EP3355592B1 - Verfahren zum betrieb eines binauralen hörgerätesystems - Google Patents

Verfahren zum betrieb eines binauralen hörgerätesystems Download PDF

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Publication number
EP3355592B1
EP3355592B1 EP17207542.6A EP17207542A EP3355592B1 EP 3355592 B1 EP3355592 B1 EP 3355592B1 EP 17207542 A EP17207542 A EP 17207542A EP 3355592 B1 EP3355592 B1 EP 3355592B1
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EP
European Patent Office
Prior art keywords
frequency
hearing aid
signal
division
audio signal
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Application number
EP17207542.6A
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German (de)
English (en)
French (fr)
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EP3355592A1 (de
Inventor
Tobias Daniel Rosenkranz
Tobias Wurzbacher
Christoph LÜKEN
Christos OREINOS
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Sivantos Pte Ltd
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Sivantos Pte Ltd
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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
    • H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
    • H04R25/552—Binaural
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • 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
    • H04R25/453—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback electronically
    • 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
    • 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 operating a binaural hearing aid system with a first hearing aid and a second hearing aid, wherein a first audio signal of the first hearing aid is divided into a first high-frequency component and a first low-frequency component, and a second audio signal of the second hearing aid in a second high-frequency component and a second low-frequency component is divided.
  • a sound signal from the environment is typically converted into an electrical signal by means of an input converter, and is processed in a signal processing unit in accordance with the audiological requirements of the user and, in particular, is amplified as a function of frequency.
  • the processed signal is then converted by an output converter into an output sound signal, which is fed to the hearing of the user.
  • Binaural hearing aid systems with two hearing aids are often used for an improved spatial hearing sensation and an improved spatial resolution of the sound signals, of which the user wears one on the left and one on the right ear.
  • the hearing aids mutually transmit their input signals generated by the respective input transducers and / or further audio signals derived therefrom by signal processing and possibly additional control signals and generate the respective output signals for the local output transducers from the local signals and the received signals.
  • an acoustic feedback loop can be created by coupling the output sound signal into the input transducer, since the output sound signal thus again amplifies the signal processing learns what can lead to significant whistling or general noise.
  • the acoustic feedback is therefore mostly suppressed by means of an internal, electrical feedback loop, in which a compensation signal is generated on the basis of the fully amplified audio signal, for example in an adaptive filter, which is fed to the input signal to compensate for the acoustic feedback.
  • the amplified audio signal is often frequency-distorted before it is fed to the adaptive filter in order to decorrelate it from the input signal, which results in formation counteracts artifacts.
  • the EP 2 988 529 A1 mentions, for example, a method for suppressing acoustic feedback in a hearing aid, a division frequency being adaptively determined as a function of the acoustic feedback, and a frequency change being applied only to the signal components above the division frequency.
  • the frequency of division is chosen to be as high as possible in order to minimize the frequency range in which the signal of the hearing aid which is frequency-modified by the hearing aid is superimposed on the non-frequency-altered direct sound for a user of the hearing aid, but on the other hand, at least the frequency range which is potentially critical for acoustic feedback should be in frequency to be changed.
  • the document EP 1 841 285 A1 discloses a binaural hearing aid system in which information is exchanged between the hearing aids to reduce the amount of redundant data stored in the memory of each of the respective hearing aids.
  • an acoustic feedback loop can form for each of the two hearing aids.
  • additional requirements result from the transmission of the individual signals between the two hearing aids and their mutual use for the generation of the output signals.
  • Frequency distortions in binaural hearing aids are known to the person skilled in the art, for example, in the form of frequency transpositions from the US 2013/0 051 566 A1 known in connection with the improvement of the spatial perception of an environment.
  • the known findings on suppression are of acoustic feedback in binaural hearing aids can only be used to a very limited extent due to the different target directions.
  • the invention is therefore based on the object of specifying a method for operating a binaural hearing aid system which is intended to permit the suppression of acoustic feedback with a spatial sensation of hearing that is as natural as possible.
  • the stated object is achieved according to the invention by a method for operating a binaural hearing aid system according to claim 1 and a binaural hearing aid system according to claim 9.
  • the first audio signal is preferably generated locally in the first hearing device and the second audio signal locally in the second hearing device.
  • the first or the second audio signal can be given by an intermediate signal in the signal processing process of the hearing aid in question.
  • an intermediate signal is usually branched off from the main signal path to suppress acoustic feedback and fed to a specially provided feedback suppression device, for example an adaptive filter, where a compensation signal is generated from the intermediate signal, which is fed back into the main signal path, so that in the main signal path Signal components based on acoustic feedback are extinguished as far as possible.
  • a specially provided feedback suppression device for example an adaptive filter
  • the main signal path includes, in particular, an input signal which is generated by an input transducer of the hearing aid from a sound signal in the environment, the input signal comprises signal components which are fed to the user-specific signal processing of the hearing aid, the user-specific signal processing particularly including frequency-dependent amplification and noise suppression, a correspondingly user-specific one processed signal and an output signal derived therefrom, which is converted by an output transducer of the hearing aid into an output sound signal for the user.
  • the suppression of the feedback can lead to losses in the sound quality, since on the one hand, for particularly tonal and / or stationary useful signals, it is difficult to distinguish between a feedback-related whistle and a useful signal component in a frequency range relevant for feedback, as a result of which signal components of the useful signal are also potentially affected by cancellation the compensation signal may be affected.
  • stationary signal components of background noise can also be audibly modulated, which can impair the hearing perception of a hearing situation even if the useful signal is not impaired.
  • the compensation signal can be generated in such a way that it contains signal components only in the relevant frequency ranges. This can now be done can be achieved that the feedback suppression device, the corresponding intermediate signal branched off from the main signal path is divided at a division frequency into a high-frequency component and a low-frequency component, and only the high-frequency component is used to generate the compensation signal.
  • each local acoustic feedback path - i.e. from the output transducer back to the input transducer of the same hearing aid - is usually considered separately a priori due to the strong attenuation of a crosswise feedback.
  • an acoustic feedback path changes locally, e.g. Due to a changed fit of the hearing aid in question in the ear as a result of jaw movements when the user speaks or the like, the suppression of the feedback should preferably be adapted to the changed circumstances, which is actually a change in the frequency range of the suppression that is optimal with regard to the local hearing sensation Frequency of division includes.
  • a first frequency distortion which is different for the first high-frequency component and the first low-frequency component, is expediently applied to the first audio signal, thereby producing a first frequency-distorted audio signal, and one for the second high-frequency component and the second low-frequency component each for the second audio signal different second frequency distortion applied and generated a second frequency-distorted audio signal.
  • the use of the first frequency distortion thus distorts the first high-frequency component and the first low-frequency component of the first audio signal, the distortion taking place to different degrees for the first high-frequency component and the first low-frequency component.
  • the first frequency distortion and the second frequency distortion can each have an identical effect on the first audio signal and the second audio signal, ie, the same frequency distortion is applied to the first high-frequency component as to the second high-frequency component, and to the first low-frequency component.
  • the same frequency distortion is applied to the second low-frequency component.
  • the first frequency distortion and the second frequency distortion only frequency-distorted the respective high-frequency component, while the respective low-frequency component of the relevant audio signal remains unchanged.
  • the proposed determination of the division frequency is therefore particularly advantageous for the use of frequency distortions in the suppression of acoustic feedback in a binaural hearing aid system.
  • the first provisional division frequency is transmitted from the first hearing aid to the second hearing aid, the second provisional division frequency being transmitted from the second hearing aid to the first hearing aid after receipt of the first provisional division frequency, and the division frequency in each case in the first hearing aid and in the second hearing aid same predetermined rule is determined based on the first provisional division frequency and the second provisional division frequency.
  • the two preliminary division frequencies are local in both hearing aids, and on the basis of a rule that is identical for both hearing aids and is stored, for example, in advance in a memory of each of the two hearing aids, the final division frequency at which the both audio signals are to be divided.
  • further communication can take place for this, for example communication requests to set up a transmission channel for the provisional division frequency, confirmation of receipt of a provisional division frequency regardless of the transmission of the value of the local provisional division frequency and / or synchronization requests for time synchronization, etc.
  • the first is preferred provisional division frequency only after a determined change in local requirements, in particular of the first acoustic feedback path, transmitted to the second hearing aid, and the synchronization process started. This considerably limits the effort and scope of communication required between the two hearing aids in order to determine the division frequency as best as possible.
  • the division frequency is advantageously determined in each case on the basis of the minimum of the first provisional division frequency and the second provisional division frequency.
  • the division frequency is determined directly as the minimum of the first provisional division frequency and the second provisional division frequency, or as a minimum within a plurality of predefined possible values for the division frequency, which in particular can form a discrete grid of possible values, so that e.g. on the basis of the lower of the two provisional division frequencies, the next lowest predetermined possible value is determined as the division frequency ("floor function").
  • a first input signal is generated from a sound signal in the environment in the first hearing aid by a first input converter, the first audio signal being generated in the first hearing aid on the basis of the first input signal by a first signal processing.
  • a second input signal is generated from the sound signal in the second hearing aid by a second input transducer, the second audio signal being generated in the second hearing aid on the basis of the second input signal by a second signal processing.
  • an input signal is generated from a sound signal in the environment using the input transducer, the signal components of which are usually subjected to user-specific signal processing are, for example a frequency band-wise amplification and noise suppression as well as dynamic compression, etc.
  • the amplification factors in the individual frequency bands are usually determined as a function of a hearing impairment to be corrected by the user, for example using an audiogram.
  • the frequency distortion of the audio signal resulting from the signal processing, and thus the proposed determination of the division frequency in a binaural hearing aid system, are particularly favorable, since this advantageously enables acoustic feedback to be corrected.
  • a first output signal is preferably generated on the basis of the first audio signal and is converted into a first output sound signal by a first output transducer of the first hearing device, with acoustic feedback being suppressed on the basis of the first frequency-distorted audio signal via a first acoustic feedback path from the first output transducer to the first input transducer.
  • the first output signal is generated on the basis of the first frequency-distorted audio signal.
  • a second output signal is generated, which is converted into a second output sound signal by a second output converter of the second hearing device, with acoustic feedback via a second acoustic feedback path from the second using the second frequency-distorted audio signal
  • Output converter to the second input converter is suppressed.
  • the division frequency is expediently updated in response to an external triggering event.
  • the triggering event here is preferably a change in the sound signal in the environment, a change in the first and / or in the second feedback path, a user input, a change in the first output signal resulting from a user input and a changed classification of the hearing situation by the hearing aid or the binaural hearing aid system.
  • the division frequency is always adapted when the external circumstances change, that is to say the sound signal of the surroundings and / or in particular the first acoustic feedback path, so that the division frequency is always adapted to the current circumstances.
  • the external conditions, in particular the first acoustic feedback path remain stable, no adjustment is necessary, so that an update is not carried out. This saves battery power because there are no unnecessary updating processes, which would also be associated with transmission power for the transmission processes.
  • the division frequency is updated in response to an internal triggering event.
  • the internal triggering event can be formed by a periodic transmitter value, so that, for example, the division frequency is temporarily set to a predetermined, preferably low value, particularly preferably the lowest possible value at regular time intervals, in order to make a valid estimate for the respective feedback path even at low values To get frequencies.
  • the frequency of division is then updated again using the method described above.
  • the invention further specifies a binaural hearing aid system with a first hearing aid and a second hearing aid, the binaural hearing aid system being set up to carry out the method described above.
  • the advantages specified for the method and for its further developments can be applied here analogously to the binaural hearing aid system.
  • a binaural hearing aid system 2 is shown in a block diagram.
  • the binaural hearing aid system 2 comprises a first hearing aid 4a and a second hearing aid 4b.
  • a first input signal 10a is generated from a sound signal 6 of the environment in the first hearing aid 4a by means of a first input converter 8a
  • a second input signal 10b is generated in the second hearing aid 4b by means of a second input converter 8b.
  • the first input converter 8a and the second input converter 8b are each provided by a microphone.
  • the respective input signal 10a, 10b is now mixed with a first or second compensation signal 12a, 12b and the resulting first or second compensated signal 14a, 14b is fed to a first or second signal processing 16a, 16b, which in each case generates an intermediate signal which is to be referred to here as the first or second audio signal 18a, 18b.
  • a first output signal 20a and a second output signal 20b are generated on the basis of the first and second audio signals 18a, 18b, which are converted into first and second output sound signals 24a, 24b by a first output converter 22a and a second output converter 22b, respectively.
  • the first and second output converters 22a, 22b are each given by a loudspeaker.
  • a first acoustic feedback path 26a is formed, via which an acoustic feedback takes place.
  • the first or second compensation signal 12a, 12b is now generated in a first or second adaptive filter 28a, 28b.
  • the first frequency distortion 30a which is given here by a frequency shift by a constant amount, is applied to the first audio signal 18a only above a division frequency tf, which divides the first audio signal 18a into a first high-frequency component HF1 and a first low-frequency component NF1 divides.
  • the resulting first frequency-distorted audio signal 32a - which comprises the frequency-shifted first high-frequency component HF1 of the first audio signal 18a - is now supplied on the one hand to the first adaptive filter 28a for generating the first compensation signal 12a, and on the other hand passed as the first output signal 20a to the first output converter 22a.
  • the respective compensation signal 12a, 12b is only generated in those frequency bands in which suppression of the acoustic feedback is necessary at all.
  • frequency distortion 30a, 30b is used for decorrelation over the entire frequency range in which the feedback is to be suppressed. That is to say, by determining the division frequency tf not only the application range of the respective frequency distortion 30a, 30b is determined in the present case, but also the frequency range of the two compensation signals 12a, 12b and thus the application range of the suppression of the acoustic feedback.
  • a first provisional division frequency tf1 is first transmitted from the first hearing device 4a to the second hearing device 4b when the first acoustic feedback path 26a changes physically.
  • the second hearing aid 4b receives the first provisional division frequency tf1 and, in turn, uses the second acoustic feedback path 26b, which could also have changed slightly, to determine a second provisional division frequency tf2, which is transmitted to the first hearing aid 4a. If there has been no change in the second acoustic feedback path 26b since the division frequency tf was last updated, then the current division frequency tf can also be transmitted as the value of the second provisional division frequency tf2.
  • Both hearing aids 4a, 4b now each have the first and the second provisional division frequency tf1, tf2.
  • the minimum of the first provisional division frequency tf1 and the second provisional division frequency tf2 is now defined as the division frequency tf.
  • the first audio signal 18a is then divided at the division frequency tf as described into a first high-frequency component HF1 and a first low-frequency component NF1, the first high-frequency component HF1 being frequency-shifted and, as the first frequency-distorted audio signal 32a, the first adaptive filter 28a for the Generation of the first compensation signal 12a is supplied.

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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)
  • Stereophonic System (AREA)
  • Circuit For Audible Band Transducer (AREA)
EP17207542.6A 2017-01-25 2017-12-15 Verfahren zum betrieb eines binauralen hörgerätesystems Active EP3355592B1 (de)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102017201195.5A DE102017201195A1 (de) 2017-01-25 2017-01-25 Verfahren zum Betrieb eines binauralen Hörgerätesystems

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EP3355592A1 EP3355592A1 (de) 2018-08-01
EP3355592B1 true EP3355592B1 (de) 2020-05-20

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US (1) US10277991B2 (da)
EP (1) EP3355592B1 (da)
CN (1) CN108347684B (da)
DE (1) DE102017201195A1 (da)
DK (1) DK3355592T3 (da)

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Publication number Priority date Publication date Assignee Title
US10319364B2 (en) * 2017-05-18 2019-06-11 Telepathy Labs, Inc. Artificial intelligence-based text-to-speech system and method
US10986447B2 (en) * 2019-06-21 2021-04-20 Analog Devices, Inc. Doppler compensation in coaxial and offset speakers
DE102020213051A1 (de) * 2020-10-15 2022-04-21 Sivantos Pte. Ltd. Verfahren zum Betrieb eines Hörhilfegeräts sowie Hörhilfegerät

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EP1699261B1 (en) * 2005-03-01 2011-05-25 Oticon A/S System and method for determining directionality of sound detected by a hearing aid
DK2317778T3 (da) * 2006-03-03 2019-06-11 Widex As Høreapparat og fremgangsmåde til at anvende forstærkningsbegrænsning i et høreapparat
DE102006014022A1 (de) 2006-03-27 2007-10-11 Siemens Audiologische Technik Gmbh Hörgerätesystem mit binauralem DataLogging und entsprechendes Verfahren
DE102008015263B4 (de) * 2008-03-20 2011-12-15 Siemens Medical Instruments Pte. Ltd. Hörsystem mit Teilbandsignalaustausch und entsprechendes Verfahren
DE102009021310B4 (de) * 2009-05-14 2011-02-24 Siemens Medical Instruments Pte. Ltd. Binaurale Hörvorrichtung und Verfahren zum Betrieb einer binauralen Hörvorrichtung mit Frequenzverzerrung
US8548180B2 (en) * 2009-11-25 2013-10-01 Panasonic Corporation System, method, program, and integrated circuit for hearing aid
JP5500125B2 (ja) * 2010-10-26 2014-05-21 パナソニック株式会社 補聴装置
DK2563045T3 (da) 2011-08-23 2014-10-27 Oticon As Fremgangsmåde og et binauralt lyttesystem for at maksimere en bedre øreeffekt
US9414150B2 (en) * 2013-03-14 2016-08-09 Cirrus Logic, Inc. Low-latency multi-driver adaptive noise canceling (ANC) system for a personal audio device
JP6285300B2 (ja) * 2014-07-07 2018-02-28 リオン株式会社 補聴器及びフィードバックキャンセラ
EP2988529B1 (de) 2014-08-20 2019-12-04 Sivantos Pte. Ltd. Adaptive teilungsfrequenz in hörhilfegeräten

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Publication number Publication date
CN108347684A (zh) 2018-07-31
EP3355592A1 (de) 2018-08-01
US20180213336A1 (en) 2018-07-26
DK3355592T3 (da) 2020-08-24
DE102017201195A1 (de) 2018-07-26
US10277991B2 (en) 2019-04-30
CN108347684B (zh) 2020-08-11

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