Hearing aid fitting method and hearing aid

Abstract

This invention provides a hearing aid fitting method and a hearing aid that allow the user to perform self-fitting. [Solution] The hearing aid fitting method initializes signal processing parameters, including gain at different frequencies, of the hearing aid based on the user's attribute data and hearing characteristic data; processes the hearing test signal to be reproduced based on the initialized gain; obtains the processed hearing test signal; reproduces the processed hearing test signal; determines the user's hearing test results after hearing assistance; if the hearing test results indicate that the hearing aid does not meet a preset first hearing assistance requirement, the gain at different frequencies of the hearing aid is adjusted based on the hearing test results; and the hearing test is continuously repeated based on the latest adjusted gain until the hearing aid meets the preset first hearing assistance requirement.

Description

Technical Field

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[0001] This application claims the priority of Chinese Patent Application No. 202411604980.6, filed with the China National Intellectual Property Administration on November 11, 2024, the content of which is incorporated herein by reference in its entirety. The present invention relates to the technical field of hearing aid fitting, and particularly to a hearing aid fitting method and a hearing aid.

Background Art

[0002] A hearing aid is mainly an auditory assistive device that helps improve the hearing ability of people with hearing impairments, enabling them to hear and understand sounds better. Usually, it is necessary to perform hearing aid fitting before the user wears the hearing aid, so that the hearing aid can achieve a satisfactory effect for the user.

[0003] Currently, hearing aid fitting usually requires the user to go to a professional fitting center and be carried out with the assistance of a professional fitting technician and dedicated equipment, and the fitting process is relatively complicated. Therefore, some self-fitting methods by the user himself / herself have been proposed. However, at present, the effect of the self-fitting method by the user himself / herself still cannot match the effect of precise adjustment by the fitting technician.

Summary of the Invention

[0004] The present invention provides a hearing aid fitting method and a hearing aid.

[0005] According to a first aspect, the present invention provides a hearing aid fitting method. The method includes: Initializing signal processing parameters at different frequencies of the hearing aid based on the user's attribute data and hearing characteristic data, the signal processing parameters including gain; The steps include processing the hearing test signal to be reproduced based on the gain after initialization, obtaining the processed hearing test signal, and using the hearing test signal to test the hearing level after the user has fitted a hearing aid, The steps include: playing back the processed hearing test signal and determining the user's hearing test results after hearing aids; If the hearing test results indicate that the hearing aid does not meet the first hearing requirement, the steps include adjusting the gain of the hearing aid at different frequencies based on the hearing test results, and continuously repeating the hearing test based on the latest adjusted gain until the hearing aid meets the preset first hearing requirement; Includes.

[0006] According to a second aspect, the present invention provides a hearing aid comprising a Bluetooth module, a processor, and a speaker.

[0007] The processor is connected to a Bluetooth module and a speaker. The Bluetooth module is configured to receive hearing test signals of different frequencies and transmit the received hearing test signals to the processor. The processor performs one of the steps described above, adjusting the gain of the hearing aid at different frequencies, processing the hearing test signals based on the adjusted gain, transmitting the processed hearing test signals to the speaker, and the speaker playing the processed hearing test signals. [Brief explanation of the drawing]

[0008] To more clearly illustrate the technical solutions in embodiments of the present invention or related technologies, the drawings that may be used in describing embodiments of the present invention or related technologies are briefly described below. Obviously, the drawings in the following description are only a few embodiments of the present invention, and those skilled in the art can obtain other relevant drawings based on these drawings without any creative effort.

[0009] [Figure 1] This is an application environment diagram of a hearing aid fitting method in one embodiment. [Figure 2] This is a flowchart of a hearing aid fitting method in one embodiment. [Figure 3] This is a flowchart of a hearing aid fitting method in another embodiment. [Figure 4] This is a schematic diagram showing the initial gain and maximum output power at different frequencies obtained in one embodiment. [Figure 5] This is a flowchart of a hearing aid fitting method in another embodiment. [Figure 6] This is a detailed flowchart of the hearing aid fitting method in one embodiment. [Figure 7] This is a schematic diagram of a language spectrogram in one embodiment. [Figure 8] This is a detailed flowchart of the hearing aid fitting method in another embodiment. [Figure 9] This is a structural block diagram of a hearing aid fitting device in one embodiment. [Figure 10] This is a structural block diagram of a hearing aid fitting device in another embodiment. [Figure 11] This is a diagram showing the internal structure of a computer device in one embodiment. [Modes for carrying out the invention]

[0010] To further clarify the object, technical means, and advantages of the present invention, the invention will be described in more detail below with reference to the drawings and examples. It should be understood that the specific embodiments described herein are for illustrative purposes only and do not limit the invention.

[0011] The self-fitting method for hearing aids provided in the embodiment of the present invention can be applied to the application environment shown in Figure 1. Here, terminal 102 communicates wirelessly with hearing aid 104 using Bluetooth or other communication methods such as Wi-Fi.

[0012] Specifically, a hearing aid self-fitting application may be installed on terminal 102, and the user may log in to the application and start the self-fitting operation. First, terminal 102 receives attribute data entered by the user, such as gender, age, and hearing characteristic data, and transmits the user attribute data and hearing characteristic data to the hearing aid. The hearing aid 104 then determines the signal processing parameters (including gain) at different frequencies, and subsequently initializes the signal processing parameters (including gain) at different frequencies. Next, the hearing aid 104 processes the hearing test signal to be reproduced based on the initial gain, then reproduces the processed hearing test signal (e.g., pure tone signals or vibrato signals of different frequencies), guides the user to perform a self-hearing test, evaluates the user's hearing level at different frequency points, determines the user's hearing test results after hearing assistance, and if the hearing test results indicate that the hearing aid does not meet a preset first hearing assistance requirement, adjusts the hearing aid's gain at different frequencies based on the hearing test results, continues processing the hearing test signal to be reproduced based on the latest adjusted gain, and continuously repeats the user hearing test until the hearing aid meets the preset first hearing assistance requirement, i.e., determines the optimal gain of the hearing aid at different frequency points.

[0013] Here, terminal 102 may be, but is not limited to, various personal computers, laptop computers, smartphones, tablet computers, Internet of Things devices, and portable wearable devices. Internet of Things devices may include smart speakers, smart TVs, smart air conditioners, smart in-car devices, projection devices, etc. Portable wearable devices may include smartwatches, smart bracelets, head-mounted devices, etc. Head-mounted devices may include virtual reality (VR) devices, augmented reality (AR) devices, smart glasses, etc.

[0014] In an exemplary embodiment, as shown in FIG. 2, a method for self-fitting a hearing aid is provided, and this method will be described by taking its application to the hearing aid 104 in FIG. 1 as an example. As can be understood, this method may also be applied to a user terminal or a server, or a system including a user terminal, a server, and a hearing aid. Specifically, this method includes the following steps S200 to S600.

[0015] S200: Based on the user's attribute data and hearing characteristic data, initialize the signal processing parameters at different frequencies of the hearing aid, and the signal processing parameters include gain.

[0016] The user's attribute data includes, but is not limited to, age, gender, and disease status such as whether suffering from a disease. The hearing characteristic data includes, but is not limited to, wearing experience, discomfort thresholds at different frequencies, and an audiogram within a predetermined period, for example, nearly half a year. The audiogram includes hearing data at 250 Hz (hertz) - 500 Hz - 1 kHz - 2 kHz - 3 kHz - 4 kHz - 8 kHz. Specifically, the user attribute data may be obtained by questionnaire or by interacting with the user through system question and answer. Note that through the questionnaire method, the degree of hearing loss and the cause of hearing loss of the user can be grasped, and it can be determined whether the user suffers from hearing loss due to diseases that require medical treatment such as auricle occlusion, otitis media, and sudden deafness, so that the initial gain can be determined subsequently.

[0017] The signal processing parameters refer to various parameters for processing audio signals inside the hearing aid, and include parameters such as gain, maximum output power, compression ratio, and noise suppression, but are not limited thereto. Gain is used to represent the amplification degree of the hearing aid for audio signals at different frequencies. In this embodiment, the initialized signal processing parameters at different frequencies may include gains at 250 Hz, 500 Hz, 750 Hz, 1 kHz, 1.5 kHz, 2 kHz, 3 kHz, 4 kHz, 6 kHz, and 8 kHz.

[0018] In practical applications, hearing aids may be communicatively connected to a user terminal, such as a smartphone. The user can input basic attribute data such as gender, age, and medical condition into the user terminal's operating interface, and provide information such as the degree of hearing loss and hearing characteristic data for the past six months. The user terminal then transmits the user's attribute data and hearing characteristic data to the hearing aid, and the hearing aid's data processing module uses standard gain calculation formulas (e.g., NAL-NL2 (National Acoustic Laboratories-Non-Linear 2, nonlinear gain formula), DSL (Desired Sensation)). The system processes user-entered attribute data and auditory feature data (such as Level, desired auditory level) and automatically calculates the initial gain of the hearing aid at different frequencies. For example, based on user-entered attribute data and auditory feature data, the initial gains of G50 (low volume), G65 (medium volume), and G80 (high volume) can be determined. To understand that if it is difficult for a user to provide an audiogram for nearly six months, the hearing aid can perform an on-the-spot hearing test on the user to obtain their audiogram. Specifically, the industry standard gold standard audiometry test, the Hughson-Westlake method, can be used to perform the hearing test on the spot. During the InSightle audiometry process, the hearing aid needs to be calibrated to output accurate frequencies and sound pressure (loudness). This ensures consistency and accuracy of the test, allowing audiologists and audiology specialists to provide the user with the optimal hearing aid adjustment and fitting.

[0019] In some other embodiments, the user can adjust and set the initial gain of the hearing aid at different frequencies in the application program interface, and the hearing aid can initialize the gain at different frequencies. The user terminal may process the attribute data and hearing feature data entered by the user based on a standard fitting formula to determine the initial gain of the hearing aid at different frequencies, and then transmit the determined initial gain to the hearing aid, which will then initialize the gain at different frequencies.

[0020] S400: Based on the gain after initialization, process the hearing test signal to be played and obtain the processed hearing test signal.

[0021] The hearing test signal usually includes a series of standard audio signals, and is used to evaluate the hearing threshold and auditory comprehension ability at different frequencies after the user wears the hearing aid, that is, to test the hearing level after the user wears the hearing aid. Specifically, the hearing test signal includes, but is not limited to, pure tone signals, tremolo signals, language test signals, noise signals, etc. Here, a pure tone signal is a signal with a single frequency, and is usually used to measure the hearing threshold of the user at different frequencies. The language test signal includes the voices of actual languages such as single-syllable words and two-syllable words, and is used to evaluate the language recognition ability of the user at different frequencies.

[0022] When specifically implemented, after the hearing aid initializes the gain, the hearing aid can process the hearing test signal to be played based on the gain after initialization and obtain the processed hearing test signal. For example, when the gain of the initialized hearing aid is 20 dB, the hearing test signal is a pure tone signal, the frequency is 1 kHz, and the initial intensity is 60 dB SPL (sound pressure level). Process the pure tone signal based on the initialized gain, that is, increase the original signal intensity of 60 dB SPL to 80 dB SPL, and obtain a pure tone signal with a processed signal intensity of 80 dB SPL.

[0023] Step S600: Play the processed hearing test signal and determine the hearing test result after the user's hearing aid.

[0024] In this embodiment, the hearing test result includes the hearing threshold and language recognition rate of the user at different frequencies, etc.

[0025] In practice, the user can perform the hearing test in a relatively quiet location with low background noise. The hearing aid has pre-stored hearing test signals to be reproduced. After the hearing aid initializes the gain, it operates based on the initialized gain, processes the hearing test signal to be reproduced, and then plays back the gain-processed hearing test signal. The user responds to the heard hearing test signal, for example, by clicking a button on the user terminal screen or by giving a verbal response. The user's response to each hearing test signal is then recorded, and the user's hearing threshold and speech recognition rate at different frequencies are evaluated and determined to obtain the hearing test results. Exemplarily, a sound field test is performed on the user using a pure tone signal, and feedback is provided on whether the user heard the speech and its clarity. The user's hearing test results after receiving the hearing aid are then obtained based on the data provided by the user.

[0026] S800: If the hearing test results indicate that the hearing aid does not meet the preset first hearing requirement, the hearing aid's gain at different frequencies is adjusted based on the hearing test results, and the hearing test is continuously repeated based on the latest adjusted gain until the hearing aid meets the preset first hearing requirement.

[0027] In this embodiment, the first hearing requirement refers to an objective hearing requirement, that is, a requirement to evaluate the hearing effect of a hearing aid based on the results of a hearing test and relevant parameters of the hearing aid using scientific methods and technical means. For example, the first hearing requirement includes, but is not limited to, that the user's speech recognition rate at different frequencies is higher than a preset speech recognition rate threshold (e.g., 85%), and / or that the user's hearing threshold at different frequencies is close to a desired threshold (e.g., 30 dB (decibels)).

[0028] In practice, if the results of the initial hearing test, performed based on the initialized gain, indicate that the hearing aid does not meet the first hearing requirement, i.e., if the user's speech recognition rate or hearing threshold at a certain frequency does not meet the first hearing requirement, the hearing aid's gain at different frequencies is continuously adjusted. Finally, the same hearing test signal is processed based on the adjusted gain, the processed hearing test signal is played back, the user's hearing test results are recorded, and the hearing aid is re-evaluated to determine whether it has met the first hearing requirement. If it has not, the hearing aid's gain is adjusted again, and the user is given another hearing test based on the latest adjusted gain. In this way, hearing tests are continuously repeated until the hearing aid meets the first hearing requirement. For example, if a user has low speech recognition in the high-frequency range, the gain in these frequency ranges can be increased. Then, the same hearing test signal is processed with the increased gain, and the processed hearing test signal is played back to test the hearing level after the user wears the hearing aid. In this way, the hearing test is repeated until the hearing aid reaches the first hearing requirement. Furthermore, to ensure overall auditory balance, after adjusting the hearing aid gain at one frequency point, the hearing aid gain at other frequency points is adaptively adjusted. For example, if, after increasing the gain at 2000 Hz, the user finds that sounds between 1000 Hz and 3000 Hz sound unbalanced or excessively sharp, these frequencies also need to be fine-tuned to restore the natural balance of hearing.

[0029] The above hearing aid fitting method differs from the hearing aid fitting method performed by a professional fitting technician, and instead provides a method to support self-fitting of hearing aids by the user. First, based on the user's attribute data and hearing characteristic data, the signal processing parameters of the hearing aid at different frequencies are initialized. Then, the hearing test signal after gain processing based on the initialization is played back, the hearing level after the user puts on the hearing aid is tested, and the user's hearing test results after hearing are obtained. Subsequently, based on the hearing test results, the gain of the hearing aid at different frequencies is iteratively adjusted. After adjusting the gain each time, the hearing level after the user puts on the hearing aid is tested again to find the optimal gain setting for the user, so that the hearing aid meets the pre-set hearing requirements. The above method combines automated hearing tests and a user feedback mechanism, repeatedly performing hearing tests on the user and iteratively adjusting the gain of the hearing aid at different frequencies based on the hearing test results. This allows the user to quickly and accurately determine the optimal gain at each frequency point of the hearing aid according to their own hearing experience and usage habits, enabling the hearing aid to achieve a better hearing effect. Furthermore, throughout the entire process, users do not need to visit a specialized fitting facility; hearing aid fitting can be done at home, making it more convenient.

[0030] In actual applications, during the initialization phase of a hearing aid, the signal processing parameters that need to be initialized may include parameters such as maximum output power in addition to gain. As shown in Figure 3, in one exemplary embodiment, S200 includes the following S220.

[0031] S220: Based on user attribute data, discomfort thresholds at different frequencies, and audiogram, determine the gain of the hearing aid at different frequencies and initialize the gain and maximum output power of the hearing aid at different frequencies.

[0032] The Uncomfortable Loudness Level (UCL) refers to the minimum sound pressure level at a particular frequency at which a sound is perceived as excessively loud and begins to cause discomfort. This threshold varies from person to person, and even patients with the same degree of hearing loss may have significantly different UCLs. Therefore, it is necessary to determine the UCL for each user at different frequencies. Specifically, the application program on the user terminal plays gradually increasing sounds at different frequency points and guides the user to provide feedback on whether they can tolerate the sound or not through buttons, gestures, or other means. When the user provides feedback that they cannot tolerate the sound, the threshold at that point is set as the UCL for that frequency point. Maximum Power Output (MPO) refers to the maximum sound pressure level that a hearing aid can output with a specific input signal.

[0033] In the specific implementation, user attribute data (e.g., age, gender, etc.) and hearing characteristic data (discomfort thresholds and audiograms at different frequencies) are acquired. The user attribute data and hearing characteristic data are then used as input to a standard fitting formula, such as the NAL-NL2 formula. The NAL-NL2 formula is used to obtain a mapping relationship from the input (audiogram + user age + gender + disease status) to the output (initial gain) at different frequencies. Subsequently, the maximum output power at different frequencies can be determined based on the user's discomfort thresholds at different frequencies. Illustratively, Figure 4 shows the initial gains of the hearing aid at different frequencies obtained by the NAL-NL2 formula. The user terminal can then transmit the obtained initial gains and maximum output power to the hearing aid, and the hearing aid initializes its initial gains and maximum output power at different frequencies based on the received initial gains at different frequencies.

[0034] In this embodiment, a clinically compiled fitting prescription formula is combined based on user attribute data, discomfort thresholds at different frequencies, and an audiogram to obtain a more accurate initial gain suited to the user, thereby enabling the hearing aid to achieve better hearing assistance.

[0035] In some exemplary embodiments, initializing the maximum output power of a hearing aid at different frequencies includes determining the maximum output power at different frequencies based on the discomfort threshold at those frequencies and then initializing the maximum output power at those frequencies.

[0036] In practical applications, the actual output of a hearing aid can be affected by ambient noise, input sound pressure level, and the characteristics of the hearing aid itself; therefore, the maximum output power (MPO) of the hearing aid needs to be set according to the user's discomfort threshold.

[0037] Specifically, the gain calculated by the NAL-NL2 formula may be initialized to ensure that the output at different frequencies does not exceed the user's comfort range. This may involve setting the maximum output power to a safe range that does not exceed the user's discomfort threshold. In this embodiment, the maximum output power at each frequency point should be close to the discomfort threshold but not exceed it, in order to ensure maximum audibility without causing hearing damage to the user. The maximum output power at different frequencies may be set accordingly. For example, if the user's discomfort threshold at 750 Hz is 100 dB, the maximum output power at 750 Hz can be set to 98 dB. In actual applications, a corresponding fixed difference may be set, and the maximum output power at the corresponding frequency may be determined based on the discomfort threshold at that frequency. For example, if the fixed difference is set to 5 dB and the user's discomfort threshold at 750 Hz is 100 dB, the maximum output power at 750 Hz can be set to 95 dB.

[0038] In this embodiment, user comfort is improved and hearing aid settings are personalized by determining the maximum output power at different frequencies based on the discomfort threshold at those frequencies.

[0039] In an exemplary embodiment, as shown in Figure 5, S400 includes the following S420. S420: Based on the gain after initialization, the pure tone signal or vibrato signal to be reproduced is processed, and the processed pure tone signal or vibrato signal is obtained.

[0040] S600 includes S620 as described below. S620: The processed pure tone signal or vibrato signal is reproduced to confirm the user's post-hearing sound field test results.

[0041] The S800 includes the S820 described below. S820: If the sound field test results indicate that the hearing aid does not meet the preset first hearing requirement, the gain of the hearing aid at different frequencies is adjusted based on the sound field test results, and the sound field test is continuously repeated based on the latest adjusted gain until the hearing aid meets the preset first hearing requirement.

[0042] In this embodiment, the hearing test signal includes a pure tone signal or a vibrato signal. The pure tone signal or vibrato signal is used to perform a sound field test on the user. The hearing test results include the sound field test results. Here, a vibrato signal is a sound signal whose frequency changes over time. Unlike a pure tone signal, the frequency of a vibrato signal is not constant but fluctuates within a certain range, and the change in frequency makes the signal closer to the changes in natural language speech, thus closer to the auditory experience in real life. A sound field test is a test method for evaluating a subject's hearing using a sound source device such as a speaker in a controlled acoustic environment. The sound field test results include data such as the user's hearing threshold (minimum audible threshold) at different frequencies.

[0043] In practice, the hearing threshold test (sound field test) performed on the user may be conducted using a pure tone signal or a vibrato signal. After initializing the hearing aid's gain, the user terminal generates a vibrato signal or a single-frequency pure tone signal within a pre-set frequency range. The hearing aid processes the pure tone signal or vibrato signal based on the initialized gain, adjusts the signal intensity to allow the user to hear appropriate sounds, and then plays back the processed pure tone signal or vibrato signal.

[0044] As an example, using the reproduction of a vibration signal, first, an audio signal is reproduced from 1kHz to 40dB, gradually increasing to 2kHz, 4kHz, and 8kHz, and then the hearing threshold at 1kHz is remeasured. The user is then guided to report whether or not they could hear the signal using buttons, gestures, voice, or other methods. For children, feedback can be obtained through games or other interactive methods. The user's hearing response at each frequency is recorded to evaluate their hearing threshold. Furthermore, subjective perceptions of the user can be inquired about to understand their experience regarding sound volume, clarity, etc., in order to obtain more accurate sound field test results. Let X1 be the initially measured hearing threshold at 1kHz, and X5 be the remeasured hearing threshold at 1kHz. If the absolute difference between X1 and X5 is 10 or less, the previously measured results are considered reliable; otherwise, remeasurement is necessary.

[0045] As an example, taking the reproduction of a pure tone signal as an example, determine the frequency points that need to be tested and test them sequentially from low frequencies to high frequencies. For example, gradually increase the frequency from a certain low sound intensity level until the user can hear the audio signal. Guide the user to report whether or not they could hear the signal using buttons, gestures, voice, or other methods, record the user's hearing threshold at each frequency point, plot the hearing thresholds at different frequencies on an audiogram, and obtain a hearing threshold curve.

[0046] After obtaining the user's hearing thresholds at different frequencies based on a pure tone signal or vibration signal, if it is determined that the user's gain is insufficient or excessive at a certain frequency, the hearing aid gain is adjusted based on the sound field test results. Then, based on the adjusted gain, the sound field test is repeated until the gain settings at all important frequency points meet the user's hearing needs and the hearing aid satisfies a preset first hearing requirement.

[0047] In this embodiment, by performing a sound field test using a pure tone signal or a vibration signal and repeatedly adjusting the gain, the hearing condition of the user after wearing the hearing aid can be accurately evaluated, and the settings of the hearing aid can be adjusted based on the test results to achieve the optimal hearing compensation effect.

[0048] As shown in Figure 6, in the exemplary embodiment, S820 includes the following S822. S822: If the sound field test results indicate that the hearing aid does not meet the preset first hearing requirement, the desired intensity values ​​of the language test signal at different frequencies are determined based on the preset language spectrogram, the desired intensity values ​​are compared with the hearing thresholds at different frequencies to determine the desired gain of the hearing aid at different frequencies, the gain of the hearing aid at different frequencies is adjusted based on the desired gain at different frequencies, and the hearing test is continuously repeated based on the latest adjusted gain until the hearing aid meets the preset first hearing requirement.

[0049] The hearing threshold, also known as the auditory threshold, refers to the minimum sound intensity at which a user can hear and recognize. The hearing threshold is expressed in decibels (dB HL, hearing level) on an audiogram. For people with normal hearing, the hearing threshold is typically between 0 and 20 dB HL, while individuals with hearing loss may have a much higher hearing threshold without hearing aids.

[0050] A speech spectrogram, also known as a speech banana diagram, is a diagram that shows the frequency and intensity distribution range of speech sounds measured using a sound level meter when multiple people speak at normal volume (Figure 7). It represents the frequency and intensity distribution range of speech sounds in people with normal hearing and is an important indicator for evaluating auditory communication ability in daily life. A sound intensity level of 20-40 dB SPL is comfortable for most users and allows them to hear and understand words as much as possible in everyday conversational environments; therefore, in this embodiment, the desired sound intensity range is set to 20-40 dB.

[0051] In practical applications, after obtaining sound field test results, the effectiveness of hearing aids can be evaluated in combination with speech banana diagrams. Specifically, if all frequency points within the hearing range amplified by the hearing aid fall within the banana diagram, it indicates that the hearing aid is effective and that the user can hear speech sounds essentially the same as a person with normal hearing. When implementing this, the goal is to adjust the hearing aid's gain settings so that the user's hearing threshold (the minimum volume at which a sound can be barely heard) approaches 20 dBHL as closely as possible in each frequency band included in the speech banana diagram.

[0052] For example, after measuring the user's hearing threshold at different frequencies, a comparison is made to see if the threshold at each frequency is close to 20 dB. If not, the difference between the hearing threshold at each frequency and the desired intensity is determined. Based on this intensity difference, the desired gain of the hearing aid at each frequency is determined, and then the gain of the hearing aid at each frequency is adjusted based on the desired gain at each frequency. For example, if the user's hearing threshold at 500 Hz is 45 dBHL, the difference between that and the desired intensity of 20 dB is 25 dB, so the current gain of the hearing aid is increased by 25 dB from the original gain. Note that adjusting the hearing aid gain is generally incremental, and multiple fine-tuning adjustments are necessary to find the optimal setting for the user.

[0053] In this embodiment, by combining the language spectrogram with the desired intensity and further determining the gain adjustment range of the hearing aid at different frequencies, it is possible to find the optimal gain at different frequencies and achieve the optimal hearing aid effect.

[0054] In practical applications, in addition to measuring the user's hearing threshold, it is also possible to measure the user's speech recognition threshold at different frequencies. As shown in Figure 8, in some exemplary embodiments, after S822, the method further includes the following steps.

[0055] S840: Processes language test signals containing different frequencies based on the latest adjusted gain.

[0056] S842: The processed language test signal is played back, a language test is performed on the user, and the results of the user's post-hearing language audiometry test are confirmed.

[0057] S844: If the results of the speech audiometry test indicate that the user's speech recognition rate is lower than the preset desired value, the gain of the hearing aid at different frequencies is adjusted based on the results of the speech audiometry test, and the speech audiometry test is continuously repeated based on the latest adjusted gain until the user's speech recognition rate is equal to or greater than the preset desired value.

[0058] In this embodiment, a sound field test and a language test are performed on the user as an example. The hearing test results include the sound field test results and the language test results, and the hearing test signal includes a pure tone signal or a vibrato signal and a language test signal.

[0059] Language recognition rate refers to a person's ability to accurately recognize language under specific conditions. Language recognition rate is usually expressed as a percentage. For example, if a person correctly recognizes 70 out of 100 words, their language recognition rate is 70%. In this embodiment, the desired language recognition rate may be 85%. In other embodiments, the desired language recognition rate may be other values ​​such as 90% or 80%, and is not specifically limited here. The language listening test results include data such as the user's language recognition rate at different frequencies and language recognition thresholds.

[0060] In practice, the language test for the user may be conducted as follows: 25 single-syllable or two-syllable words (i.e., language test signals) are prepared, covering a general language frequency range. The hearing aid then operates based on the latest adjusted gain, playing the 25 single-syllable or two-syllable words. After each word is played, the user is asked to repeat or select the correct word. The user's response to each word is then recorded as correct or incorrect, and the percentage of words correctly answered by the user relative to the total number of words (i.e., language recognition rate = number of correct answers / total number of words × 100%) is statistically calculated. If the user's language recognition rate at a certain frequency point measured in this round does not reach 85%, the frequency band in which the user's recognition rate is low is analyzed based on the language audiometry results, and the gain of the corresponding frequency band is adjusted. Next, based on the latest adjusted gain, 25 single-syllable or two-syllable words are processed, and the language test with the user is continued to verify whether the new gain setting effectively improved the language recognition rate. The above process is then continued, and the language test is repeated after each gain adjustment until the user's language recognition rate at each frequency point after hearing assistance reaches 85% or higher.

[0061] In this embodiment, individualized gain adjustments are made to each user's specific needs through continuous iterative adjustments and testing, gradually optimizing the hearing aid settings until the optimal hearing state is reached, thereby achieving optimal language comprehension.

[0062] Based on the results of a speech audiometry test, the gain of the hearing aid can be adjusted by analyzing the words that the user answered incorrectly. In an exemplary embodiment, adjusting the gain of the hearing aid at different frequencies based on the results of a speech audiometry test includes extracting the misrecognized words that the user answered incorrectly from the speech audiometry test results, determining the six ring tones of the misrecognized words and the target frequencies corresponding to the six ring tones, and adjusting the gain of the hearing aid at the target frequencies.

[0063] The six ring tones (m, u, a, i, sh, s) cover important frequency components in language. m: Supports low frequencies. u: Supports low frequencies. a: Corresponds to intermediate frequencies. i: Corresponds to intermediate frequencies. sh: Supports high frequencies. s: Supports high frequencies.

[0064] In the above embodiment, each speech audiometry test can record the misrecognized words the user incorrectly answered and the words the user answered correctly. If the user's speech recognition rate is less than 85% of the desired speech recognition rate, the hearing aid gain at the corresponding frequency point is adjusted based on the six ring tones corresponding to the incorrect words. For example, if the user has difficulty recognizing high-frequency words, the gain in the high-frequency band (e.g., 3000Hz and 3500Hz) can be increased. Finally, based on the latest adjusted gain, the speech audiometry test is performed again to check the effect of the adjustment. If the recognition rate still has not reached the desired value (85% or higher), the analysis of incorrect words continues and the hearing aid settings are adjusted until the user's speech recognition rate reaches the desired level. Furthermore, in other embodiments, fine-tuning may be performed based on specific user feedback to obtain a higher recognition rate.

[0065] For example, suppose the user correctly answers 18 words in their first speech audiometry test, resulting in a speech recognition rate of 72%. Analysis of the recorded user errors reveals that the user makes many mistakes with high-frequency words (e.g., "sh," "s"). Therefore, the hearing aid gain is adjusted at 3000Hz and 3500Hz. The hearing aid gain at other frequencies is also adaptively adjusted. Based on the latest adjusted gain, a second speech audiometry test is conducted. If the user correctly answers 22 words in this test, resulting in a speech recognition rate of 88%, the hearing test can be terminated as the desired value of 85% has already been reached or exceeded.

[0066] In this embodiment, by analyzing the six ring tones of words the user incorrectly answers and gradually optimizing the hearing aid's parameter settings, the user's language recognition accuracy at different frequencies can be improved to a high level. This not only enhances the user's auditory experience but also improves their communication skills in daily life.

[0067] In some exemplary embodiments, after adjusting the gain of the hearing aid at the target frequency, the method further includes the following: If the number of gain adjustments reaches the upper limit of adjustments, and the results of the speech audiometry test indicate that the user's speech recognition rate at the target frequency is lower than a preset desired value for speech recognition rate, but the results of the sound field test indicate that the user heard a pure tone signal or vibration signal at the target frequency, then a preset rehabilitation training sample is played and rehabilitation training is performed on the user.

[0068] In actual applications, there are many factors influencing the user's language recognition rate, so to ensure the smooth progress of the test, the maximum number of gain adjustments can be set to 5. In this embodiment, the rehabilitation training samples may include short recordings in different environmental scenes.

[0069] If the speech recognition rate at a certain target frequency still does not reach the desired value of 85%, but the user's speech banana diagram indicates that the user heard a pure tone or vibrato signal at this target frequency, it is determined that the user can hear the speech but cannot understand the meaning of the speech signal. In this case, it is necessary to provide the user with individualized rehabilitation training to enhance the user's language comprehension function. Specifically, a rehabilitation training screen corresponding to the user's terminal is displayed, the hearing aid plays short recordings in different environmental scenes, and the user is guided to complete the hearing rehabilitation training by listening to the recordings, attempting to understand the content of the recordings, and completing keyword fill-in-the-blanks on the user terminal screen. Throughout the entire process, the hearing aid must provide clear audio input to enable comprehension, and stable auditory conditions should be provided at different stages of training, thereby supporting the user in gradually improving their language comprehension ability. In other embodiments, the rehabilitation training may be conducted using other rehabilitation samples, and is not limited thereto.

[0070] In this embodiment, by incorporating rehabilitation training into the self-fitting process of hearing aids, the hearing aids not only enable users to hear sounds, but also allow them to transform from simply "hearing" to "understanding."

[0071] In addition to the method of fitting based on the objective data described above, subjective fitting by the user can also be incorporated. In some exemplary embodiments, after continuously and repeatedly testing the user's hearing level after wearing the hearing aid based on the latest adjusted gain, the method further includes obtaining feedback audiometry data from the user and adjusting the gain of the hearing aid at different frequencies based on the audiometry data until the hearing aid meets a pre-set second hearing requirement.

[0072] In this embodiment, the second hearing requirement refers to a subjective hearing requirement, specifically, during the process of the user actually using the hearing aid, it is determined, in combination with the individual's experience and sensations while wearing the hearing aid, that the hearing aid achieves the user's desired hearing effect, and the hearing satisfaction level of the hearing aid is determined. If the satisfaction level is higher than a preset satisfaction threshold, for example 90%, it is determined that the hearing aid has met the second hearing requirement. To make it easier to understand, in another embodiment, the user is guided to score their satisfaction level with the hearing aid, and if the satisfaction score is higher than a preset score threshold, for example 9 points, it is determined that the hearing aid has met the second hearing requirement. Here, the satisfaction threshold or satisfaction score may be other numerical values ​​and are not limited thereto.

[0073] In practical applications, after determining that the hearing aid meets the objective hearing needs by conducting sound field tests and speech audiometry tests on the user, the user may determine whether the hearing aid achieves the desired hearing effect by fine-tuning the hearing aid's gain based on the user's subjective hearing level. For example, the user terminal may ask the user questions via the user interface of the application program, for instance, whether the user's voice is present while wearing the hearing aid, whether there are echoes or normal sounds, and whether any other unusual sounds were heard in daily life. The user can then provide feedback on their actual hearing experience by voice, by pressing buttons on the hearing aid, or by tapping the hearing aid. The hearing aid records the audiometry test data provided by the user and then, based on the audiometry test data, adjusts the gain of the hearing aid at different frequencies until the user's satisfaction with the hearing aid exceeds a preset satisfaction threshold, thereby completing the self-fitting of the hearing aid.

[0074] In some other embodiments, after obtaining hearing test data from the user, the hearing aid's gain at different frequencies can be adjusted based on the hearing test data and known user hearing characteristic data (e.g., wearing experience and discomfort thresholds at different frequencies) until the user's satisfaction with the hearing aid exceeds a preset satisfaction threshold, thereby completing the hearing aid's self-fitting.

[0075] For example, fine-tuning the hearing aid gain based on the user's wearing experience and acceptance may be done as follows: For a user receiving their first fitting, after determining the target gain, the hearing aid may be given 80% of the target gain in the first month, 90% in the second month, and then 100% to allow the user to adapt better. Alternatively, for example, during the self-fitting process, if the user provides feedback that they cannot hear the sound of air conditioning, the hearing aid may determine that the G50 low-volume gain is too low and gradually increase the G50 all-frequency gain in a preset adjustment step size, e.g., 2 dB, until the user achieves a comfortable hearing experience. If the user provides feedback that their own voice sounds too loud, the G80 high-volume gain may be determined to be too high and gradually decrease the G80 all-frequency gain in a preset adjustment step size of 2 dB until the user achieves a comfortable hearing experience.

[0076] In this embodiment, by combining objective and subjective adjustments, a more comprehensive evaluation can be performed, enabling the hearing aid to achieve better hearing assistance. Furthermore, it allows users to make personalized adjustments according to their individual needs and actual circumstances, resulting in the hearing aid being a better fit to the user's actual needs.

[0077] To more clearly illustrate the hearing aid fitting method provided in the embodiments of the present invention, the following examples will be provided. The following examples include the following steps.

[0078] S100: Determine the hearing aid's gain at different frequencies based on user attribute data, discomfort thresholds at different frequencies, and audiogram.

[0079] S102: Determine the maximum output power of the hearing aid at different frequencies based on the discomfort threshold at different frequencies.

[0080] S104: Initialize the hearing aid's initial gain and maximum output power at different frequencies.

[0081] S106: Based on the gain after initialization, the pure tone signal or vibrato signal to be reproduced is processed, the processed pure tone signal or vibrato signal is reproduced, a sound field test is performed for the user, and the sound field test results after the user's hearing are finalized.

[0082] S108: If the sound field test results indicate that the hearing aid does not meet the pre-set objective hearing requirements, the desired intensity values ​​of the language test signal at different frequencies are determined based on a pre-set language spectrogram, and the desired intensity values ​​are compared with the hearing thresholds at different frequencies to determine the desired gain of the hearing aid at different frequencies.

[0083] S110: Based on the desired gain at different frequencies, the hearing aid's gain at each frequency is adjusted, and the sound field test is continuously repeated based on the latest adjusted gain until the user's hearing threshold at each frequency approaches the desired threshold.

[0084] S112: Based on the latest adjusted gain, the system processes language test signals containing different frequencies, plays back the processed language test signals, and confirms the user's post-hearing language audiometry results.

[0085] S114: If the results of the speech audiometry test indicate that the user's speech recognition rate is lower than the preset desired value, the misrecognized words that the user incorrectly answered are extracted from the speech audiometry test results, the six ring tones of the misrecognized words and the target frequencies corresponding to the six ring tones are determined, the gain of the hearing aid at the target frequencies is adjusted, and the speech audiometry test is continuously repeated based on the latest adjusted gain until the user's speech recognition rate is equal to or greater than the preset desired value.

[0086] In this process, if, during the speech audiometry test, the user's speech recognition rate at a target frequency still does not reach the desired value of 85% even after five gain adjustments, but the user's speech banana diagram indicates that the user can hear pure tone or vibrato signals at this target frequency, it is determined that the user needs personalized rehabilitation training. Specifically, a rehabilitation training screen corresponding to the user's terminal is displayed, the hearing aid plays short recordings in different environmental scenes, and after listening to the recordings, the user is guided to complete the hearing rehabilitation training by attempting to understand the content of the recordings and filling in the blanks with keywords on the user terminal screen.

[0087] S116: Acquire hearing test data provided by the user and adjust the gain of the hearing aid at different frequencies based on the hearing test data and hearing characteristic data until the pre-set subjective hearing assistance needs are met.

[0088] It should be noted that while the steps in the flowcharts for each of the above embodiments are shown sequentially according to the arrows, these steps are not necessarily executed sequentially in the order indicated by the arrows. Unless otherwise explicitly stated herein, the execution of these steps is not limited to a strict order, and they may be executed in other orders. Furthermore, at least some of the steps in the flowcharts for each of the above embodiments may include multiple steps or stages, and these steps or stages do not necessarily need to be completed at the same time; they may be executed at different times. The execution order of these steps or stages also does not necessarily need to be sequential; they may be executed sequentially or alternately with other steps or at least some of the steps or stages in other steps.

[0089] Based on a similar inventive concept, embodiments of the present invention further provide a hearing aid fitting device for realizing the above-described hearing aid fitting method. Since the technical means for solving the problems provided by this device are similar to the means for realizing the method described above, specific limitations in the embodiments of one or more hearing aid fitting devices provided below can refer to the limitations for the above-described hearing aid fitting method, and are therefore omitted here.

[0090] In an exemplary embodiment, as shown in Figure 9, a hearing aid fitting device 900 is provided, which includes an initialization module 910, a signal processing module 920, a hearing test module 930, and a parameter adjustment module 940.

[0091] The initialization module 910 initializes signal processing parameters, including the gain of the hearing aid at different frequencies, based on the user's attribute data and hearing characteristic data.

[0092] The signal processing module 920 processes the hearing test signal to be reproduced based on the initialized gain, and obtains a processed hearing test signal. This hearing test signal is used to test the hearing level of the user after they have fitted a hearing aid.

[0093] The hearing test module 930 plays back the processed hearing test signal and determines the user's hearing test result after receiving hearing aids.

[0094] The parameter adjustment module 940 is used to adjust the gain of the hearing aid at different frequencies based on the hearing test results if the hearing test results indicate that the hearing aid does not meet the preset first hearing requirement, and to continuously repeat the hearing test based on the latest adjusted gain until the hearing aid meets the preset first hearing requirement.

[0095] In the exemplary embodiment, the hearing test module 930 is further used to process the pure tone signal or vibration signal to be reproduced based on the initialized gain, to obtain the processed pure tone signal or vibration signal, to reproduce the processed pure tone signal or vibration signal, and to determine the user's post-hearing sound field test results, and the pure tone signal or vibration signal is used for the user's sound field test.

[0096] In an exemplary embodiment, the parameter adjustment module 940 is further used to determine desired intensity values ​​of language test signals at different frequencies based on a preset language spectrogram, compare the desired intensity values ​​with hearing thresholds at different frequencies, determine the desired gain of the hearing aid at different frequencies, and adjust the gain of the hearing aid at different frequencies based on the desired gain at different frequencies.

[0097] In an exemplary embodiment, the hearing test module 930 is also used to process language test signals containing different frequencies based on the latest adjusted gain to obtain a processed language test signal. The language test signal is used to perform a language audiometry test on the user. The processed language test signal is played back to confirm the user's post-hearing language audiometry test results. If the language audiometry test results indicate that the user's language recognition rate is lower than a desired value, the gain of the hearing aid at different frequencies is adjusted based on the language audiometry test results, and the language test is repeatedly performed based on the latest adjusted gain until the user's language recognition rate is equal to or greater than a preset desired value.

[0098] In an exemplary embodiment, the parameter adjustment module 940 is further used to extract misrecognized words that the user incorrectly answered from the speech audiometry results, determine the Linsen 6 tones of the misrecognized words and the target frequencies corresponding to the Linsen 6 tones, and adjust the gain of the hearing aid at the target frequencies.

[0099] In an exemplary embodiment, the hearing feature data includes discomfort thresholds at different frequencies and audiograms within a preset period. The initialization module 910 is also used to determine the gain of the hearing aid at different frequencies and to initialize the hearing aid's gain and maximum output power at different frequencies, based on the attribute data, discomfort thresholds at different frequencies, and audiograms.

[0100] In an exemplary embodiment, the initialization module 910 further determines the maximum output power at different frequencies based on the discomfort threshold at each frequency and initializes the maximum output power at each frequency.

[0101] As shown in Figure 10, in an exemplary embodiment, the apparatus further includes a rehabilitation training module 950. The rehabilitation training module 950 is used to perform rehabilitation training on a user by playing a preset rehabilitation training sample when the number of gain adjustments reaches the upper limit of the number of adjustments, the speech listening test results indicate that the user's speech recognition rate at the target frequency is lower than a preset desired value for speech recognition rate, but the sound field test results indicate that the user was able to hear a pure tone signal or vibrato signal at the target frequency.

[0102] As shown in Figure 10, in an exemplary embodiment, the device further includes a subjective adjustment module 960. The subjective adjustment module 960 is used to acquire hearing test data fed back from the user and to adjust the gain of the hearing aid at different frequencies based on the hearing test data until a preset second hearing assistance request is met.

[0103] In an exemplary embodiment, the subjective adjustment module 960 is also used to acquire hearing test data fed back from the user and to adjust the gain of the hearing aid at different frequencies based on the hearing test data and hearing characteristic data until a preset second hearing assistance request is met.

[0104] All or part of each module in the hearing aid fitting device described above can be implemented by software, hardware, or a combination thereof. Each of the above modules may be embedded in a processor in a computer device in hardware form, or it may be independent of the processor in a computer device, or it may be stored in the memory of a computer device in software form so that the processor can call and execute the operations corresponding to each of the above modules.

[0105] In an exemplary embodiment, a hearing aid is provided that includes a Bluetooth module, a processor, and a speaker. The processor is connected to the Bluetooth module and the speaker.

[0106] The Bluetooth module is used to receive hearing test signals of different frequencies and transmit the received hearing test signals to a processor. The processor is used to perform the steps in any of the above embodiments of the hearing aid fitting method, adjust the gain of the hearing aid at different frequencies, process the hearing test signals based on the adjusted gain, and transmit the processed hearing test signals to a speaker. The speaker plays the processed hearing test signals.

[0107] Specifically, the hearing aid connects to an external Bluetooth test device, such as a smartphone, via a Bluetooth module. The Bluetooth module receives a hearing test signal transmitted from the smartphone, sends the received hearing test signal to a processor, which processes the hearing test signal and adjusts the gain of the hearing aid at different frequencies until the hearing aid meets a preset hearing requirement.

[0108] The components included in the hearing aids listed above are merely components related to the technical means of the present invention and do not limit the hearing aids to which the technical means of the present invention are applied. In addition to the components listed above, power modules, microphones, other components, etc., may be further included.

[0109] In an exemplary embodiment, a computer device is provided. This computer device may be a server. Its internal structure is shown in Figure 11. The computer device includes a processor, memory, an input / output interface (I / O), and a communication interface. The processor, memory, and input / output interface are connected via a system bus, and the communication interface is connected to the system bus via the input / output interface. The processor of the computer device is configured to provide computing and control capabilities. The memory of the computer device includes a non-volatile storage medium and internal memory. This non-volatile storage medium stores the operating system, computer programs, and a database. The internal memory provides an environment for the execution of the operating system and computer programs on the non-volatile storage medium. The database of the computer device is used to store user attribute data, hearing characteristics, and hearing test data, etc. The input / output interface of the computer device is used to exchange information between the processor and external devices. The communication interface of the computer device is used to communicate with external terminals via a network. When the computer program is executed by the processor, a hearing aid fitting method is realized.

[0110] As those skilled in the art will understand, the structure shown in Figure 11 is merely a block diagram of some structures related to the technical means of the present invention and does not limit the computer equipment to which the technical means of the present invention is applied. Specific computer equipment may include more or fewer components than those shown in the figure, or may be a combination of some components, or may have a different arrangement of components.

[0111] In an exemplary embodiment, a computer device including memory and a processor is provided. When a computer program is stored in the memory and the processor executes the computer program, the steps in any one of the above embodiments of the hearing aid fitting method are realized.

[0112] In an exemplary embodiment, a computer-readable storage medium is provided in which a computer program is stored. When the computer program is executed by the processor, the steps in any one of the above embodiments of the hearing aid fitting method are realized.

[0113] In one embodiment, a computer program product including a computer program is provided, and when this computer program is executed by a processor, the steps in any one of the above embodiments of the hearing aid fitting method are realized.

[0114] Furthermore, the user information (including, but not limited to, user device information and user personal information) and data (including, but not limited to, data for analysis, stored data, and displayed data) according to the present invention are all information and data approved by the user or fully approved by each party, and the collection, use, and processing of the relevant data comply with the relevant regulations.

[0115] As those skilled in the art will understand, all or part of the flow in the methods of the above embodiments can be implemented by directing the relevant hardware with a computer program. The computer program may be stored in a non-volatile computer-readable storage medium. When the computer program is executed, it may include the flow of each embodiment of the above methods. Any memory, database, or other medium used in the embodiments provided by the present invention may include at least one of non-volatile memory and volatile memory. Non-volatile memory may include read-only memory (ROM), magnetic tape, floppy disk, flash memory, optical memory, high-density embedded non-volatile memory, resistive random access memory (ReRAM), magnetoresistive random access memory (MRAM), ferroelectric random access memory (FRAM), phase change memory (PCM), graphene memory, etc. Volatile memory may include random access memory (RAM) or external cache memory, etc. RAM may be in various forms, such as static random access memory (SRAM) or dynamic random access memory (DRAM), but is not limited to these. The database in the embodiments provided in this invention may include at least one of relational databases and non-relational databases. The non-relational database may include, but is not limited to, a blockchain-based distributed database.The processors in each embodiment provided in the present invention may be, but are not limited to, general-purpose processors, central processing units, graphics processors, digital signal processors, programmable logic, quantum computing-based data processing logic, artificial intelligence (AI) processors, and the like.

[0116] Each of the technical features of the above embodiments can be combined in any way, and for the sake of brevity, not all possible combinations of each of the technical features in the above embodiments have been described. However, as long as there is no inconsistency in these combinations of technical features, they should be considered to fall within the scope of the present invention.

[0117] The above examples represent only a few embodiments of the present invention, and while the description is more specific and detailed, it should not be understood as limiting the scope of protection of the present invention. Those skilled in the art can make some modifications and improvements without departing from the spirit of the present invention, and all of these fall within the scope of protection of the present invention. Therefore, the scope of protection of the present invention is as defined in the appended claims.

Claims

1. A method for fitting hearing aids, Based on user attribute data and hearing characteristic data, the signal processing parameters of the hearing aid at different frequencies are initialized, and the signal processing parameters include a gain step (200), Step (400) involves processing the hearing test signal to be reproduced based on the gain after initialization, obtaining the processed hearing test signal, and using the hearing test signal to test the hearing level after the user has fitted a hearing aid. The process involves playing back the processed hearing test signal and determining the user's hearing test results after hearing assistance (600), If the hearing test results indicate that the hearing aid does not meet the first hearing requirement, the steps (800) are to adjust the gain of the hearing aid at different frequencies based on the hearing test results and to continuously repeat the hearing test based on the latest adjusted gain until the hearing aid meets the preset first hearing requirement. A method characterized by including

2. The audiometry signal includes a pure tone signal or a vibrato signal, the audiometry result includes a sound field test result, and the step (400) of processing the audiometry signal to be reproduced based on the gain after initialization and obtaining the processed audiometry signal is: The process includes steps (420) of processing a pure tone signal or vibrato signal to be played back based on the gain after initialization, obtaining the processed pure tone signal or vibrato signal, and using the pure tone signal or vibrato signal to perform a sound field test for the user. The step (600) of playing back the processed hearing test signal and confirming the user's hearing test results after hearing aid is, The method according to claim 1, characterized by including a step (620) of reproducing the processed pure tone signal or vibrato signal and determining the user's post-hearing sound field test results.

3. The sound field test results include the user's hearing thresholds at different frequencies after hearing assistance, and the step of adjusting the gain of the hearing aid at different frequencies based on the sound field test results is as follows: Based on a pre-set language spectrum, the desired intensity values ​​of language test signals at different frequencies are determined, The desired gain of the hearing aid at different frequencies is determined by comparing the hearing threshold and desired intensity value at different frequencies. Adjusting the gain of the hearing aid at different frequencies based on the desired gain at different frequencies, The method according to claim 2, characterized by including

4. The audiometry signal further includes language test signals of different frequencies, the audiometry result further includes language listening test results, and the method, after the step of adjusting the gain of the hearing aid at different frequencies based on the sound field test results until the hearing aid satisfies a preset first hearing requirement, Step (840) involves processing a language test signal containing different frequencies based on the latest adjusted gain, obtaining the processed language test signal, and using the language test signal to perform a language listening test on the user. The process includes a step (842) of playing back the processed language test signal and determining the results of the user's post-hearing language audiometry test, If the results of the language listening test indicate that the user's language recognition rate is less than a predetermined desired value for language recognition rate, the steps (844) are to adjust the gain of the hearing aid at different frequencies based on the results of the language listening test and to continuously repeat the language listening test based on the latest adjusted gain until the user's language recognition rate is equal to or greater than the predetermined desired value for language recognition rate, The method according to claim 2, further comprising:

5. After adjusting the gain parameter values ​​of the hearing aid at different frequencies based on the sound field test results until the hearing aid satisfies the preset first hearing requirement, the method continues as follows: The method according to claim 4, further comprising the step that, if the hearing aid satisfies a preset first hearing requirement, the hearing thresholds of the user using the hearing aid at different frequencies are greater than or equal to a desired intensity value of a language test signal at each different frequency.

6. The method according to claim 4, further comprising the step of guiding the user to undergo rehabilitation training if the user's language recognition rate is equal to or greater than a preset desired language recognition rate, and the user's hearing threshold at different frequencies is equal to or greater than a desired intensity value of the language test signal at different frequencies.

7. The results of the aforementioned language audiometry test include the user's language recognition rate at different frequencies after hearing assistance, The step of adjusting the gain of the hearing aid at different frequencies based on the results of the speech audiometry test is: From the results of the aforementioned language listening test, extract the misrecognized words that the user answered incorrectly, To determine the six ring sounds of the misrecognized word and the target frequencies corresponding to the six ring sounds, Adjusting the gain of the hearing aid at the target frequency, The method according to claim 4, characterized by including

8. The auditory characteristic data includes discomfort thresholds at different frequencies and audiograms within a preset time period, and the signal processing parameters further include maximum output power. The step (200) of initializing the signal processing parameters of the hearing aid at different frequencies based on user attribute data and auditory characteristic data is as follows: The method according to claim 1, characterized by including the step (220) of determining the gain of the hearing aid at different frequencies based on the attribute data, the discomfort threshold at different frequencies, and the audiogram, and initializing the gain and maximum output power of the hearing aid at different frequencies.

9. Determining the user's discomfort threshold at different frequencies is A step of playing audio at a preset volume at a specific frequency, Steps to guide users to provide feedback on whether the audio is tolerable, If the user feedback indicates that the sound is unbearable, the process involves determining a pre-set volume level as the user's discomfort threshold at a specific frequency. If the user feedback indicates that the sound is tolerable, the volume is increased until the user provides feedback that the sound is unbearable, and the final volume is determined as the user's discomfort threshold at a specific frequency. The method according to claim 8, characterized by including the following:

10. Initializing the maximum output power of a hearing aid at different frequencies is The method according to claim 8, characterized by including determining the maximum output power at different frequencies based on the discomfort threshold at different frequencies, and initializing the maximum output power at different frequencies.

11. Determining the maximum output power of the hearing aid at different frequencies based on the discomfort threshold at different frequencies is: The method according to claim 10, characterized in that the maximum output power value of the hearing aid at different frequencies is below the user's discomfort threshold at each of those different frequencies.

12. After adjusting the gain of the hearing aid at the target frequency, the method is as follows: The method according to claim 7, characterized in that, when the number of gain adjustments reaches the upper limit of the number of adjustments, the result of the language listening test indicates that the user's language recognition rate at the target frequency is smaller than a preset desired value for language recognition rate, and the result of the sound field test indicates that the user was able to hear the pure tone signal or vibrato signal at the target frequency, the method further includes the step of playing a preset rehabilitation training sample and performing rehabilitation training on the user.

13. After continuously and repeatedly testing the hearing level of the user after they have fitted the hearing aid, based on the latest adjusted gain, the method proceeds as follows: Steps include obtaining hearing test data provided by the user, The steps include adjusting the gain of the hearing aid at different frequencies based on the hearing test data until the hearing aid satisfies a pre-set second hearing requirement, The method according to any one of claims 1 to 7, further comprising:

14. After continuously and repeatedly testing the hearing level of the user after they have fitted the hearing aid, based on the latest adjusted gain, the method proceeds as follows: Steps include obtaining hearing test data provided by the user, The steps include adjusting the gain of the hearing aid at different frequencies based on the hearing test data and the hearing characteristic data until the hearing aid satisfies a pre-set second hearing requirement, The method according to any one of claims 1 to 7, further comprising:

15. A hearing aid comprising a Bluetooth module, a processor, and a speaker, The processor is connected to the Bluetooth module and the speaker. The Bluetooth module is configured to receive hearing test signals of different frequencies and transmit the received hearing test signals to the processor, wherein the processor performs the steps of the method according to any one of claims 1 to 10, adjusts the gain of the hearing aid at different frequencies, processes the hearing test signals based on the adjusted gains, transmits the processed hearing test signals to the speaker, and the speaker reproduces the processed hearing test signals.

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