktionalen signalverarbeitung für ein hörgerät

Country Status (5)

Country Link
US (1) US11558696B2 (zh)
EP (1) EP3945733B1 (zh)
JP (1) JP7193210B2 (zh)
CN (1) CN114071314A (zh)
DE (1) DE102020209555A1 (zh)

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102022206916A1 (de) * 2022-07-06 2024-01-11 Sivantos Pte. Ltd. Verfahren zur direktionalen Signalverarbeitung für ein Hörinstrument

Family Cites Families (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8942387B2 (en) 2002-02-05 2015-01-27 Mh Acoustics Llc Noise-reducing directional microphone array
DK1443798T3 (da) * 2004-02-10 2006-10-09 Phonak Ag Höreapparat med zoomfunktion til öret af et individ
DE102006047983A1 (de) * 2006-10-10 2008-04-24 Siemens Audiologische Technik Gmbh Verarbeitung eines Eingangssignals in einem Hörgerät
WO2009102811A1 (en) 2008-02-11 2009-08-20 Cochlear Americas Cancellation of bone conducted sound in a hearing prosthesis
DE102015211747B4 (de) * 2015-06-24 2017-05-18 Sivantos Pte. Ltd. Verfahren zur Signalverarbeitung in einem binauralen Hörgerät
DE102017206788B3 (de) * 2017-04-21 2018-08-02 Sivantos Pte. Ltd. Verfahren zum Betrieb eines Hörgerätes
DE102017215823B3 (de) 2017-09-07 2018-09-20 Sivantos Pte. Ltd. Verfahren zum Betrieb eines Hörgerätes
DE102017221006A1 (de) * 2017-11-23 2019-05-23 Sivantos Pte. Ltd. Verfahren zum Betrieb eines Hörgerätes
EP3503581B1 (en) * 2017-12-21 2022-03-16 Sonova AG Reducing noise in a sound signal of a hearing device
EP4009667A1 (en) * 2018-06-22 2022-06-08 Oticon A/s A hearing device comprising an acoustic event detector
DE102019205709B3 (de) 2019-04-18 2020-07-09 Sivantos Pte. Ltd. Verfahren zur direktionalen Signalverarbeitung für ein Hörgerät

Also Published As

Publication number Publication date
US11558696B2 (en) 2023-01-17
JP7193210B2 (ja) 2022-12-20
US20220038828A1 (en) 2022-02-03
DE102020209555A1 (de) 2022-02-03
EP3945733C0 (de) 2023-06-07
CN114071314A (zh) 2022-02-18
JP2022027584A (ja) 2022-02-10
EP3945733A1 (de) 2022-02-02

Similar Documents

Publication Publication Date Title
DE102019205709B3 (de) Verfahren zur direktionalen Signalverarbeitung für ein Hörgerät
EP3461147B1 (de) Verfahren zum betrieb eines hörgerätes
EP1771034A2 (de) Mikrofonkalibrierung bei einem RGSC-Beamformer
EP1414268A2 (de) Verfahren zum Einstellen und zum Betrieb eines Hörhilfegerätes sowie Hörhilfegerät
EP1473967B1 (de) Verfahren zur Unterdrückung mindestens eines akustischen Störsignals und Vorrichtung zur Durchführung des Verfahrens
EP2840809B1 (de) Steuerung der effektstärke eines binauralen direktionalen mikrofons
EP2537351B1 (de) Verfahren zur binauralen seitenwahrnehmung für hörinstrumente
EP1307072A2 (de) Verfahren zum Betrieb eines Hörgerätes sowie Hörgerät
EP3393143B1 (de) Verfahren zum betrieb eines hörgerätes
EP3926982A2 (de) Verfahren zur richtungsabhängigen rauschunterdrückung für ein hörsystem, welches eine hörvorrichtung umfasst
EP3945733B1 (de) Verfahren zur direktionalen signalverarbeitung für ein hörgerät
DE60316474T2 (de) Mikrofonsystem mit richtansprechverhalten
EP1269576B1 (de) Verfahren zur vorgabe der übertragungscharakteristik einer mikrophonanordnung und mikrophonanordnung
DE102020210805B3 (de) Verfahren zur direktionalen Signalverarbeitung für ein akustisches System
DE202019107201U1 (de) Binaurales Hörgerät für eine verbesserte räumliche Hörwahrnehmung
DE102019211943B4 (de) Verfahren zur direktionalen Signalverarbeitung für ein Hörgerät
DE602004001058T2 (de) Hörhilfegerät mit einer Zoom-Funktion für das Ohr eines Individuums
EP2437521B2 (de) Verfahren zur Frequenzkompression mit harmonischer Korrektur und entsprechende Vorrichtung
EP1916872B1 (de) Differentielles Richtmikrofonsystem und Hörhilfsgerät mit einem solchen differentiellen Richtmikrofonsystem
DE102022206916A1 (de) Verfahren zur direktionalen Signalverarbeitung für ein Hörinstrument
DE102022202646B3 (de) Verfahren zum Betrieb eines binauralen Hörsystems
EP3534624B1 (de) Verfahren zum betrieb eines hörgerätes
DE19844748A1 (de) Verfahren zum Bereitstellen einer Richtmikrofoncharakteristik und Hörgerät
WO2000041436A1 (de) Verfahren zur erzeugung eines elektrischen signals bzw. verfahren zur hervorhebung von akustischen signalen aus einer vorzugsrichtung, übertrager und vorrichtung
DE102020202206A1 (de) Verfahren zur Unterdrückung eines Eigenrauschens einer Mikrofonanordnung

Legal Events

Date Code Title Description
PUAI Public reference made under article 153(3) epc to a published international application that has entered the european phase

Free format text: ORIGINAL CODE: 0009012

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: THE APPLICATION HAS BEEN PUBLISHED

AK Designated contracting states

Kind code of ref document: A1

Designated state(s): AL AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HR HU IE IS IT LI LT LU LV MC MK MT NL NO PL PT RO RS SE SI SK SM TR

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: REQUEST FOR EXAMINATION WAS MADE

17P Request for examination filed

Effective date: 20220511

RBV Designated contracting states (corrected)

Designated state(s): AL AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HR HU IE IS IT LI LT LU LV MC MK MT NL NO PL PT RO RS SE SI SK SM TR

GRAP Despatch of communication of intention to grant a patent

Free format text: ORIGINAL CODE: EPIDOSNIGR1

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: GRANT OF PATENT IS INTENDED

INTG Intention to grant announced

Effective date: 20220915

GRAS Grant fee paid

Free format text: ORIGINAL CODE: EPIDOSNIGR3

GRAA (expected) grant

Free format text: ORIGINAL CODE: 0009210

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: THE PATENT HAS BEEN GRANTED

AK Designated contracting states

Kind code of ref document: B1

Designated state(s): AL AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HR HU IE IS IT LI LT LU LV MC MK MT NL NO PL PT RO RS SE SI SK SM TR

REG Reference to a national code

Ref country code: GB

Ref legal event code: FG4D

Free format text: NOT ENGLISH

REG Reference to a national code

Ref country code: CH

Ref legal event code: EP

Ref country code: AT

Ref legal event code: REF

Ref document number: 1578279

Country of ref document: AT

Kind code of ref document: T

Effective date: 20230615

REG Reference to a national code

Ref country code: DE

Ref legal event code: R096

Ref document number: 502021000787

Country of ref document: DE

U01 Request for unitary effect filed

Effective date: 20230628

U07 Unitary effect registered

Designated state(s): AT BE BG DE DK EE FI FR IT LT LU LV MT NL PT SE SI

Effective date: 20230706

REG Reference to a national code

Ref country code: LT

Ref legal event code: MG9D

U20 Renewal fee paid [unitary effect]

Year of fee payment: 3

Effective date: 20230823

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: NO

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230907

Ref country code: ES

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230607

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: RS

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230607

Ref country code: HR

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230607

Ref country code: GR

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230908

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: SK

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230607

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: IS

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20231007

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: SM

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230607

Ref country code: SK

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230607

Ref country code: RO

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230607

Ref country code: IS

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20231007

Ref country code: CZ

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230607

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: PL

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230607

REG Reference to a national code

Ref country code: DE

Ref legal event code: R097

Ref document number: 502021000787

Country of ref document: DE

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: MC

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230607

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: MC

Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT

Effective date: 20230607

PLBE No opposition filed within time limit

Free format text: ORIGINAL CODE: 0009261

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: NO OPPOSITION FILED WITHIN TIME LIMIT

REG Reference to a national code

Ref country code: IE

Ref legal event code: MM4A

26N No opposition filed

Effective date: 20240308