EP4002885A1 - Procédé d'aide à l'utilisation d'un appareil auditif et appareil auditif - Google Patents

Procédé d'aide à l'utilisation d'un appareil auditif et appareil auditif Download PDF

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Publication number
EP4002885A1
EP4002885A1 EP21197154.4A EP21197154A EP4002885A1 EP 4002885 A1 EP4002885 A1 EP 4002885A1 EP 21197154 A EP21197154 A EP 21197154A EP 4002885 A1 EP4002885 A1 EP 4002885A1
Authority
EP
European Patent Office
Prior art keywords
configuration
hearing
hearing aid
digital filter
signal processing
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.)
Withdrawn
Application number
EP21197154.4A
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German (de)
English (en)
Inventor
Matthias Fröhlich
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 EP4002885A1 publication Critical patent/EP4002885A1/fr
Withdrawn legal-status Critical Current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
    • H04R25/50—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
    • 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
    • H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2460/00—Details of hearing devices, i.e. of ear- or headphones covered by H04R1/10 or H04R5/033 but not provided for in any of their subgroups, or of hearing aids covered by H04R25/00 but not provided for in any of its subgroups
    • H04R2460/01—Hearing devices using active noise cancellation

Definitions

  • the invention relates to a method to support the use of a hearing aid. It also relates to a corresponding hearing aid.
  • Hearing aids are usually referred to as classic hearing aids whose main function is to amplify acoustic signals. They are usually used to care for people with a hearing deficit due to a functional deficit of the hearing organ and in particular for the care of people who are hard of hearing.
  • Such hearing aids generally have at least one input converter, one signal processing device and one output converter as essential components.
  • the at least one input converter is in the form of an acousto-electric converter, ie in particular a microphone.
  • An electro-acoustic converter is used as the output converter, typically a miniature loudspeaker, which is also referred to as a "receiver".
  • the signal processing device is implemented by an electronic circuit implemented on a printed circuit board. Irrespective of this, the signal processing device has an amplifier or is set up to implement an amplifier function.
  • hearing aids are often set up to implement a filter function for noise suppression in addition to an amplifier function.
  • Corresponding filter functions and hearing aids designed for this purpose are known in principle and are known, for example, from EP 3 565 270 A1 , the DE 10 2015 207 706 B3 and the U.S. 2005/0256594 A1 refer to. Further examples of corresponding filter functions can be found in “ Dillon, Harvey: Hearing Aids, 2001, Thieme Verlag " and in “ Sandlin, Robert E.: Textbook of Hearing Aid Amplification, Second Edition, Singular Publishing Group " to find.
  • the invention is based on the object of specifying an advantageous method for supporting the use of a hearing aid and an advantageously configured hearing aid.
  • the method according to the invention serves to support the use of a hearing aid, in particular a hearing aid of the type mentioned at the outset.
  • the hearing aid according to the invention in turn is set up for the method according to the invention or at least one of the method steps and in particular for carrying out at least one method step of the method according to the invention.
  • the hearing aid has a signal processing device for generating an output signal as a function of an input signal, specifically in such a way that noise contained in the input signal is suppressed by means of a digital filter. This means that the signal processing device is set up for noise suppression.
  • an electrical input signal is then typically generated by means of a microphone of the hearing device as a function of an acoustic input signal, ie an acoustic signal from the area surrounding the hearing device.
  • This electrical input signal is then expediently fed to the signal processing device and first converted here into a digital input signal.
  • the digital input signal is then usually processed in a main processing step and a digital output signal is thereby generated.
  • the digital output signal in turn is expediently converted into an electrical output signal and finally converted into an acoustic output signal, typically by means of a loudspeaker of the hearing device.
  • the acoustic output signal preferably represents a simulation of the acoustic input signal, in which at least individual frequency components are amplified in comparison to the acoustic input signal. Accordingly, in the main processing, an amplification function is applied to the digital input signal. In addition, however, a filter function, namely the aforementioned digital filter, is applied to the digital input signal, with the filter function usually being applied first and then the amplifier function. Here, the filter effect serves to suppress noise.
  • a first configuration is now stored in the signal processing device for the filter function or the digital filter, on the basis of which the digital filter has a first filter effect.
  • a second configuration is stored in the signal processing device, as a result of which the filter has a second, reduced filter effect.
  • the reduced filter effect based on the filter effect of the first configuration expediently results in weaker noise suppression and/or at least weaker suppression of selected frequency components in the signal that is the filter function is processed.
  • a triggerable and time-controlled adaptation process is stored in the signal processing device in the course of the method.
  • the first configuration is specified as the starting configuration. If the adaptation process is then triggered, the adaptation process is then carried out by the signal processing device, ie in particular carried out automatically, as a result of which the configuration of the digital filter is transferred from the first configuration to the second configuration.
  • the first configuration for the digital filter is then specified, particularly at the start of the adaptation process in the signal processing device, and during the adaptation process the configuration for the digital filter is modified by the signal processing device continuously or in steps, i.e. in a predefined number of steps, until the end of the Adjustment process in the signal processing device, the second configuration for the digital filter is specified.
  • the adjustment by the adjustment process preferably takes place while the hearing device is being used by a hearing device wearer who is using the hearing device to at least partially compensate for a hearing deficit, namely his/her hearing deficit. More preferably, the adaptation takes place during an adjustment period after purchasing the hearing device, during which the hearing device wearer gets used to the hearing device. The adaptation process then preferably supports the hearing device wearer in getting used to it and thus in using the hearing device. In this case, the adaptation process can also be referred to as an acclimatization process.
  • the starting configuration is also specified by the manufacturer.
  • the hearing device is then typically pre-programmed and/or preset in the course of or at the end of the manufacturing process of the hearing device.
  • the pre-programming or the presetting which then also specifies the first configuration as the starting configuration for the digital filter
  • the hearing device is then released for sale and/or to the end user.
  • the triggerable and time-controlled adaptation process is preferably also stored in the signal processing device in the course of or at the end of the manufacturing process of the hearing aid, in particular by the hearing aid being pre-programmed and/or preset. This means that the adjustment process is also preferably specified by the manufacturer.
  • a fitting session is carried out with the city configuration in the course of the method, in which the hearing device is adapted to the individual needs of a hearing device wearer, ie in particular the aforementioned hearing device wearer.
  • a corresponding adjustment session usually takes place with a service provider for hearing aids, such as a hearing aid acoustician or hearing aid acoustician, who then adjusts the hearing aid and thus adapts it to the individual needs of the hearing aid wearer.
  • the service provider is typically also a user of the hearing device, even if only a temporary user.
  • the hearing aid wearer is the main user.
  • the hearing device is therefore adjusted to the individual needs of the hearing device wearer.
  • a previously described amplifier function of the hearing device is preferably adapted to the individual needs of the hearing device wearer, with the adaptation typically taking place as a function of what is known as an audiogram, which reflects the hearing deficit of the hearing device wearer.
  • the service provider typically also tests the hearing impression conveyed by the hearing device.
  • the service provider listens to the hearing aid, for example, before it is attached to the hearing loss or hearing deficit of the hearing aid wearer. In this case, the hearing device is then usually in the so-called delivery state. In some cases, a slight standard hearing loss is already programmed into the hearing aid when it is delivered.
  • the service provider can also listen into the hearing aid without having to connect it to fitting software. It is also typical that the service provider tests the hearing impression with the configuration of the amplifier function adapted to the hearing deficit of the hearing aid wearer.
  • the hearing impression of the hearing device is usually dependent on the hearing ability of the user, for example the service provider who is testing the hearing device.
  • the hearing impression of the hearing device is usually dependent, among other things, on the configuration of the filter function, ie the digital filter.
  • the first configuration which is preferably used as the starting configuration during the adjustment session, is now advantageously chosen independently of this in such a way that a particularly good hearing impression is conveyed to a user without a hearing deficit, ie in particular to the service provider.
  • the first configuration is preferably such that the digital filter with the first configuration has a strong filtering effect, or at least a stronger filtering effect than with the second configuration.
  • the digital filter in the first configuration then causes a stronger noise suppression than in the second configuration.
  • the second configuration is therefore preferably selected in such a way that a particularly good hearing impression is conveyed to a user with a hearing deficit, ie in particular to a hearing aid wearer.
  • the second configuration is preferably such that the digital filter with the second configuration has a weak filter effect or at least a reduced filter effect compared to the filter effect of the first configuration.
  • the second configuration is then also advantageous for the user with hearing loss, ie in particular for the hearing aid wearer, since a corresponding filter function, as is known, not only suppresses unwanted noise but also filters out other signal components.
  • (strong) noise reduction also has a negative effect, for example on speech intelligibility.
  • This negative effect is typically weaker with weaker noise suppression, and for this reason too the second configuration with the second reduced filter effect is advantageous for the user with hearing impairments, since the second configuration typically results in better speech intelligibility.
  • a previously described adjustment session is preferably carried out with the starting configuration in the course of the method.
  • a previously described amplifier function of the signal processing device is also preferably adapted to the individual needs of the hearing aid wearer, ie the main user, during the adaptation session, with the adaptation typically being based on what is known as an audiogram.
  • the amplifier function is typically adapted as a function of the hearing deficit of the hearing device wearer, which is caused by a functional deficit of the hearing organ of the hearing device wearer.
  • the adjustment process is then triggered or started, for example by a start command being fed into the hearing aid, in particular by the service provider.
  • the adaptation process is carried out after a specified wearing time of the hearing device, in which the hearing device wearer uses the hearing aid, triggered in particular automatically.
  • a specified wearing time of the hearing device for example, when the hearing device is switched on for the first time, a countdown or a timer or a counter is activated, which then finally automatically triggers or starts the adaptation process after a predetermined period of time.
  • the wearing time in the hearing aid is determined as a function of the state of charge of an accumulator in the hearing aid or as a function of the remaining charge of a battery in the hearing aid.
  • a mobile data processing unit for example a smartphone
  • the mobile data processing unit is preferably coupled to the hearing device at least temporarily, in particular for the purpose of data transmission.
  • Another typical variant of the method is one in which the adaptation process extends over more than two days and in particular more than two weeks.
  • the adaptation is more preferably carried out in such a way that the filter effect of the digital filter is successively reduced over a longer period of time.
  • a linear reduction for example, is expedient here.
  • the reduction usually takes place in a number of discrete stages, with at least five stages typically being provided, in particular more than ten.
  • the filter effect is reduced by one level every 24 hours, preferably over at least ten and more preferably at least 20 days.
  • the reduced filter effect of the digital filter in the second configuration is limited to a predetermined frequency range. This means that the second filter effect in the specified frequency range is reduced compared to the first filter effect in this frequency range. Outside this predetermined frequency range, however, the filter effect of the digital filter in the second configuration preferably corresponds approximately or exactly to the filter effect of the digital filter in the first configuration.
  • the specified frequency range is preferably specified in an adjustment session, ie in particular an aforementioned adjustment session, by specifying an individual frequency range.
  • the second configuration is stored in the adjustment session in the signal processing device or is at least adjusted by specifying an individual frequency range.
  • the individual frequency range is more preferably dependent on the main user, that is to say the hearing device wearer, with the individual frequency range advantageously extending over a frequency range over which the hearing deficit of the hearing device wearer also extends.
  • Hearing aid 2 shown schematically is designed as a so-called behind-the-ear hearing aid. It has a BTE housing 4 which is designed to be worn behind an ear (not shown) of a user (not shown), in particular a hearing aid wearer, of the hearing aid 2 .
  • a sound tube 6 is connected to the BTE housing 4, via which an acoustic output signal generated within the BTE housing 4 is forwarded to an earpiece 8. With the earpiece 8, the acoustic output signal is then coupled into the user's ear.
  • a microphone 10 as an acousto-electrical input converter, a signal processing device 12, a loudspeaker 14 as an electro-acoustic output converter and an accumulator 16 or a battery are also arranged inside the BTE housing 4 .
  • the hearing device 2 designed in this way is set up to generate an electrical input signal as a function of an acoustic input signal, ie an acoustic signal from the environment of the hearing device 2, by means of the microphone 10 of the hearing device 2 in a basic operating mode.
  • This electrical input signal is then expediently fed to the signal processing device 12 and is first converted here into a digital input signal.
  • the digital input signal is then processed in a main processing step and a digital output signal is thereby generated.
  • the digital output signal is in turn converted into an electrical output signal and finally converted into an acoustic output signal by means of the loudspeaker 14 of the hearing aid 2 .
  • the acoustic output signal represents a simulation of the acoustic input signal, in which at least individual frequency components are amplified in comparison to the acoustic input signal. Accordingly, in the main processing, an amplification function is applied to the digital input signal. In addition, a filter function in the form of a digital filter is also applied to the digital input signal, with the filter function preferably being applied first and then the amplifier function. Here, the filter effect and thus the digital filter serves to suppress noise.
  • the manufacturer of the hearing aid 2 (not shown) stores a first configuration in the signal processing device for the filter function or the digital filter, based on which the digital filter has a first filter effect.
  • the manufacturer stores a second configuration for the digital filter in the signal processing device, as a result of which the filter has a second, reduced filter effect.
  • the reduced filter effect based on the filter effect of the first configuration results in weaker noise suppression and/or at least weaker suppression of selected frequency components in the signal that is processed with the filter function.
  • a triggerable and time-controlled adaptation process is stored in the signal processing device by the manufacturer.
  • the manufacturer for the digital filter the first configuration is specified as the start configuration. All of this usually happens at the end of the manufacturing process of the hearing aid 2.
  • a fitting session is carried out, in which the hearing device 2 is adapted to the individual needs of the hearing device wearer, not shown.
  • that adaptation session is carried out with the city configuration which is advantageous for such an adaptation session.
  • a corresponding fitting session usually takes place with a service provider for hearing aids, such as a hearing care professional, who is also not shown.
  • the service provider is also a user of the hearing aid 2, albeit only a temporary user.
  • the hearing aid wearer is the main user.
  • the previously described amplifier function of the hearing aid 2 is typically also adjusted to the individual needs of the hearing aid wearer, with the adjustment typically taking place as a function of a so-called audiogram which reflects the hearing deficit of the hearing aid wearer.
  • the adjustment process is then triggered or started, for example by the service provider feeding a start command into the hearing device.
  • the adjustment process is automatically triggered after a predetermined wearing time of the hearing device 2 of, for example, five days, during which the hearing device wearer uses the hearing device 2 .
  • a countdown is activated, by which the adjustment process is then finally automatically triggered or started after the specified time period, ie the specified wearing time.
  • the stored adaptation process is executed by the signal processing device, as a result of which the configuration of the digital filter is automatically transferred from the first configuration to the second configuration becomes.
  • the adjustment process also extends over four weeks as an example.
  • the adaptation takes place in such a way that the filter effect of the digital filter is gradually reduced. To this end, the reduction takes place in a number of discrete stages, with 28 stages being provided in the exemplary embodiment.
  • the filter effect is reduced by one level every 24 hours.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Soundproofing, Sound Blocking, And Sound Damping (AREA)
EP21197154.4A 2020-11-13 2021-09-16 Procédé d'aide à l'utilisation d'un appareil auditif et appareil auditif Withdrawn EP4002885A1 (fr)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
DE102020214329.3A DE102020214329A1 (de) 2020-11-13 2020-11-13 Verfahren zur Unterstützung bei der Nutzung eines Hörgerätes und Hörgerät

Publications (1)

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EP4002885A1 true EP4002885A1 (fr) 2022-05-25

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EP21197154.4A Withdrawn EP4002885A1 (fr) 2020-11-13 2021-09-16 Procédé d'aide à l'utilisation d'un appareil auditif et appareil auditif

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Country Link
US (1) US20220159393A1 (fr)
EP (1) EP4002885A1 (fr)
CN (1) CN114501278A (fr)
DE (1) DE102020214329A1 (fr)

Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2001078485A2 (fr) * 2000-04-14 2001-10-25 Kammermeier, Heike Prothese auditive a adaptation a commande par temps de fonctionnement
DE60006255T2 (de) * 1999-09-02 2004-08-12 Gn Resound A/S Hörgerät und damit kommunikationsfähige externe einheit
US20050256594A1 (en) 2004-04-29 2005-11-17 Sui-Kay Wong Digital noise filter system and related apparatus and methods
EP2254354A1 (fr) * 2009-05-19 2010-11-24 Siemens Medical Instruments Pte. Ltd. Procédé d'acclimatation d'un dispositif auditif programmable et dispositif auditif correspondant
US20150036851A1 (en) * 2013-08-02 2015-02-05 Starkey Laboratories, Inc. Automatic hearing aid adaptation over time via mobile application
DE102015207706B3 (de) 2015-04-27 2016-08-18 Sivantos Pte. Ltd. Verfahren zur frequenzabhängigen Rauschunterdrückung eines Eingangssignals
EP3565270A1 (fr) 2018-04-30 2019-11-06 Sivantos Pte. Ltd. Procédé de réduction du bruit dans un signal audio

Family Cites Families (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE10021985A1 (de) * 2000-04-14 2001-10-25 Simon Kammermeier Hörgerät mit betriebszeitgesteuerter Anpassung

Patent Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE60006255T2 (de) * 1999-09-02 2004-08-12 Gn Resound A/S Hörgerät und damit kommunikationsfähige externe einheit
WO2001078485A2 (fr) * 2000-04-14 2001-10-25 Kammermeier, Heike Prothese auditive a adaptation a commande par temps de fonctionnement
US20050256594A1 (en) 2004-04-29 2005-11-17 Sui-Kay Wong Digital noise filter system and related apparatus and methods
EP2254354A1 (fr) * 2009-05-19 2010-11-24 Siemens Medical Instruments Pte. Ltd. Procédé d'acclimatation d'un dispositif auditif programmable et dispositif auditif correspondant
US20150036851A1 (en) * 2013-08-02 2015-02-05 Starkey Laboratories, Inc. Automatic hearing aid adaptation over time via mobile application
DE102015207706B3 (de) 2015-04-27 2016-08-18 Sivantos Pte. Ltd. Verfahren zur frequenzabhängigen Rauschunterdrückung eines Eingangssignals
EP3565270A1 (fr) 2018-04-30 2019-11-06 Sivantos Pte. Ltd. Procédé de réduction du bruit dans un signal audio

Non-Patent Citations (2)

* Cited by examiner, † Cited by third party
Title
DILLON, HARVEY: "Hearing Aids", 2001, THIEME VERLAG
SANDLIN, ROBERT E.: "Textbook of Hearing Aid Amplification", SINGULAR PUBLISHING GROUP

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Publication number Publication date
US20220159393A1 (en) 2022-05-19
CN114501278A (zh) 2022-05-13
DE102020214329A1 (de) 2022-05-19

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