EP4149121A1 - Procédé de fonctionnement d'un appareil auditif - Google Patents

Procédé de fonctionnement d'un appareil auditif Download PDF

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Publication number
EP4149121A1
EP4149121A1 EP22190784.3A EP22190784A EP4149121A1 EP 4149121 A1 EP4149121 A1 EP 4149121A1 EP 22190784 A EP22190784 A EP 22190784A EP 4149121 A1 EP4149121 A1 EP 4149121A1
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EP
European Patent Office
Prior art keywords
signal
directional
weighting factor
signals
hearing aid
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.)
Pending
Application number
EP22190784.3A
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German (de)
English (en)
Inventor
Homayoun KAMKAR-PARSI
Marko Lugger
Juliane Borsum
Manuel BUSCH
Michael BÜRGER
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
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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 EP4149121A1 publication Critical patent/EP4149121A1/fr
Pending legal-status Critical Current

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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
    • H04R25/405—Arrangements for obtaining a desired directivity characteristic by combining a plurality of transducers
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/40—Arrangements for obtaining a desired directivity characteristic
    • H04R25/407—Circuits for combining signals of a plurality of transducers
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
    • H04R25/552—Binaural

Definitions

  • the invention relates to a method for operating a hearing aid, which has at least two input transducers and at least one output transducer, with directional signals generated from the input signals of the input transducers forming an output signal which is converted into a sound signal by the output transducer.
  • Hearing aid devices are portable hearing aids that are used to care for people who are hard of hearing or hard of hearing.
  • different designs of hearing aid devices such as behind-the-ear hearing aids (BTE) and hearing aids with an external receiver (RIC: receiver in the canal) and in-the-ear hearing aids (ITE), for
  • BTE behind-the-ear hearing aids
  • RIC receiver in the canal
  • ITE in-the-ear hearing aids
  • concha hearing aids or canal hearing aids ITE: In-The-Ear
  • CIC Completely-In-Channel
  • IIC Invisible-In-The-Channel
  • the hearing aids listed by way of example are worn on the outer ear or in the auditory canal of a hearing aid device user.
  • Bone conduction hearing aids, implantable or vibrotactile hearing aids are also available on the market. The damaged hearing is stimulated either mechanically or electrically.
  • such hearing aids have an input converter, an amplifier and an output converter as essential components.
  • the input transducer is typically an acousto-electric transducer such as a microphone and/or an electromagnetic receiver such as an induction coil or (radio frequency, RF) antenna.
  • the output converter is usually an electro-acoustic converter, for example a miniature speaker (earphone), or implemented as an electromechanical transducer such as a bone conduction phone.
  • the amplifier is usually integrated into a signal processing device. The energy is usually supplied by a battery or a chargeable accumulator.
  • a so-called binaural hearing aid device two such hearing aids are worn by a user, with a communication link existing between the hearing aids.
  • data possibly also large amounts of data, are exchanged wirelessly between the hearing device on the right and left ear.
  • the exchanged data and information enable the hearing aids to be adapted particularly effectively to a particular acoustic environment. In particular, this enables a particularly authentic spatial sound for the user and improves speech understanding, even in noisy environments.
  • Handling conversational situations is one of the core problems in the use of hearing aids.
  • this is due to the fact that important information is often conveyed to the user of a hearing aid in a personal conversation.
  • a beamforming or directional microphone algorithm is often used in modern hearing aids, through which a narrow directional characteristic, eg a directional cone that is aimed in the direction of the interlocutor.
  • a narrow directional characteristic eg a directional cone that is aimed in the direction of the interlocutor.
  • Such a directional cone as a filter over the input signals of the hearing aid results in the voice signal of the conversation partner being amplified, while noises originating from another direction are significantly suppressed.
  • hearing aids are known in which a number of directional signals with different directional characteristics are used from the microphone signals to generate an output signal.
  • This is also referred to below as the multi-beam concept.
  • Such a multi-beam concept enables, for example, a so-called surrounding beam or surrounding directional cone (region beam).
  • Such an ambient beam is automatically activated, for example, when the hearing aid wearer is having a conversation with more than one target speaker, or when the hearing aid wearer is having a conversation with a single speaker in an offset position without having to turn their head to the conversation partner.
  • the environment beam algorithm is designed here, for example, in such a way that it specifically covers a spatial area in which the conversation partners are located by controlling and combining several flexible, narrow directional signals or directional characteristics from different directions, which are used in parallel.
  • This ambient beam creates various new polar pattern or directivity pattern tailored to the listening situation in which the active conversation partner is located.
  • the technical problem here is that the interlocutors still have the same original speech volume in the output signal, although the background noise and the external interference noise in the distance can be reduced well. This means there is no amplified hearing. In other words, the speakers are not louder and do not stand out in the conversational situations that the hearing aid wearer is in.
  • the invention is based on the object of specifying a particularly suitable method for operating a hearing aid.
  • a speech signal should be emphasized more in the output signal without losing information from the environment.
  • the invention is also based on the object of specifying a particularly suitable hearing aid.
  • the method according to the invention is intended for operating a hearing device, in particular a hearing aid device, and is suitable and designed for this.
  • the hearing aid has at least two input converters for generating input signals and at least one output converter for generating a sound signal.
  • At least two directional signals with different directional characteristics are formed from the input signals, with the directional signals then being examined for the presence of a useful signal.
  • a first weighting factor is assigned to the directional signal with the largest signal component of the useful signal, and a second weighting factor is assigned to the other directional signals.
  • the directional signals are multiplied by the respective assigned weighting factor, and an output signal is then formed therefrom, which is converted into a sound signal by the output transducer.
  • the weighting factors are preferably linear factors.
  • a multi-beam or ambient beam concept is thus implemented, in which the useful signal or useful signal components in the output signal can automatically be represented more prominently and louder by the weighting factors.
  • a multi-beam or ambient beam extension is thus realized, which can be adapted particularly flexibly to the respective hearing situation, and in which background noise and distant, disruptive signal sources can be reduced.
  • a directional signal is a signal that is particularly sensitive to a reference sound from a reference sound source in a specific angular range and has significantly reduced sensitivity when the reference sound source is arranged outside of the given angular range with respect to the reference sound.
  • the directional signal can have a maximum in its sensitivity with respect to the reference sound at a given central angle, with the sensitivity to the reference signal decreasing with an increasing angular distance from the central angle.
  • This angular dependency is also referred to below as the directional characteristic.
  • directional cones or directional lobes rays, beams
  • ie directional characteristics with a lobe-shaped or cone-shaped geometry are included as directional characteristics.
  • Such directional signals or directional characteristics can be generated from the input signals, for example, by “sum and delay” methods.
  • the examination for the presence of the useful signal is carried out, for example, on the basis of an examination as to whether the useful signal is similar to a useful signal source that is predetermined in terms of type.
  • a useful signal source specified by type includes, in particular, a useful signal source that can be specified and/or recognized based on the spectral properties of signal components of the generated useful signal, i.e., for example, a specific speaker whose speech signal is detected in the hearing aid based on its spectral properties and based on the distribution of formats can be distinguished from the speech signals of other possible speakers.
  • spectral parameters of the useful signal source are specified, with a probability being determined as to whether the directional signals contain signal components which are compatible with the spectral parameters.
  • a predetermined probability limit value is exceeded, it is concluded that the useful signal is present.
  • a voice activity detection unit Voice Activity Detection, VAD
  • speakers or voice signals are recognized in the input signal, and potential target speakers or useful signals are determined.
  • the method according to the invention essentially implements a listening mode in which “augmented or enhanced hearing” (augmented listening) or “improved hearing” or “hearing with improved senses” is made possible. It is possible here to automatically make the useful signal or the useful signal source, for example an active conversation partner, more prominent and louder than usual by means of the first weighting factor in the output signal. The useful signal source is thus perceived as being closer to the hearing aid wearer. This means that the useful signal source is "zoomed in” and is more strongly emphasized in the output signal.
  • the second weighting factors are preferably selected in such a way that ambient noise is well preserved in the background.
  • the weighting factors are therefore essentially an automatic volume control in the direction of the useful signal source, for example in the direction of the active speaker.
  • This automatic, directional volume control (ADVC) makes it easier for the hearing aid wearer to listen to conversations.
  • the directional signal multiplied by the first weighting factor, or its directional characteristic preferably has a comparatively small angle widening.
  • this directional signal has a comparatively narrow beam, that is to say a narrow angular expansion, by means of which the useful signal or the useful signal source is tracked.
  • the method according to the invention is automatically hidden or ended, for example. This means that the reinforcement is preferably only applied when it is necessary. As a result, intelligent amplification is preferably implemented.
  • the output signal is formed from a superposition of the directional signals multiplied by the weighting factors.
  • a linear superposition takes place here. This means that the weighted directional signals are preferably added or summed together.
  • the first weighting factor and/or the second weighting factor is set as a function of a current environmental situation.
  • the conjunction “and/or” is to be understood here and in the following in such a way that the features linked by means of this conjunction can be designed both together and as alternatives to one another.
  • an environmental situation is to be understood here in particular as an acoustic environmental situation or a hearing situation.
  • the environmental situation is identified and characterized, for example, by means of a situation detection and/or at least one level measurement and/or at least one algorithm of the hearing device or the signal processing.
  • the Classified environmental situation according to specific criteria, and each of these classes is assigned a specific setting of the weighting factors.
  • the weighting factors are preferably controlled automatically by a scene analysis, which is based on a combination of speaker localization and tracking, background noise estimation, estimation of the speech intensity, the signal-to-noise ratio, . . .
  • the weighting factors are determined as a function of frequency and time. In particular, this means that the weighting factors in different frequency bands are dimensioned differently, for example.
  • the useful signals are voice signals, characteristic spectral conditions of the voice of the conversation partner can also be taken into account.
  • the second weighting factor is applied here in particular over all frequencies or only to certain frequencies.
  • the weighting factors are set in predetermined (value) ranges.
  • the value ranges can be set either in adjustment software from the hearing aid acoustician (Hearing Care Professional, HCP) or via external additional devices, for example with application software (application, app) on a smartphone. This means that the hearing aid acoustician can, for example, decide for each hearing aid wearer whether the user's preference or need is more in the direction of the inventive extended hearing than in the direction of conventional hearing.
  • the first weighting factor is expediently dimensioned larger than the second weighting factor. This ensures that the useful signal appears amplified or louder in the output signal.
  • the second weighting factor has a value range between zero (0) and one (1). This means that the second weighting factor is greater than or equal to zero ( ⁇ 0) and less than or equal to one ( ⁇ 1).
  • the first weighting factor is greater than or equal to zero and less than or equal to an adjustable parameter.
  • the parameter is greater than or equal to one, for example, but in particular the parameter is greater than the upper limit of the second weighting factor. Changing or optimizing the parameter enables a desired gain factor for the useful signal to be set easily.
  • the parameter is set as a function of a signal level of the useful signal. This means that the degree of amplification is controlled by the original input volume of the useful signal. If the signal level of the useful signal is below a certain threshold value, the first weighting factor is automatically increased. If, for example, a conversation partner speaks quietly during a conversation, the useful signal is automatically amplified even more. If, on the other hand, the speaker is already loud, then, for example, the amplification or the first weighting factor is automatically reduced.
  • the useful signal is a voice signal.
  • the useful signal source is a specific speaker or interlocutor, and the useful signal is a (human) speech signal.
  • the method can be used particularly advantageously in the case of a speaker as the useful signal source, since on the one hand a specific speech signal can be identified on the basis of a large number of spectral parameters characteristic of the voice and of the language, so that a particularly reliable amplification using the first weighting factor is made possible . This significantly improves the intelligibility of the speech signal.
  • the hearing device is used in particular to supply a hearing-impaired user (hearing system user).
  • the hearing aid is designed to pick up sound signals from the environment and output them to a user of the hearing aid.
  • the hearing aid has at least two input converters, in particular acousto-electrical converters, such as microphones, and at least one output converter, in particular an electro-acoustic converter, such as a receiver.
  • the input converters pick up sound signals (noises, tones, speech, etc.) from the environment and convert them into an electrical input signal.
  • An electrical output signal is generated from the electrical input signal by modifying the input signal in signal processing.
  • Signal processing is part of the hearing aid, for example.
  • the input converter and the output converter and possibly also the signal processing are housed in particular in a housing of the hearing aid.
  • the housing is designed to be worn by the user on the head and near the ear, e.g., in the ear, on the ear, or behind the ear.
  • the hearing aid is preferably designed as a BTE hearing aid, ITO hearing aid or RIC hearing aid.
  • the hearing aid in particular the signal processing, also has a controller, ie a control unit.
  • the controller is generally set up—in terms of program and/or circuitry—to carry out the method according to the invention described above.
  • the controller is thus specifically set up to determine a number of directional signals from the input signals and to analyze signal components of a useful signal in the directional signals, as well as to assign weighting factors to the directional signals depending on the signal components and to multiply them by them, and from this an output signal for the output converter to create.
  • the controller is formed, at least in its core, by a microcontroller with a processor and a data memory, in which the functionality for carrying out the method according to the invention is implemented programmatically in the form of operating software (firmware). is, so that the method - if necessary in interaction with a device user - is carried out automatically when the operating software is executed in the microcontroller.
  • the controller can also be formed by a non-programmable electronic component, such as an application-specific integrated circuit (ASIC), in which the functionality for carrying out the method according to the invention is implemented with circuitry means.
  • ASIC application-specific integrated circuit
  • the hearing device is designed binaurally and for this purpose has two individual devices, which each have at least two input transducers and at least one output transducer and are thus designed to pick up sound signals from the environment and output them to a user of the hearing device.
  • a wireless interface is provided for data exchange between the two individual devices.
  • the directional characteristics of the directional signals are, in particular, binaural directional characteristics, which means that the directional signals are determined using the input signals of both individual devices.
  • a binaural hearing device With a binaural hearing device, the two individual devices are worn by the user on different sides of the head, so that each individual device is assigned to one ear.
  • a monaural hearing device with only one individual device is also suitable. The explanations regarding a monaural hearing device can be transferred to a binaural hearing device and vice versa.
  • the 1 shows the basic structure of a hearing device 2 according to the invention.
  • the hearing device 2 is designed as a binaural hearing aid device with two hearing aid devices or individual devices 4a, 4b that are coupled in terms of signaling.
  • the individual devices 4a, 4b are in this case configured as behind-the-ear hearing aid devices (BTE).
  • BTE behind-the-ear hearing aid devices
  • the individual devices 4a, 4b are coupled or can be coupled to one another in terms of signals by means of a wireless communication link 6.
  • the communication connection 6 is, for example, an inductive coupling between the individual devices 4a and 4b; alternatively, the communication connection 6 is designed, for example, as a radio connection, in particular as a Bluetooth or RFID connection, between the individual devices 4a and 4b.
  • the structure of the individual devices 4a, 4b is explained below using the example of the individual device 4a.
  • the individual devices 4a includes, as in the 1 shown schematically, a device housing 8, in which one or more microphones, also referred to as (acousto-electrical) input transducer 10 are installed. A sound or the acoustic signals in the surroundings of the hearing aid 2 are recorded with the input converters 10 and converted into electrical acoustic data as input signals 12 .
  • the input signals 12 are processed by a controller 14 of a signal processing device 16 which is also arranged in the device housing 10 .
  • the signal processing device 16 On the basis of the input signals 12, the signal processing device 16 generates an output signal 18 which is routed to a loudspeaker or earpiece 20.
  • the earphone 20 is designed as an (electro-acoustic) output converter 20, which converts and outputs the electrical output signal 18 into an acoustic signal or sound signal.
  • the acoustic signal is optionally transmitted via a not-shown Sound tube or external receiver, with an earmold seated in the ear canal, transmitted to the eardrum of a hearing system user.
  • an electromechanical output converter 20 for example, is also conceivable as a receiver, such as in the case of a bone conduction receiver.
  • the individual device 4a and in particular the signal processing device 16 are supplied with energy by means of a battery 22 accommodated in the device housing 8.
  • the signal processing device 16 is routed in terms of signals to a first transceiver 24 and to a second transceiver 26 of the individual device 4a.
  • the transceiver 24 serves in particular for sending and receiving wireless signals via the communication link 6 and the transceiver 26 for sending and receiving wireless signals via a communication link to an additional device external to the hearing aid, for example a smartphone.
  • an additional device external to the hearing aid for example a smartphone.
  • a method for operating the hearing device 2 during a hearing situation is shown in a block diagram in which a conversation partner 28 is positioned at an angle of approximately 45° with respect to a frontal direction 30 of the hearing device user (hearing device wearer).
  • the hearing situation is such that the conversation between the hearing device user and the conversation partner 28 is superimposed by background noises which originate from noise sources distributed in the area.
  • the conversation partner 28 is a useful signal source, with the speech or the speech signal of the conversation partner 28 representing a useful signal.
  • the method for an individual device 4a, 4b, which is carried out in the controller 14, is described below. However, the method is preferably carried out binaurally, so that the output signal 18 is generated using the input signals 12 of the input converters 10 of both individual devices 4a, 4b.
  • the sound signal 32 which results from the useful signal and the background noise (interference, noise signals), is detected by the input converters 10, which each generate a corresponding input signal 12.
  • a number of directional signals 34 with different directional characteristics 36 are now formed from the input signals 12 by spatial filtering.
  • Examples are in the 2 Schematically four directional signals 34a, 34b, 34c, 34d for four different directional characteristics 36a, 36b, 36c, 36d shown.
  • the directional characteristics 36a, 36b, 36c, 36d are each designed, for example, as lobed or conical directional beams, which each have the same angular widening 38 and differ only with regard to a central angle 40 with respect to the frontal direction 30.
  • the central angle 40 is defined in each case by the angle between the direction of maximum sensitivity of the directional characteristic 36a, 36b, 36c, 36d and the frontal direction 30 of the hearing device user.
  • a selection unit 42 uses the directional signals 34a, 34b, 34c, 34d of the directional characteristics 36a, 36b, 36c, 36d to determine the presence of the useful signal source or the conversation partner 28 in the respective direction of the central angle 40 via the corresponding signal levels.
  • the directional signal 34c has the largest signal component of the useful signal.
  • the directional signal 34c is assigned a first weighting factor bw1 and the other directional signals 34a, 34b, 34d are each assigned a second weighting factor bw2, and the directional signals 34a, 34b, 34c, 34d are multiplied by the respective weighting factor bw1, bw2.
  • the weighting factors bw1 and bw2 can be applied to all frequencies or are multiplied by the directional signals 34a, 34b, 34c, 34d at specific frequencies (that is to say, for example, relevant to speech understanding).
  • the weighting factors bw1, bw2 can thus be dimensioned differently in different frequency bands.
  • the directional signals 34a, 34b, 34c, 34d multiplied by the weighting factors bw1, bw2 are then mixed with one another in a mixing unit 46 by linear superposition.
  • the resulting superposition signal forms, for example, the output signal 18 for the output converter 20, which converts the output signal 18 into an audible sound signal.
  • the superposition signal of the mixing unit 46 is preferably fed to a signal processing block of the signal processing unit 16 (not shown in detail), in which all further processing algorithms specific to the hearing device 2 are executed.
  • the signal processing block then generates the output signal 18.
  • An amplification of the signal processing block can also be present in the relevant frequencies in order to make the speaker even clearer in the output signal 18.
  • the method described above is implemented in particular as a multi-beam or ambient beam concept, in which the useful signal or useful signal components in the output signal 18 are automatically represented more prominently and louder by the weighting factors bw1, bw2.
  • the method essentially implements a listening mode in which “extended or amplified hearing” (augmented listening) is made possible.
  • the useful signal source or the conversation partner 28 is thus perceived by the hearing aid user as (spatially) closer. This means that the useful signal source is “zoomed in” and is more strongly emphasized in the output signal 18 .
  • the weighting factor bw1 is larger than the weighting factor bw2.
  • the weighting factors bw2 are, in particular, greater than or equal to zero and less than or equal to one (0 ⁇ bw2 ⁇ 1). In this case, the weighting factors bw2 are preferably selected in such a way that ambient noise is well preserved in the background.
  • the weighting factor bw1 is greater than or equal to zero and less than or equal to an adjustable parameter (0 ⁇ bw1 ⁇ parameter).
  • the value ranges of the weighting factors bw1, bw2 and in particular the parameters can be set here, for example depending on the preference of the hearing aid wearer, either in adjustment software from the hearing aid acoustician or via external additional devices, for example with application software (application, app) on a smartphone.
  • the weighting factors bw1, bw2 or their values and/or the parameters can be set depending on a current environmental situation or hearing situation.
  • the environmental situation is identified and characterized, for example, by means of a situation recognition 48 .
  • the weighting factors bw1, bw2 are preferably controlled automatically by a scene analysis, which is based on a combination of speaker localization and tracking, background noise estimation, estimation of the speech intensity, the signal-to-noise ratio, et cetera.

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  • Engineering & Computer Science (AREA)
  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Circuit For Audible Band Transducer (AREA)
EP22190784.3A 2021-09-13 2022-08-17 Procédé de fonctionnement d'un appareil auditif Pending EP4149121A1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102021210098.8A DE102021210098A1 (de) 2021-09-13 2021-09-13 Verfahren zum Betrieb eines Hörgeräts

Publications (1)

Publication Number Publication Date
EP4149121A1 true EP4149121A1 (fr) 2023-03-15

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EP22190784.3A Pending EP4149121A1 (fr) 2021-09-13 2022-08-17 Procédé de fonctionnement d'un appareil auditif

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US (1) US20230080855A1 (fr)
EP (1) EP4149121A1 (fr)
CN (1) CN115811691A (fr)
DE (1) DE102021210098A1 (fr)

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP2811762A1 (fr) * 2013-05-16 2014-12-10 Siemens Medical Instruments Pte. Ltd. Système binaural de formation de faisceau fondé sur la logique
EP3328097A1 (fr) * 2016-11-24 2018-05-30 Oticon A/s Dispositif auditif comprenant un détecteur de parole autonome
EP3337189A1 (fr) 2016-12-15 2018-06-20 Sivantos Pte. Ltd. Procédé de détermination de direction d'une source de signal
EP3337187A1 (fr) 2016-12-15 2018-06-20 Sivantos Pte. Ltd. Procédé de fonctionnement d'un dispositif de correction auditive
DE102019205709B3 (de) * 2019-04-18 2020-07-09 Sivantos Pte. Ltd. Verfahren zur direktionalen Signalverarbeitung für ein Hörgerät

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP2811762A1 (fr) * 2013-05-16 2014-12-10 Siemens Medical Instruments Pte. Ltd. Système binaural de formation de faisceau fondé sur la logique
EP3328097A1 (fr) * 2016-11-24 2018-05-30 Oticon A/s Dispositif auditif comprenant un détecteur de parole autonome
EP3337189A1 (fr) 2016-12-15 2018-06-20 Sivantos Pte. Ltd. Procédé de détermination de direction d'une source de signal
EP3337187A1 (fr) 2016-12-15 2018-06-20 Sivantos Pte. Ltd. Procédé de fonctionnement d'un dispositif de correction auditive
US10547956B2 (en) * 2016-12-15 2020-01-28 Sivantos Pte. Ltd. Method of operating a hearing aid, and hearing aid
DE102019205709B3 (de) * 2019-04-18 2020-07-09 Sivantos Pte. Ltd. Verfahren zur direktionalen Signalverarbeitung für ein Hörgerät

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US20230080855A1 (en) 2023-03-16
CN115811691A (zh) 2023-03-17

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