WO2023280359A1 - Procédés d'adaptation pour prothèse auditive et prothèse auditive configurée pour mettre en oeuvre de tels procédés d'adaptation - Google Patents

Procédés d'adaptation pour prothèse auditive et prothèse auditive configurée pour mettre en oeuvre de tels procédés d'adaptation Download PDF

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Publication number
WO2023280359A1
WO2023280359A1 PCT/DK2022/000158 DK2022000158W WO2023280359A1 WO 2023280359 A1 WO2023280359 A1 WO 2023280359A1 DK 2022000158 W DK2022000158 W DK 2022000158W WO 2023280359 A1 WO2023280359 A1 WO 2023280359A1
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WO
WIPO (PCT)
Prior art keywords
hearing aid
user
volume control
insertion gain
setting
Prior art date
Application number
PCT/DK2022/000158
Other languages
English (en)
Inventor
Christian Rossing Kraft
Bo PETERSEN.
Original Assignee
Audientes A/S
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 Audientes A/S filed Critical Audientes A/S
Publication of WO2023280359A1 publication Critical patent/WO2023280359A1/fr

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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
    • H04R25/35—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
    • H04R25/55—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
    • H04R25/558—Remote control, e.g. of amplification, frequency
    • 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
    • H04R2430/00—Signal processing covered by H04R, not provided for in its groups
    • H04R2430/01—Aspects of volume control, not necessarily automatic, in sound systems
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2430/00—Signal processing covered by H04R, not provided for in its groups
    • H04R2430/03—Synergistic effects of band splitting and sub-band processing

Definitions

  • the present invention relates to the field of hearing aids, more specifically to self-fitting hearing aids, i.e., hearing aids that are configured such that a hearing-impaired user can adjust the hearing aid himself/herself without the aid of a trained audiologist and/or external equipment and nevertheless obtain a hearing aid adjustment that is close to optimal. Still more specifically, the invention relates to adaptation/acclimatization methods for such hearing aids and hearing aids that are configured to apply such methods.
  • Adaptation/acclimatization of hearing aids is essential since most users, when getting their first hearing aid, already have a certain hearing loss, and hence getting full hearing restored typically leads to frustration, stress and potentially to rejecting the use of the hearing aid.
  • volume control keys do not generally satisfy the adaptation needs of the user, since such volume control keys generally work in a “linear” way, i.e. , that the gain of the hearing aid is changed equally at all frequencies for a given change ( ⁇ Vol) of the setting of the volume control key.
  • the terms "adaptation” and “acclimatization” are understood to have the same meaning, namely that a person that is not used to wear a hearing aid usually needs a certain period of time before he is able to fully benefit from using the hearing aid. This means that the person after being initially fitted with a hearing aid gradually adapts/acclimatizes to the use of the hearing aid and to obtain the best possible benefit from the hearing aid. For example, when a hearing-impaired person initially is fitted with a hearing aid, he will often prefer a gain at a given frequency that is below the gain, which from an audiological point of view would give him the best possible benefit from the hearing aid.
  • adaptive generally means getting used to the hearing aid, such that the user obtains the best possible benefit from using the hearing aid.
  • REIG Real-Ear Insertion Gain
  • the real-ear insertion gain is the difference in dB between the sound pressure level at a given position in the ear canal generated by a hearing aid placed on the ear of the user (the so-called “aided ear response”) and the sound pressure level generated at the same position in the ear canal when no hearing aid is placed on the ear (the so-called “open ear response”) when the user is situated in a given surrounding sound field.
  • the term “real-ear” indicates that the insertion gain is actually measured in the user’s ear.
  • A-REIG Adapted user REIG. This describes the real ear insertion gain that the user prefers after he/she is fully adapted/acclimatized to the use of a particular hearing aid.
  • N-REIG Novice user REIG. This is the gain that a typical / average first-time user would prefer right after fitting the hearing aid for the first time. This can according to some studies be on the order of 15 dB lower than A-REIG for the frequency where the user has the biggest hearing loss.
  • the present invention provides according to a first aspect a method for user-administered adaptation to the use of a hearing aid, which hearing aid is provided with a user-operable volume control and status determining means configured to determine if the hearing aid is in a non-adapted or fully adapted mode; wherein the method comprises the following steps: determine if the hearing aid is in the non-adapted mode or in the fully adapted mode;
  • the insertion gain of the hearing aid depends on the frequency f A and on the setting of the user-operable volume control in such a manner that a given change ⁇ Vol of the setting of the volume control results in a change of insertion gain ⁇ INSG(f A , HL) at one or more of the given frequencies f A that is a function F(f A , HL) of the hearing loss at each respective of the given frequencies f A when the hearing loss is at or above a given level dBHL at that specific frequency f A ;
  • the hearing aid when the hearing aid is in the fully adapted mode, applying in the hearing aid the insertion gain INSG(f A ) that the hearing aid is adjusted to when the mode determining means indicates that the user of the hearing aid is fully adapted to the use of the hearing aid, which insertion gain is regarded as the insertion gain that the user prefers after the user is fully adapted to the use of the hearing aid.
  • the status determining means is a user-operable switch that allows the user to set the hearing aid in either the non-adapted mode or the fully adapted mode.
  • the volume control of the hearing aid works in a linear way, i.e a given change of volume control setting ( ⁇ Vol) results in the same change of insertion gain ⁇ INSG(f A ) at all frequencies/in ail frequency bands.
  • the status determining means are autonomous means, i.e. not user-operable means, configured to set the hearing aid to the fully adapted mode based on the usage pattern of the volume control over a given period of time, in this embodiment, if the user turn the volume control to a position at which the insertion gain of the hearing aid is a predetermined REIG a predetermined number of times within a predetermined period of time, the status of the hearing aid is regarded as fully adapted, and the hearing aid is changed to the “fully adapted mode”, in which the volume controls work in a linear way, i.e a given change of volume control setting ( ⁇ Vol) results in the same change of insertion gain at all frequencies/in all frequency bands.
  • ⁇ Vol volume control setting
  • the above-mentioned predetermined REIG is a real ear insertion gain that is based on the user’s hearing threshold as a function of frequency, where the REIG is determined using a known hearing aid fitting method that for each standard audiology frequency prescribes a corresponding REIG.
  • the function (F(f A , HL)) is increasing with increasing hearing loss (HL),
  • the method comprises the steps of: a) based on the user’s hearing loss, at a plurality of given frequencies (f A ) determining a prescribed insertion gain Gp(f A ) at each of said frequencies (f A ); b) providing the user with the hearing aid adjusted to Gp(f A ); c) setting the hearing aid in the non-adapted mode; d) instructing the user to adjust the volume control of the hearing aid such that the sound provided by the hearing aid is experienced as pleasant in the user’s everyday surroundings; e) instructing the user, after a period of time, to readjust the volume control, if the user finds that the sound produced by the hearing aid could be improved; f) repeating steps (e) and (f) during an adaptation period to allow the user to determine the finally chosen adjustment of the volume control; g) when the user has reached a setting of the volumen control that the user finds provides the best possible sound reproduction of the hearing aid in the user’s everyday acoustic environments, setting the mode of the
  • the change of insertion gain is obtained by in each of a predetermined number of frequency bands B(f A ), each comprising one of said frequencies f A , changing the gain of the hearing aid of that particular frequency band.
  • the change of insertion gain is obtained by providing a controllable compression means in each of the frequency bands, where the compression characteristics of each individual of the controllable compression means depend on the setting of the volume control.
  • the compression threshold of each of the individual compression means is a function of the volume control setting.
  • the input/output characteristic of each of the individual controllable compression means comprises more than one threshold, whereby different degrees of compression, i.e. different compression ratios, can be applied in different input ranges.
  • the one or more thresholds of the individual controllable compression means is controlled by the volume control setting, In an embodiment of the fist aspect, the compression ratio of each of said individual compression means is a function of the volume control setting.
  • the change of insertion gain at each of sid frequencies f A is obtained by in each of said predetermined number of frequency bands B(f A ) changing the gain of the hearing aid of that particular frequency band and by changing the compression characteristics in each of these frequency bands.
  • a hearing aid provided with means for user-administered adaptation to the use of the hearing aid, which hearing aid is provided with: a) a user-operable volume control; b) status determining means configured to determine if the hearing aid is in a non-adapted or fuily adapted mode; c) an input transducer configured to convert an acoustic input signal to an electric output signal which output signal is provided, with or without amplification, to a filter bank providing respective second output signals to respective insertion gain determining units, each of which provides a third output signal; d) a combining unit configured to receive the third output signals and to provide a fourth output signal that is a combination of the third output signals; e) output amplifier means configured to receive the fourth output signal and to provide a fifth output signal to an output transducer configured to convert the fifth output signal to an acoustic signal that can be provided to the outer ear of the user; where the hearing aid is further provided with: f) a control
  • control unit provides, when the adaptation mode setting unit is set to adaptation, each respective of the controllable insertion gain determining units with a respective control signal such that a given change of the volume control setting ( ⁇ Vol) results in a corresponding change of insertion gain ( ⁇ INSG) of each of the controllable insertion gain units that is greater, the higher the user’s hearing loss in the respective frequency band is, when the hearing loss is above a predefined frequency dependent threshold, and constant when the hearing loss is below this threshold.
  • ⁇ Vol volume control setting
  • ⁇ INSG change of insertion gain
  • controllable insertion gain determining units are controilabie gain units.
  • controllable insertion gain determining units are controilabie compression units.
  • the compression threshold of each respective compression unit depends on the setting of the volume control.
  • the compression ratio of each respective compression unit depends on the setting of the volume control.
  • the input/output characteristic of each of the individual controilabie compression means comprises more than one threshold, whereby different degrees of compression, i.e. different compression ratios, can be applied in different input ranges.
  • the one or more thresholds of the individual controilabie compression means is controlled by the volume control setting.
  • the controllable insertion gain determining units are a combination of controllable gain units and controllable compression units configured such that for any given of said frequency bands either solely a controilabie insertion gain unit is used or solely a controilabie compression unit is used, or a combination of a controllable insertion gain unit and a controllable compression unit is used.
  • the status determining means is a user-operable switch that allows the user to set the hearing aid in either the non-adapted mode or the fully adapted mode.
  • the volume control of the hearing aid works in a linear way, i.e a given change of volume control setting ( ⁇ Vol) results in the same change of insertion gain at all frequencies/in all frequency bands.
  • the status determining means are autonomous means, i.e. not user-operable means, configured to set the hearing aid to the fully adapted mode based on the usage pattern of the volume control over a given period of time, in this embodiment, if the user turn the volume control to a position at which the insertion gain of the hearing aid is a predetermined REIG a predetermined number of times within a predetermined period of time, the status of the hearing aid is regarded as fully adapted, and the hearing aid is changed to the “fully adapted mode”, in which the volume controls work in a linear way, i.e a given change of volume control setting ( ⁇ Vol) results in the same change of insertion gain at all frequencies/in all frequency bands.
  • ⁇ Vol volume control setting
  • the above-mentioned predetermined REIG is a real ear insertion gain that is based on the user’s hearing threshold as a function of frequency, where the REIG is determined using a known hearing aid fitting method that for each standard audiology frequency prescribes a corresponding REIG.
  • figure 1 shows a plot of insertion gain (dB) as a function of frequency for a number of different settings of the volume control relating to an embodiment of the invention
  • figure 2 shows a table illustrating the effect of changes of the volume control setting on insertion gain (dB) at different frequencies relating to another embodiment of the invention
  • figure 3 shows a surface plot of insertion gain (dB) as a function of frequency and volume control setting relating to still another embodiment of the invention
  • figure 4 shows tables of input-output characteristics for three different settings of the volume control relating to an embodiment of the invention that applies frequency and volume control setting dependent compression
  • figure 5 shows the effect of the setting of the volume control on insertion gain of an embodiment of a hearing aid according to the invention
  • figure 8 shows a schematic block diagram of an embodiment of a hearing aid applying nonlinear gain as a function of volume control setting according to the principles of the invention
  • figure 7 shows
  • FIG. 1 With reference to figure 1 there is shown a plot of insertion gain at four frequencies: 500 Hz, 1000 Hz, 2000 Hz and 4000 Hz. in the plot, the solid line shows A-REIG relating to a rather severely hearing-impaired user who has the highest hearing loss at 4kHz.
  • the volume control (which in the present embodiment may comprise a number of discrete steps) is functioning a non-linear manner between the A-REIG and the N ⁇ REIG thereby reducing/amplifying the sounds more per step at the frequencies where the user has a higher hearing loss, while working in a linear manner above and below A-REIG and N ⁇ REIG.
  • volume control above A-REIG and below N-REIG is suggested in one embodiment of the invention to be linear, but since N-REIG (and even A-REIG) are based on a chosen prescription method (such as the half-gain rule or a NAL fitting rule) they may not necessarily apply to ail users, and the volume control may alternatively vary the insertion gain in a nonlinear/percentagewise manner as a function of the user’s hearing loss also above A-REIG and below N-REIG.
  • a chosen prescription method such as the half-gain rule or a NAL fitting rule
  • the percentage change of 5% used in the implementation shown in figure 1 can be changed if necessary, according to the specific circumstances such as hearing loss and user preferences.
  • the change should and could depend on the user’s hearing loss at the "worst” frequency and based on a general rule that a change of less than 2dB is not possible to hear (for any person).
  • the change of insertion gain for each press of the volume key or step of a volume control could be 2dB at the frequency with the largest hearing loss and could for other frequencies be less than 2dB, depending on the hearing loss at each frequency and percentage wise to the frequency with the worst hearing loss.
  • An example of the effect of volume control changes that is different from that of figure 1 Is shown in the table in figure 2.
  • FIG 3 With reference to figure 3 there is shown a surface plot of insertion gain (dB) as a function of frequency and volume control setting relating to still another embodiment of the invention.
  • the maximum insertion gain of 40 dB is obtained at 6 kHz and the insertion gain surface shows an insertion gain that would typically be used to compensate for a typical age- related sensory-neural hearing loss.
  • the first three figures relate to the first aspect of the invention, in which only a non-linear gain is applied.
  • the volume control can be set between maximum (10 equal to 100%) and minimum (0 equal to 0%).
  • the three volume control settings that are shown in figure 4 correspond to: 8 (80%), 7 (70%) and 6 (60%) and the tables are limited to frequencies of 4000 Hz, 3000 Hz, 2000 Hz and 1000 Hz. Of cause, compression could also be applied af other frequencies if desired.
  • the compression effect that is shown in the shaded cells of the tables is in this embodiment obtained by varying the compression threshold and maintaining the compression ratio, but it would also be possible to vary any of the other parameters that characterize audio compression such as compression ratio or attack and release time.
  • a novel (un-adapted) user of a hearing aid may require a prescribed insertion gain at 4 kHz of 30 dB, at 3 kHz of 25 dB, at 2 kHz of 20 dB and at 1 kHz of 15 dB.
  • This insertion gain as a function of frequency is obtained with the volume control set to position 8 as shown in figure 4a, With this setting of the volume control, no compression is applied.
  • the hearing aid is now set in adaptation mode and the user tries the hearing in his normal acoustic environments during an adaptation period.
  • the compressor With this setting of the volume control, the compressor becomes active about a certain frequency-dependent threshold (for instance at an input level of between 50 and 55 dBSPL at 4 kHz) and thereby limits the loudness of input levels in excess of 50 to 55 dBSPL at 4 kHz.
  • the user finds that he/she would actually prefer a volume control setting at 7, as the loudness at this setting is no longer annoying and the sound quality and speech intelligibility is actually improved by this increased volume control setting.
  • the user finds that the initial volume control setting of 8 (that corresponded to the prescribed setting) is in fact the best, as the loudness is no longer annoying, and the quality of the sound provided by the hearing aid is better at this setting than at the lower settings of the volume control.
  • the user is now fully adapted to the hearing aid according to this embodiment of the invention, and the hearing aid is set to the fully adapted mode.
  • FIG. 5 there is shown a non-limiting example of the effect of the setting of the volume control on insertion gain of an embodiment of a hearing aid according to the invention.
  • the dependency of insertion gain (dB) on volume control setting is shown at the frequencies 250 Hz, 500 Hz, 1000 Hz, 2000 Hz, 3000 Hz, 4000 Hz, 5000 Hz and 6000 Hz for a change of volume control setting from maximum (10) to minimum (0).
  • FIG 6 there is shown a schematic block diagram of an embodiment of a hearing aid applying non-linear gain as a function of frequency and volume control setting according to the principles of the invention.
  • the hearing aid that is generally indicated by reference numeral 1 comprises a microphone 2 the output signal S 1 of which id provided to an amplifier 3 that provides an amplified version of the microphone signal S 1 to a filter bank that in the shown - non-limiting - embodiment comprises four bandpass filters 4, 5, 6, 7 having passbands at 500 Hz, 1000 Hz, 2000 Hz and 4000 Hz. It is understood that fewer or more filter bands could alternatively have been used for instance corresponding to all standard audiometry frequencies and that the bandwidfhs of the filters can be chosen as desired.
  • the respective bandpass filters provide filtered output signals S 2 , S 3 , S 4 and S 5 respectively.
  • the filtered output signals are provided to respective controllable gain units 8, 9, 10,11, the gains of which can be controlled by control signals C 1 , C 2 , C 3 , C 4 provided by a control unit 12.
  • the respective output signals S 6 , S 7 , S 5 , S 9 from the controllable gain units 8, 9, 10, 11 are combined in a combination unit 15 thereby providing a combined output signal S 10 that is used to drive a hearing aid output transducer 17 (called loudspeaker or telephone).
  • the output amplified 16 may not necessarily be needed if the combined output signal S10 is powerful enough to drive the output transducer 17.
  • the control signals C 1 , C 2 , C 3 , C 4 are provided by the control unit 12 based on the setting of the adaptation mode setting unit 22 and the setting of the volume control 13, By means of the adaptation setting unit, there can be chosen at least between an adaptation mode in which the adaptation method of the invention is applied by the hearing aid and a fully adapted mode as described in the disclosure of the invention.
  • FIG 7 there is shown a schematic block diagram of an embodiment of a hearing aid applying frequency and volume control setting dependent compression according to the principles of the invention.
  • the hearing aid comprises a microphone 2 a microphone amplifier 3 and a filter bank 4, 5, 6, 7 that may be identical to the one used in the embodiment shown in figure 6 or configured otherwise as desired.
  • controllable gain units 8’, 9’. 10’, 1 T may be connected to the respective outputs from the filter bank, although these gain units can also form an integral part of each respective controllable compressor units 18, 19, 20, 21.
  • control signals C5, C6, C7 and C8 which are provided by the control unit 12 based on signals from the adaptation mode unit 22 and the setting of the volume control 13.
  • line 14 indicates that, when the hearing aid is in the fully adapted mode, the output of the hearing aid can simply be controlled by the user by varying the gain of the output amplifier 16. Furthermore, line 14’ indicates that also the input amplifier 3 can optionally be controlled by the control unit 12 for instance based on the setting to the volume control 13.
  • the embodiments of the hearing aid according to the invention are shown as simple block diagrams that for instance could be implemented as analog circuits, in practical implementations at least a number of these functional blocks may be implemented digitally and executed by appropriate software incorporated in the hearing aid.
  • the block diagrams shown in figures 6 and 7 primarily serve to illustrate the functional contents of the hearing aid according to the invention.

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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)
  • Tone Control, Compression And Expansion, Limiting Amplitude (AREA)

Abstract

L'invention concerne un procédé d'adaptation gérée par l'utilisateur à l'utilisation d'une prothèse auditive, ladite prothèse auditive étant pourvue d'un moyen de détermination de volume actionnable par l'utilisateur et d'un moyen de détermination d'état configuré pour déterminer si la prothèse auditive se trouve dans un mode non adapté ou complètement adapté; le procédé comprenant les étapes suivantes consistant à : déterminer si la prothèse auditive se trouve dans le mode non adapté ou dans le mode complètement adapté; lorsque la prothèse auditive se trouve dans le mode non adapté, le gain d'insertion de la prothèse auditive dépend de la fréquence fA et du réglage Vol de la commande de volume actionnable par l'utilisateur de telle sorte qu'un changement donné ΔVol du réglage de la commande de volume entraîne un changement de gain du gain d'insertion ΔINSG(fA, HL) à une ou plusieurs des fréquences données fA qui sont une fonction F(fA, HL) de la perte auditive à chaque fréquence respective des fréquences données fA lorsque la perte auditive est supérieure ou égale à un niveau donné dBHL à cette fréquence spécifique fA ; lorsque la prothèse auditive se trouve dans le mode complètement adapté, appliquer, au moyen de la prothèse auditive, le gain d'insertion INSG(fA) auquel est ajustée la prothèse auditive lorsque le moyen de détermination de mode indique que l'utilisateur de la prothèse auditive est complètement adapté à l'utilisation de la prothèse auditive, ledit gain d'insertion étant considéré comme étant le gain d'insertion que l'utilisateur préfère une fois que l'utilisateur est complètement adapté à l'utilisation de la prothèse auditive. L'invention concerne en outre une prothèse auditive configurée pour mettre en œuvre le procédé de l'invention.
PCT/DK2022/000158 2021-07-08 2022-07-05 Procédés d'adaptation pour prothèse auditive et prothèse auditive configurée pour mettre en oeuvre de tels procédés d'adaptation WO2023280359A1 (fr)

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EPEP21020358.4 2021-07-08
EP21020358.4A EP4117308A1 (fr) 2021-07-08 2021-07-08 Procédés d'adaptation pour une prothèse auditive et prothèse auditive incorporant de tels procédés d'adaptation

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Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1998031193A1 (fr) * 1997-01-10 1998-07-16 Resound Corporation Systeme de prothese auditive laissant le conduit auditif ouvert
EP3614380A1 (fr) * 2018-08-22 2020-02-26 Mimi Hearing Technologies GmbH Systèmes et procédés d'amélioration sonore dans des systèmes audio
DE102020114026A1 (de) * 2019-06-01 2020-12-03 Apple Inc. Mediensystem und verfahren zur berücksichtigung eines hörverlustes
US20200413206A1 (en) * 2016-04-11 2020-12-31 Enrique Gajstut Audio amplification electronic device with independent pitch and bass response adjustment
EP3783921A1 (fr) * 2019-08-23 2021-02-24 Sonova AG Réglage d'un gain dépendant de la fréquence d'un dispositif auditif
EP3783918A1 (fr) * 2019-08-22 2021-02-24 Sonova AG Commande d'une dynamique de volume d'un appareil auditif

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1998031193A1 (fr) * 1997-01-10 1998-07-16 Resound Corporation Systeme de prothese auditive laissant le conduit auditif ouvert
US20200413206A1 (en) * 2016-04-11 2020-12-31 Enrique Gajstut Audio amplification electronic device with independent pitch and bass response adjustment
EP3614380A1 (fr) * 2018-08-22 2020-02-26 Mimi Hearing Technologies GmbH Systèmes et procédés d'amélioration sonore dans des systèmes audio
DE102020114026A1 (de) * 2019-06-01 2020-12-03 Apple Inc. Mediensystem und verfahren zur berücksichtigung eines hörverlustes
EP3783918A1 (fr) * 2019-08-22 2021-02-24 Sonova AG Commande d'une dynamique de volume d'un appareil auditif
EP3783921A1 (fr) * 2019-08-23 2021-02-24 Sonova AG Réglage d'un gain dépendant de la fréquence d'un dispositif auditif

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