EP2584795B1 - Procédé de détermination d'une ligne caractéristique de compression - Google Patents

Procédé de détermination d'une ligne caractéristique de compression Download PDF

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EP2584795B1
EP2584795B1 EP12188476.1A EP12188476A EP2584795B1 EP 2584795 B1 EP2584795 B1 EP 2584795B1 EP 12188476 A EP12188476 A EP 12188476A EP 2584795 B1 EP2584795 B1 EP 2584795B1
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frequency
max
bark
hearing
bands
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German (de)
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EP2584795A3 (fr
EP2584795A2 (fr
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Ronny Hannemann
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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
    • H04R25/70—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
    • 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
    • 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
    • H04R25/353—Frequency, e.g. frequency 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
    • H04R25/552—Binaural

Definitions

  • the present invention relates to a method for determining a knee point of a frequency compression characteristic for a hearing device. Moreover, the present invention relates to a method for determining a frequency compression characteristic and a method for adjusting a binaural hearing system.
  • hearing device here is understood to mean any device which can be worn in or on the ear and triggers a sound stimulus, in particular a hearing device, headphones and the like.
  • Hearing aids are portable hearing aids that are used to care for the hearing impaired.
  • different types of hearing aids such as behind-the-ear hearing aids (BTE), hearing aid with external receiver (RIC: receiver in the canal) and in-the-ear hearing aids (IDO), e.g. Concha hearing aids or canal hearing aids (ITE, CIC).
  • BTE behind-the-ear hearing aids
  • RIC hearing aid with external receiver
  • IDO in-the-ear hearing aids
  • ITE canal hearing aids
  • the hearing aids listed by way of example are worn on the outer ear or in the ear canal.
  • bone conduction hearing aids, implantable or vibrotactile hearing aids are also available on the market. The stimulation of the damaged hearing takes place either mechanically or electrically.
  • Hearing aids have in principle as essential components an input transducer, an amplifier and an output transducer.
  • the input transducer is usually a sound receiver, z. As a microphone, and / or an electromagnetic receiver, for. B. an induction coil.
  • the output transducer is usually used as an electroacoustic transducer, z. As miniature speaker, or as an electromechanical transducer, z. B. bone conduction, realized.
  • the amplifier is usually integrated in a signal processing unit. This basic structure is in FIG. 1 shown using the example of a behind-the-ear hearing aid. In a hearing aid housing 1 for Carrying behind the ear, one or more microphones 2 are installed for recording the sound from the environment.
  • a signal processing unit 3 which is also integrated in the hearing aid housing 1, processes the microphone signals and amplifies them.
  • the output signal of the signal processing unit 3 is transmitted to a loudspeaker or earpiece 4, which outputs an acoustic signal.
  • the sound is optionally transmitted via a sound tube, which is fixed with an earmold in the ear canal, to the eardrum of the device carrier.
  • the power supply of the hearing device and in particular the signal processing unit 3 is effected by a likewise integrated into the hearing aid housing 1 battery. 5
  • Frequency compression is a relatively new technology in hearing aids. Frequency compression makes high-frequency information audible that can not be heard without this procedure. This is achieved by an algorithm that maps high frequency information from higher frequencies to lower frequencies. Originally low frequencies are replaced with the new information.
  • the US 2011/0249843 A1 describes a method for determining a knee point of a frequency compression characteristic for a hearing aid.
  • a critical frequency in the frequency domain is determined, the input signal is analyzed, a cutoff frequency is defined, a source frequency above the cutoff frequency is identified, and a target frequency band below the cutoff frequency is identified.
  • the DE 10 2009 058 415 A1 describes that in a hearing aid existing sounds and in particular their fundamental frequencies are to be determined in the input signal and the frequency transpositions are to be executed in dependence on the determined fundamental frequencies.
  • the transposed harmonics are again placed on the frequency raster of the fundamental frequency, so that the sound property is retained even after the frequency transposition.
  • the object of the present invention is therefore to be able to adjust the frequency compression of a hearing device in a simple manner so that it is possible to achieve advantages in terms of speech intelligibility.
  • the knee point of the frequency compression characteristic is determined as a function of the maximum audible frequency of the user (ie the highest frequency audible by the user) of the hearing device. It is assumed that a frequency compression characteristic has at least two legs, which are connected to each other at the knee point. By suitable displacement of the knee point in accordance with the prescribed rule, it is thus possible to optimize the information that can be transmitted in the audible range to the user of the hearing device.
  • the knee point is always set above 1.5 kHz. Since below the knee point the frequencies are typically transmitted uncompressed, in the case of the knee point above 1.5 kHz, all essential spectral components are transmitted unchanged, allowing the user to distinguish female voices from male voices.
  • the knee point is calculated using the Bark scale.
  • the Bark scale represents a psychoacoustic scale for the perceived pitch (tonality).
  • an allocation rule merely has to determine what the no_bands_down value in units of frequency bands (critical bands) is as a function of the maximum audible frequency. This value can be determined analytically for each frequency or, for example, in tabular form for individual frequency channels.
  • the lower part of a frequency compression characteristic is set from zero to the knee-point frequency. There is no compression in this frequency range.
  • the input value f_source_max is calculated to the output value f_max, which corresponds to the maximum audible frequency, using the Bark scale.
  • the algorithm for adjusting the frequency compression is closer to the psychoacoustic magnitude of the actual perceptible pitch.
  • a method for automatic adjustment of a binaural hearing system can be provided. It is particularly advantageous if the just described frequency compression characteristic is determined for that ear of the user of the hearing devices, which has the lower hearing loss. This ensures that the user of the hearing devices is not lost information that the user could still hear.
  • a frequency compression algorithm of a hearing aid or other hearing device is to be adjusted to provide a benefit in terms of speech intelligibility as compared to the case of a hearing aid without frequency compression. All other parameters of the hearing aid except the frequency compression are not changed (gain, level compression, etc.).
  • this frequency compression characteristic 10 has the in FIG. 3 illustrated structure. It has two linear sections 11 and 12, of which the first section 11 leads from the origin of the diagram to a knee point 13, and the second linear section 12 from the knee point 13 to an end point 14. The first linear section 11 has the slope one, so that no frequency compression takes place in the frequency range from zero to the knee point 13 or the frequency f_cutoff.
  • the frequency compression characteristic is therefore characterized by three parameters: the frequency f_cutoff, which represents the two coordinates of the knee point 13 and corresponds to the starting point of the actual frequency compression algorithm (all frequencies below f_cutoff are not affected by the algorithm), the frequency f_max, which is the maximum audible frequency and the frequency f_source_max corresponding to the original input frequency which is mapped to the output frequency f_max by the frequency compression characteristic.
  • the information in the original frequency range between f_cutoff and f_source_max is mapped to the area between f_cutoff and f_max. This reduction in bandwidth results in the audibility of high frequency information at lower frequencies at the expense of loss of original low frequency information.
  • the fact whether a user of a hearing device is suitable for the frequency compression according to the invention can be estimated reliably with two measurements. These measurements should be performed on the ear with better residual hearing.
  • the first measurement corresponds to an audiogram and the second measurement concerns the presence of a so-called dead region in the user's ear.
  • Based solely on the audiogram it is usually not possible to reliably determine the maximum audible frequency. This is because, for example, on the basilar membrane hairs are not excited by the sound waves directly to vibrate, but also by vibrations of the basilar membrane itself. Thus, for example, sound is heard, which is beyond an actual maximum audible frequency.
  • a dead area or its lower limit is determined by the so-called TEN test (see below).
  • a benefit achievable by a hearing aid can be calculated.
  • the calculation of the hearing aid output spectrum allows an estimate of the maximum audible frequency with the respective setting.
  • the intersection of the hearing aid output spectrum with the hearing loss (audiogram) determines the so-called maximum audible frequency f_max.
  • the calculated maximum audible frequency f_max can be changed to the resultant value.
  • the parameters of the frequency compression characteristic f_cutoff and f_source_max are determined according to the invention on the basis of frequency groups (critical bands), cf. Bark-Skala and Eberhard Zwicker: "Subdivision of the audible frequency range into critical bands", J. Acoust Soc. At the. Volume 33, page 248, Feb. 1961 ).
  • the starting point for the calculations is the maximum audible frequency f_max, which also corresponds to the lower frequency of a dead region.
  • the maximum audible frequency f_max is determined from the audiogram, which itself was measured in step 16, and possibly the TEN test, which was carried out in step 17.
  • the frequency f_cutoff in step 18 which represents the coordinates of the knee point 13.
  • the maximum source frequency f_source_max is determined as a function of the frequency f_max, which is mapped to the same frequency f_max.
  • a frequency compression characteristic curve 10 is determined with which the frequency compression algorithm is set.
  • the algorithm thus formed results in a frequency compression setting which ensures improved speech intelligibility.
  • the value f_max_bark should be changeable, for example if a lower frequency compression is desired. It should then be ensured, for example for a given filter bank, that the changed value f_max_bark represents a frequency between 2 kHz and 8 kHz.
  • f_cutoff 1960 ⁇ f_max_bark - no_bands_down + 0 . 53 / 26 . 28 - f_max_bark - no_bands_down
  • values for f_max ⁇ 2 kHz would lead to f_cutoff values ⁇ 1.5 kHz, which should be avoided from an audiological point of view. Therefore, values for f_max ⁇ 2 kHz are always set to 2 kHz, regardless of the actual measured value.
  • the above calculations ensure that audiological requirements 1 and 2 (see above) are met. These requirements are the basis for improving speech intelligibility through the frequency compression algorithm.
  • the values in the table here refer to a filter bank with 48 channels, each with a bandwidth of 250 Hz.
  • the illustrated fitting strategy for a frequency compression algorithm combines several hearing aid fitting steps, which were typically done manually (eg, measurements on 2 cm 3 test volumes).
  • the hearing threshold resulting from wearing the hearing aid is used for the estimation of the maximum audible frequency, as is the usual manual unbundling of the center frequencies of the fricatives "s" and “sch” in the hearing aid fitting.
  • This manual method for separating "s” and “sch” is now automated in the manner according to the invention.
  • the concept of critical bandwidths (frequency groups according to the Bark scale) is also used in the presented automatic adaptation, so that ultimately there are clear advantages in the automatic adaptation of frequency compression with regard to speech intelligibility.
  • the hearing impaired subjects show an improved speech intelligibility.
  • the adaptation strategy according to the invention of a frequency compression algorithm on the one hand shows a measurable improvement in speech intelligibility when frequency compression is activated and, on the other hand, a faster one Adaptation of hearing aids with frequency compression algorithms.
  • the adaptation can now be automated and does not require long measurements and fitting sessions.
  • it is also possible to predict an additional benefit with regard to speech intelligibility with frequency compression.
  • Another advantage is that improved speech intelligibility already sets up after initial adaptation.

Claims (5)

  1. Procédé de détermination d'un courbe caractéristique de compression de fréquence (10) transformant une valeur d'entrée f_in en une valeur de sortie f_out pour un dispositif auditif, comportant un point d'inflexion (13),
    - dans lequel on détermine une fréquence maximale audible f_max d'un utilisateur du dispositif et, en fonction de celle-ci, le point d'inflexion (13), dans lequel chaque valeur d'entrée f_in est égale à la valeur de sortie respective f_out en dessous du point d'inflexion (13) calculé à l'aide de valeurs de l'échelle de Bark,
    caractérisé
    - en ce qu'on établit une fréquence d'entrée initiale maximale audible f_source_max et une fréquence f_cutoff du point d'inflexion (13) de la courbe caractéristique de compression de fréquence (10) sur la base de groupes de fréquences, dans lequel on calcule la fréquence d'entrée originale audible maximale en tant que valeur d'entrée f_source_max pour la valeur de sortie f_max qui correspond à la fréquence maximale audible, au moyen de l'échelle de Bark, à l'aide de la formule : f_source_max = 1960 ⋅ f_max_bark + no_bands_up + 0 , 53 / 26 , 28 − f_max_bark + no_bands_up ,
    Figure imgb0010
     où f_max_bark est la fréquence maximale audible f_max, convertie en une valeur de Bark et où no_bands_up est un nombre de groupes de fréquences établi en fonction de la fréquence maximale audible, et
    - en ce qu'une coordonnée f_cutoff du point d'inflexion (13) est calculée à l'aide de la formule : f_cutoff = 1960 ⋅ f_max_bark − no_bands_down + 0 , 53 / ( 26 , 28 − f_max_bark − no_bands_down ,
    Figure imgb0011
     où f_max_bark est la fréquence maximale audible, convertie en une valeur de Bark et où no_bands_down est le nombre de groupes de fréquences établi en fonction de la fréquence maximale f_max.
  2. Procédé selon la revendication 1, dans lequel le point d'inflexion (13) est établi dans chaque cas au-dessus de 1,5 kHz.
  3. Procédé selon la revendication 1 ou 2, dans lequel un taux de compression maximal au-dessus du point d'inflexion (13) est égal à 4.
  4. Procédé de réglage d'un système auditif binaural comportant deux dispositifs auditifs, comprenant l'étape consistant à déterminer une courbe caractéristique de compression de fréquence (10) selon l'une quelconque des revendications 1 à 3.
  5. Procédé selon la revendication 4, dans lequel la courbe caractéristique de compression de fréquence (10) est déterminée selon l'une quelconque des revendications 1 à 3 pour l'oreille de l'utilisateur des dispositifs auditifs qui présente la plus faible perte auditive.
EP12188476.1A 2011-10-21 2012-10-15 Procédé de détermination d'une ligne caractéristique de compression Active EP2584795B1 (fr)

Applications Claiming Priority (1)

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DE102011085036A DE102011085036A1 (de) 2011-10-21 2011-10-21 Verfahren zum Ermitteln einer Kompressionskennlinie

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EP3030313B1 (fr) * 2013-08-09 2023-01-04 Advanced Bionics AG Système comprenant un stimulateur cochléaire et un deuxième stimulateur auditif
US10575103B2 (en) 2015-04-10 2020-02-25 Starkey Laboratories, Inc. Neural network-driven frequency translation
US9843875B2 (en) 2015-09-25 2017-12-12 Starkey Laboratories, Inc. Binaurally coordinated frequency translation in hearing assistance devices
CN114786107B (zh) * 2022-05-10 2023-08-22 东南大学 一种助听器验配方法

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US7248711B2 (en) * 2003-03-06 2007-07-24 Phonak Ag Method for frequency transposition and use of the method in a hearing device and a communication device
CN102684628B (zh) * 2006-04-27 2014-11-26 杜比实验室特许公司 修正音频动态处理器的参数的方法以及执行该方法的设备
DE102009058415B4 (de) * 2009-12-16 2012-12-06 Siemens Medical Instruments Pte. Ltd. Verfahren zur Frequenztransposition bei einem Hörhilfegerät sowie Hörhilfegerät
DK2375782T3 (en) * 2010-04-09 2019-03-18 Oticon As Improvements in sound perception by using frequency transposing by moving the envelope

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US20130101123A1 (en) 2013-04-25
DE102011085036A1 (de) 2013-04-25
EP2584795A3 (fr) 2014-07-16
EP2584795A2 (fr) 2013-04-24
US9232326B2 (en) 2016-01-05

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