WO2013139106A1 - Procédé de détermination du gain de compensation auditive d'un dispositif de prothèse auditive - Google Patents

Procédé de détermination du gain de compensation auditive d'un dispositif de prothèse auditive Download PDF

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Publication number
WO2013139106A1
WO2013139106A1 PCT/CN2012/080147 CN2012080147W WO2013139106A1 WO 2013139106 A1 WO2013139106 A1 WO 2013139106A1 CN 2012080147 W CN2012080147 W CN 2012080147W WO 2013139106 A1 WO2013139106 A1 WO 2013139106A1
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Prior art keywords
hearing
frequency
compensation gain
ear
compensation
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PCT/CN2012/080147
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English (en)
Chinese (zh)
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陈章立
胡广书
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清华大学
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Publication of WO2013139106A1 publication Critical patent/WO2013139106A1/fr

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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
    • H04R25/35—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
    • H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting

Definitions

  • the present invention relates to a method of determining parameters of a hearing aid device, and more particularly to a method for determining hearing compensation gain of a hearing aid device based on damage to the outer ear hair cells and inner hair cells. Background technique
  • Hearing loss ie, deafness
  • the patient can perform sound amplification by wearing a hearing aid device to restore or partially restore sound perception. Due to the complexity of the human ear, different degrees of hearing loss at different frequencies are compensated for different levels of input sound. In order to accurately and effectively give the compensation gain, the formula for the appropriate compensation gain that various hearing loss conditions should give under various input sound conditions based on relevant research experience and results is called the hearing aid fitting formula.
  • the existing hearing aid fitting formula is mainly based on the hearing threshold to calculate the compensation gain, but the hearing loss information reflected by the hearing threshold is not sufficient, mainly because the hearing loss is the result of the joint action of the outer hair cell damage and the inner hair cell damage of the ear, and External hair cell damage and inner hair cell damage play different roles in the process of hearing loss, namely: outer hair cell damage causes rise in hearing threshold, decreased auditory frequency resolution, and decreased auditory nonlinear gain, while inner hair cells Damage generally only causes the hearing threshold to rise, so the result of calculating the compensation gain based only on the hearing threshold is not very accurate.
  • the existing hearing compensation gain needs to be realized in the hearing aid device through the multi-channel compression amplification algorithm.
  • the existing hearing aid fitting formula generally only gives 50 dB SPL (Sound Pressure Level), 65 dB SPL and 85 dB SPL sound intensity.
  • the compensation gain of the long-term average speech spectrum is then determined by setting the number of channels and the frequency at the intersection of the channels, thereby determining the compression threshold and compression ratio of each channel, so that the multi-channel amplification algorithm can achieve the compensation under the above three input sound intensity conditions.
  • the compensation of other input sound intensity is automatically calculated, but there are two problems in the above method: 1. The optimal number of channels and the frequency of channel intersection cannot be quickly and accurately selected; 2. Others are different from long-term average speech.
  • the compensation gain calculated from the sound input of the spectrum may deviate from the ideal compensation gain. Summary of the invention
  • an object of the present invention is to provide a method capable of quickly and accurately determining the hearing compensation gain of a hearing aid device or an electronic device having a hearing aid function.
  • a method of determining a hearing compensation gain of a hearing aid device comprising the steps of: testing a hearing loss of a hearing loss person to determine a frequency CF at which gain compensation is required; based on normal hearing and impairment
  • the auditory loudness perception model calculates the compensation gain value IGohcdB(CF) of the outer ear hair cell damage ; based on the loudness perception model, calculates the compensation gain value IGIhcdB(CF) of the ear hair cell damage; IGohcdB(CF) and IGIhcdB (CF) is added to obtain the compensation gain IGdB(CF) of the hearing loss at the frequency CF.
  • a method for determining a hearing compensation gain of a hearing aid device comprising the steps of: 1) testing a hearing of a test subject to determine a frequency CF at which gain compensation is required; 2) based on The loudness perception model of normal auditory and impaired hearing, the damage value HLohcdB(CF) of the outer ear hair cells at the auditory damage frequency CF, and the compensation gain value IGohcdB(CF) of the outer ear hair cell damage ; 3) for the auditory damage frequency Intra-ear hair cell damage value HLihcdB(CF) at CF, the compensation gain value IGIhcdB(CF) for calculating hair cell damage in the ear; 4)
  • the hearing damage frequency CF is lower than 1000 Hz
  • the compensation gain at the frequency CF is based on The frequency CF is correspondingly attenuated, and the attenuation value is INTdB(CF); when the hearing impairment frequency CF is greater than or equal to 1000 Hz
  • IGohcdB(CF) IGohcdB(CF) + IGihcdB (CF) + INTdB(CF).
  • the compensation gain value of the outer ear hair cell damage in step 2) is IGohcdB(CF):
  • IGohcdB(CF) m [GdBN (CF) - GdBI (CF)] where m is the coefficient and m is calculated as:
  • GdBI(CF) is the active gain of the damaged ear
  • GdBN(CF) is the active gain of the normal ear.
  • Step 3 Compensation gain value of hair cell damage in the middle ear IGihcdB(CF):
  • IGihcdB (CF) 0.5 ⁇ max [HLihcdB (CF) , 40] where max represents the maximum value of both HLihcdB(CF) and 40.
  • the attenuation values of the compensation gains at different frequencies CF in step 4) are: the frequency CF is 125HZ corresponding to the attenuation value INTdB(CF) is -15dB, and the frequency CF is 250HZ corresponding to the attenuation value INTdB(CF) is -10 dB, The frequency CF is 500HZ corresponding to the attenuation value INTdB(CF) is -5 dB, the frequency CF is 1000HZ corresponding to the attenuation value INTdB(CF) is 0 dB, and other attenuation values below the 1000HZ frequency CF is INTdB(CF) Calculated by interpolation.
  • an electronic device having a hearing aid function comprising: a digital signal processor configured to calculate an ear hair cell damage of a hearing loss person based on a loudness perception model of normal hearing and damage hearing
  • the compensation gain value IGohcdB(CF) where CF is the center frequency at which the hearing loss of the hearing loss person needs to be compensated; based on the loudness sensation model, the compensation gain value IGIhcdB of the ear hair cell damage of the hearing loss person is calculated.
  • the output unit outputs a compensated sound signal.
  • the electronic device can be any of a hearing aid, an audio player, and a mobile phone.
  • FIG. 1 is a flow block diagram of an embodiment of a method of determining a hearing compensation gain of a hearing aid device of the present invention
  • 2(a) is a graph showing the relationship between the maximum active gain GdBm(CF) and the frequency CF in the embodiment of the present invention
  • Figure 2 (b) is an active gain GdB (CF) and passive excitation response in an embodiment of the invention
  • Figures 3 (a) ⁇ 3 (d) are the audiograms of four common hearing loss in the embodiment of the present invention
  • Figures 4 (a) ⁇ 4 (d) are for the four common hearing losses in Figure 3, using this A comparison of the compensation gain given by the hearing aid fitting formula of the embodiment of the invention and the existing NAL-NL2 fitting formula;
  • 5(a) to 5(h) show the use of the present invention for the two typical hearing loss scenarios of FIG. 3 when using time domain noise having the same spectrum as the long-term average speech spectrum as input.
  • FIG. 6(a) to 6(h) illustrate, according to an embodiment of the present invention, when an actual voice is used as an input, the same hearing loss situation as in FIG. 5, according to an embodiment of the present invention
  • an embodiment of the method for determining hearing compensation gain of a hearing aid device based on damage to the outer ear hair cells and inner hair cells of the present invention comprises the following steps:
  • the detection method generally selects some commonly used frequency points to perform auditory diagnosis on the ear of the testee.
  • the commonly used frequency point is 125. Hz, 250 Hz, 500 Hz, 1000 Hz, 2000 Hz, 4000 Hz, 6000 Hz and 8000 Hz.
  • the sound intensity that can be received by the test subject at each frequency is determined by diagnosis, and the audiogram of the testee's ear is obtained.
  • the audiogram of the tester's ear is compared with the normal ear's audiogram, and at which frequency the CF's hearing loss is determined, the hearing loss is appropriately compensated at this frequency CF.
  • the damage value of the ear outer hair cells at the hearing impairment frequency CF is HLohcdB(CF), and the hearing of the hearing normal ear and the hearing impairment ear is calculated at this frequency CF.
  • the difference in the positive gain at the point is the compensation gain value IGohcdB(CF) of the hair cell damage outside the ear.
  • the sound spectrum input to the ear of the subject under the free sound field condition is X(f)
  • the sound spectrum X(f) passes through the outer ear and the middle ear to filter the OME(f), and then reaches the ear cochlea.
  • the spectrum is Y(f):
  • Y(f) X(f) OME(f)
  • OME(f) is the English abbreviation for the outer ear and middle ear frequency response.
  • W PF (CF, f) is the frequency response of the auditory passive filter at frequency f CF
  • W PF (CF, f) is the frequency response of the auditory passive filter at frequency f CF
  • W PF (CF, f) is the frequency response of the auditory passive filter at frequency f CF
  • t u (CF) 15.6 tL (CF) and TU (CF) is a passive control frequency is CF auditory filter shape at the E PF (CF) can be calculated according to the active gain GdB (CF CF frequency hearing loss ear at )
  • the maximum active gain of the normal ear at the frequency CF is GdBmN(CF):
  • the frequency CF can be 125 Hz, 250 Hz, 500 Hz, 1000 Hz, 2000 Hz, 4000
  • Hz and 8000 Hz are respectively substituted into equation (5) to calculate the maximum active gain value GdBmN(CF) of the normal ear at different frequencies, and the calculation result is shown in Fig. 2 (a).
  • the abscissa in Figure 2 (a) represents the frequency CF in Hz, and the ordinate represents the maximum active gain GdBm(CF) in dB.
  • the circle in the figure indicates the frequency CF is 125Hz, 250 Hz, 500 Hz, 1000 Hz. ,
  • the solid line in the figure is the curve connecting the frequencies.
  • GdBml(CF) GdBmN (CF) - HLohcdB(CF) ( 6 )
  • the abscissa in Figure 2 (b) is the passive excitation response E PF dB(CF) in dB; the ordinate is the active gain GdB(CF)
  • the unit is dB; the top four thick solid lines in the figure correspond to the active gain of the normal ear, named GdBN(CF), where the letter N represents the normal ear, and the lower solid line corresponds to the active gain of the auditory ear, named It is GdBI(CF), where the letter I represents the damage ear, and the bottom line corresponds to the minimum value of the active gain, which is -13 dB.
  • the input spectrum is calculated as X by replacing GdBmN(CF) in equation (5) and GdBml(CF) in equation (6) with GdBm(CF) in equation (4), respectively.
  • the auditory active gains of hearing-impaired ears and hearing-impaired ears, GdBN(CF) and GdBI(CF) thus obtaining the compensation gain IGohcdB(CF) of the hearing aid fitting formula for external hair cell damage:
  • IG. hcdB (CF) m [GdBN ( CF) - GdBI ( CF)] ( 7 )
  • m is the coefficient and m is linear with the damage ear hearing gain GdBI(CF).
  • the slope and intercept of this linear relationship The distance varies with the change of the normal ear hearing gain GdBN(CF), and the formula for calculating m is:
  • the in-hair hair cell damage value at CF is HLihcdB(CF), and the compensation gain of the hair cell damage in the ear is calculated.
  • IGihcdB(CF) is:
  • IGihcdB (CF) 0.5.
  • HLihcdB (CF) ( 9 ) max represents the maximum value of both HLihcdB(CF) and 40, because when HLihcdB(CF) is greater than or equal to 40 dB, the hair cells in the ear may It has been completely damaged, so no further compensation is required. After the hair cells in the ear are damaged, part of the sensory function is not recovered due to sound amplification. It is not necessary to make the compensation gain equal to the degree of damage. Therefore, according to the experience, the coefficient (0.5) is multiplied by a factor of 0.5 in the present invention. There is no experimental means to verify the optimal value of this coefficient, so this coefficient may be further adjusted according to the specific damage situation, Adjust to 0.4 or 0.6.
  • the compensation gain of the frequency CF should be correspondingly attenuated according to the frequency CF to reduce the uplink masking effect (the masking effect is the classical effect of psychoacoustics, that is, the low frequency sound is easy to cover up)
  • the high-frequency sound, called "upstream" from low frequency to high frequency, and the attenuation value of IN at each frequency CF are as shown in Table 1:
  • the attenuation at other frequencies can be calculated by interpolation according to Table 1 above.
  • the hearing impairment frequency CF is greater than or equal to 1000 Hz, the attenuation value INTdB(CF) at the frequency CF is 0;
  • IGdB(CF) IG. hcdB (CF) + IGi cdB(CF) + INTdB (CF) (10)
  • the above compensation gain IGdB(CF) is the value at the frequency CF
  • the time domain signal input to the ear of the testee is calculated by short-time Fourier transform framing, and the input spectrum X(f) corresponding to the time domain signal of each frame is obtained, which is input to the testee due to the actual application.
  • the signal in the ear is a time domain signal
  • the input signal of the hearing aid fitting formula of the present invention is a spectrum signal, so that conversion between the time domain signal and the frequency domain signal is required in use.
  • Figures 3(a) to 3(d) the embodiment of the present invention cites four typical hearing loss conditions, and Figure 3(a) shows the hearing loss of a moderately flat MF; Figure 3 (b) Shows the hearing loss of the moderately ascending MG; Figure 3 (c) shows the hearing loss of the moderately steep MS;
  • FIG. (d) shows the hearing loss of the severe flat SF.
  • Each type of hearing loss includes the hearing threshold HLdB(CF) (— ⁇ — , solid circles in the circle), HLohcdB(CF) ( ⁇ & -, square dotted line), and HLihcdB (CF) in the ear. - ⁇ - , triangle dotted line).
  • Figures 4(a) to 4(d) are the compensation gains given by the hearing aid fitting formula of the embodiment of the present invention for the four common hearing losses in Figure 3 and the existing NAL-NL2 fitting formula. Compare the schematics.
  • the abscissa in the figure is the frequency f, the unit is Hz, and the ordinate is the compensation gain IGdB.
  • FIG. 4 (f) is a schematic diagram of the compensation gain of the MF-type hearing loss when the input is a long-term speech spectrum, using the hearing aid fitting formula and the NAL-NL2 fitting formula. The upper, middle and lower curves respectively correspond to The input sound intensity is 50 dB SPL, 65 dB SPL and 80 dB SPL; Figure 4 (b) is the MG type hearing loss. When the input is a long-term speech spectrum, the hearing aid fitting formula and the NAL-NL2 fitting are used.
  • Figure 4 (c) is a comparison of the compensation gains of the MS-type hearing loss using the hearing aid fitting formula and the NAL-NL2 fitting formula when the input is a long-term speech spectrum
  • d) is a schematic diagram of the compensation gain of the SF type hearing loss when the input is a long-term speech spectrum, using the hearing aid fitting formula and the NAL-NL2 fitting formula.
  • embodiments of the present invention provide long-term average speech spectral input at 50 dB SPL, 65 dB SPL, and 80 dB SPL sound intensity, after the present invention.
  • the gain compensation calculated by the hearing aid fitting formula of the embodiment (as shown by the solid line in the figure, corresponding to the 50 dB SPL, 65 dB SPL and 80 dB SPL input sound intensity from top to bottom), according to Australia
  • the compensation gain calculated by the National Acoustics Laboratory NAL-NL2 formula (as indicated by the dotted line in the figure, corresponds to 50 dB SPL, 65 dB SPL and 80 dB SPL input sound intensity from top to bottom).
  • the results calculated by the hearing aid fitting formula of the embodiment of the present invention have a similar trend to the results calculated by the NAL-NL2 formula, since the compensation gain given by the NAL-NL2 formula is already clinically available. It is widely used and proven to be effective, so it is appropriate to determine the hearing compensation gain of hearing aids.
  • Figure 5 illustrates the results of processing in accordance with an embodiment of the present invention.
  • Figure 5 (a) ⁇ 5 (c) The mark is time t, the unit is s, and the ordinate indicates the sound amplitude.
  • Figure 5 (d) ⁇ 5 (f) the abscissa is the frequency f, the unit is Hz, and the ordinate represents the sound spectrum, the unit is dB SPL
  • the abscissa of ⁇ 5 (h) is the frequency f, the unit is Hz, and the ordinate represents the compensation gain IGdB(f) in dB.
  • FIG. 5 (a) shows the noise time domain waveform input to the normal human ear. It is a time-domain waveform diagram of steady-state noise processed by a non-hearing aid formula with a duration of 2 s and a sound intensity of 65 dB SPL. The spectrum of the noise is the same as the long-term average speech spectrum.
  • Figure 5 (a) shows the noise time domain waveform input to the normal human ear. It is a time-domain waveform diagram of steady-state noise processed by a non-hearing aid formula with a duration of 2 s and a sound intensity of 65 dB SPL. The spectrum of the noise is the same as the long-term average speech spectrum.
  • (d) is the long-term spectrum of the noise (that is, the Fourier transform of the entire noise time domain waveform, which is different from the frame spectrum obtained by the short-time Fourier transform, but since the noise is steady-state noise, each frame spectrum It should be the same as the long-term spectrum) and is a schematic diagram of the steady-state noise that has not been processed by the hearing aid formula.
  • Fig. 5(b) shows the noise time domain waveform of the input damaged human ear after the algorithm of the embodiment of the present invention for the hearing loss situation of MF, that is, the MF type hearing loss is given by the hearing aid fitting formula.
  • a time-domain waveform diagram of steady-state noise obtained after compensating for gain.
  • Figure 5 (e) is a long-term spectrum of the noise, and is a spectrum diagram of steady-state noise obtained by using the hearing aid fitting formula of the present invention to give a compensation gain to the MF type hearing loss
  • Figure 5 (c) is for the MS The hearing loss situation, the noise time domain waveform of the human ear damaged by the input processed by the algorithm of the present invention, that is, the time domain waveform diagram of the steady state noise obtained by using the hearing aid fitting formula to compensate the MS type hearing loss .
  • Figure 5 (f) is a long-term spectrum of the noise, and is a spectrum diagram of the steady-state noise obtained by using the hearing aid formula to compensate the MS type of hearing loss.
  • Figure 5 (g) shows the difference between the spectra in Figure 5 (e) and Figure 5 (d), Figure 5
  • the black line in (g) represents the difference between the spectrum of Figure 5 (e) and the spectrum of Figure 5 (d).
  • the difference is the compensation gain of the algorithm for MF.
  • the gray line corresponds to the middle solid line in Figure 4 (a).
  • the gray line gives the compensation gain calculated by the fitting formula of the embodiment of the present invention directly using the input spectrum and the MF hearing loss condition of FIG. 5(d), and can represent the use of the hearing aid when the input sound intensity is 65 dB SPL.
  • the formula gives the compensation gain given to the MF.
  • Figure 5 (h) shows the difference between the spectra in Figure 5 (f) and Figure 5 (d)
  • the black line in the figure shows the difference between the spectrum of Figure 5 (f) and the spectrum of Figure 5 (d)
  • the gray line gives The compensation gain calculated by the hearing aid fitting formula of the embodiment of the present invention directly using FIG. 5(d) input spectrum and MS hearing loss condition
  • the gray line corresponds to the intermediate real in FIG. 4(c) Line, which can represent the compensation gain given to the MS by the hearing aid fitting formula when the input sound intensity is 65 dB SPL.
  • the gray and white lines in Fig. 5 (g) and Fig. 5 (h) are coincident with each other, which proves the correctness of the algorithm.
  • Figs. 6(a) to 6(h) when an actual speech (sound intensity 65 dB SPL) is given as an input, the same hearing loss as in Fig. 5 is given. (MF and MS), the processing results achieved by the hearing aid fitting formula and its algorithm of the embodiment of the present invention. Different from the steady-state noise in Figure 5, the actual speech is a time-varying signal, that is, the spectrum changes with time.
  • Figure 6 (a) is a time-domain waveform diagram of real speech processed by a non-fitted formula with a duration of 2 s and a sound intensity of 65 dB SPL;
  • Figure 6 (b) is a hearing aid fitting formula using an embodiment of the present invention Schematic diagram of the time domain waveform of the speech obtained by giving the compensation gain to the MF type hearing loss;
  • Figure 6 (c) is a time-domain waveform diagram of the speech obtained by giving the compensation gain to the MS type hearing loss using the hearing aid fitting formula;
  • (d) is a spectrum diagram of speech that has not been processed by the hearing aid formula;
  • Figure 6 (e) is a schematic diagram of the spectrum of speech obtained by using the hearing aid fitting formula to compensate the MF type hearing loss;
  • Figure 6 (f) Is a spectrum diagram of the speech obtained by using the hearing aid fitting formula to compensate the MS type hearing loss; the black line in Fig.
  • FIG. 6 (g) is the difference between the spectra in Fig. 6 (e) and Fig. 6 (d) Schematic, the difference is the compensation gain of the MF implemented by the algorithm, and the gray line is the compensation gain calculated by the hearing aid fitting formula according to the spectrum of Fig. 6 (d) for the MF type hearing loss; Figure 6 (h) The black line is shown in Figure 6 (f) and Figure 6 (d) The difference in the spectrum, which is the compensation gain of the algorithm for the MF. The gray line is the compensation gain calculated for the MS type hearing loss according to the spectrum of Fig. 6(d). .
  • the embodiment of the present invention has the following advantages due to the above technical solution: 1. Based on the existing normal hearing and damage auditory loudness feeling model, according to the hearing loss of the ear outer hair cells and inner hair cell damage to the hearing The different characteristics of the injury are compensated accordingly, and the hearing aid fitting formula is obtained based on the hearing damage of the outer ear hair cells and inner hair cells, and the final compensation gain is obtained, so that more accurate and effective compensation can be given for the hearing loss. , solved the existing hearing aid The compensation formula is based on the hearing threshold only when the compensation gain is not accurate enough. 2.
  • the channel processing and the compression amplification process are included, and the process completely simulates the physiological process, so that the input of any sound can be more in the hearing aid device.
  • the ideal compensation target is achieved well, so the compensation gain required by the hearing loss person can be quickly calculated without the existing multi-channel compression amplification algorithm.
  • the present invention can be widely applied to the determination of the hearing compensation gain of a hearing aid device.

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Abstract

La présente invention concerne un procédé de détermination du gain de compensation auditive d'un dispositif de prothèse auditive, comprenant : l'essai de l'ouïe d'une personne ayant une perte d'audition pour déterminer la fréquence CF à une position nécessitant une compensation de gain ; sur la base d'un modèle de perception d'intensité d'ouïe normale et d'ouïe endommagée, le calcul de la valeur de compensation de gain IGohcdB (CF) d'un endommagement de cellule ciliée d'oreille externe ; sur la base du modèle de perception d'intensité, le calcul de la valeur de gain de compensation IGihcdB (CF) d'un endommagement de cellule ciliée d'oreille interne ; l'addition du IGohcdB (CF) et du IGihcdB (CF) pour obtenir le gain de compensation IGdB (CF) de la personne à perte d'audition à la fréquence CF. La présente invention peut être largement utilisée dans les dispositifs d'audition auxiliaires tels que les prothèses auditives et analogues.
PCT/CN2012/080147 2012-03-22 2012-08-15 Procédé de détermination du gain de compensation auditive d'un dispositif de prothèse auditive WO2013139106A1 (fr)

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CN111050261A (zh) * 2019-12-20 2020-04-21 深圳市易优斯科技有限公司 听力补偿方法、装置及计算机可读存储介质

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CN112383870B (zh) * 2020-10-29 2022-03-18 惠州市锦好医疗科技股份有限公司 自适应听力参数验配方法、装置
CN113411733B (zh) * 2021-06-18 2023-04-07 南京工程学院 一种面向免验配助听器的参数自调节方法

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