Hearing aid auxiliary fitting system and fitting method

Abstract

The invention discloses a hearing aid auxiliary fitting system and fitting method. The hearing aid auxiliary fitting system is characterized by comprising a hearing screening module, a dynamic environment adaptation module, a real-time effect simulation module and a sound effect comparison module, the hearing screening module is used for basic hearing testing and loading a preset fitting curve based on a screening result; the dynamic environment adaptation module is used for collecting an environment noise sound spectrum and automatically improving gain in a frequency band where environment noise is seriously masked based on hearing threshold data obtained by the hearing screening module. The real-time effect simulation module is used for converting an external audio signal into an audio signal which is used for simulating the hearing aid and is received in actual use; and the sound effect comparison module is used for collecting sound signals received by different hearing aids, and comparing and analyzing the sound signals. According to the invention, the fitting efficiency of the hearing aid is improved, and the fitting effect and accuracy are also improved.

Description

Technical Field

[0001] This invention relates to the field of hearing aid fitting, and more particularly to a hearing aid assisted fitting system and assisted fitting method. Background Technology

[0002] A hearing aid is a small amplifier that amplifies sounds that are otherwise inaudible. By utilizing the residual hearing of the hearing-impaired person, the sound is transmitted to the auditory center of the brain, allowing them to perceive the sound. This brings great convenience to the hearing-impaired.

[0003] In the process of fitting hearing aids, it is generally necessary to conduct preliminary examinations and communication, such as ear canal examination, hearing assessment, and needs communication. Then, the selection and adjustment of hearing aids are carried out, such as model selection, parameter adjustment, effect evaluation, and subsequent usage guidance and follow-up.

[0004] The hearing aid fitting process suffers from significant fragmentation: a complete hearing test is required to obtain threshold data before hearing aid parameters are manually adjusted, resulting in a time-consuming process and preventing users from immediately perceiving the effects. Existing fitting devices generally suffer from large size and a lack of environmental noise adaptation capabilities, leading to insufficient fitting accuracy in complex acoustic environments. Therefore, addressing these technical problems is a direction that those skilled in the art need to strive towards. Summary of the Invention

[0005] The purpose of this invention is to provide a hearing aid fitting system and method that improve fitting accuracy and enhance user experience.

[0006] To achieve the above objectives, the technical solution adopted by the present invention is: a hearing aid-assisted fitting system, comprising: The hearing screening module is used for basic hearing tests and loads a preset fitting curve based on the screening results; The dynamic environment adaptation module is used to collect the ambient noise spectrum and automatically increase the gain in frequency bands where ambient noise is severely masked, based on the hearing threshold data obtained by the hearing screening module. The real-time effect simulation module is used to convert external audio signals into audio signals that simulate the hearing aids received in actual use. The sound effect comparison module is used to collect the sound signals received by different hearing aids and compare and analyze them.

[0007] In the above technical solution, the dynamic environment adaptation module collects ambient noise signals through a dual-microphone array; The dual-microphone array includes an omnidirectional microphone array and a directional microphone array. The omnidirectional microphone array is used to acquire noise information from all directions, and the directional microphone array is used to acquire noise sources in a predetermined direction and enhance the ability to capture noise in the predetermined direction.

[0008] In the above technical solution, the bidirectional microphone array continuously and in real time collects environmental noise signals, and the dynamic environment adaptation module analyzes, extracts features, judges gain adjustment, and calculates gain compensation for the noise signals. The dynamic environment adaptation module dynamically adjusts the gain of each frequency band of the hearing aid based on the changes in ambient noise collected and monitored in real time by the bidirectional microphone array, in order to ensure the best hearing effect of the hearing aid.

[0009] In the above technical solution, the real-time effect simulation module collects external audio signals, processes the external audio signals, and converts them into external audio digital signals. The external audio digital signals are then used to simulate the audio signals received by the hearing aid in actual use. By outputting the simulated hearing aid audio signals through an output device, the user hears the simulated hearing aid effect, and the final fitting parameters of the hearing aid are determined based on user feedback.

[0010] In the above technical solution, the sound effect comparison module is used to import the audio signal parameters for simulating hearing aids and / or the personalized fitting parameters of hearing aids in the real-time effect simulation module into different models of hearing aids; Different models of hearing aids receive test audio from the same external audio source and collect the differences in sound quality received by the corresponding hearing aids. The sound quality collected by different hearing aids is compared, and the data is stored and analyzed. Alternatively, test audio signals from different hearing aid models can be transmitted via wired or wireless means. Software can then play and collect the test audio from different hearing aids, compare the sound quality played by different hearing aids, and store and analyze the data.

[0011] The present invention also provides a hearing aid fitting assistance method, which uses the above-mentioned hearing aid fitting assistance system, and the steps are as follows: ① Rapid hearing screening: The system performs rapid hearing screening on users based on different frequencies, marks abnormal frequency points, obtains hearing threshold data, forms a complete audiogram draft, and loads the matching preset fitting curve of the hearing aid from the built-in database based on the complete audiogram draft; ② Dynamic environment adaptation: The dynamic environment adaptation module collects the ambient noise spectrum of the fitting environment, and based on the hearing threshold data obtained in step S1, automatically increases the gain of each frequency band of the hearing aid in the frequency band where the ambient noise is severely masked, so as to always maintain the best fitting hearing effect of the hearing aid in subsequent steps. ③ Determination of fitting parameters: External audio is collected through an audio input device, processed and converted into an external audio digital signal. The sound output by the external audio digital signal through the output device can simulate the sound heard by the hearing aid in actual use. The sound of the external audio digital signal is output through the output device so that the user can hear the simulated hearing aid effect. Based on the user feedback, the final fitting parameters of the hearing aid are determined. ④ Hearing aid sound effect comparison: Import the final fitting parameters of the hearing aid in step S3 into the different models of hearing aids to be compared, and set the hearing aids according to the final fitting parameters. Different models of hearing aids are used to receive the sound from a unified external sound source, and the sound quality information of the sound received by different models of hearing aids is collected. The sound quality of different models of hearing aids is compared, and the data is stored and analyzed to assist in the final fitting of hearing aids.

[0012] In the above technical solution, step ② includes the following steps: A1. Simultaneously collect ambient noise signals using a dual-microphone array and convert them into digital signals; A2. Data preprocessing: The acquired digital signals are filtered to remove DC offset and low-frequency jitter interference signals, and the gain of the filtered digital signals is adjusted to ensure that the signal strength acquired by the dual microphone array is consistent. A3. Real-time noise signal analysis and feature extraction: Analyze the frequency spectrum slope of the preprocessed noise signal in step A2, make a preliminary judgment on the characteristics of the noise, and calculate the masking effect value based on the user's hearing threshold data and the sound pressure level of each frequency band. A4. Gain Adjustment in Key Frequency Bands: Based on each frequency band within each frequency band, determine whether there is a noise masking effect. For frequency bands with noise masking effects, adjust the gain to improve the audibility of the sound in that frequency band. A5. Continue the above steps to achieve continuous monitoring and dynamic adjustment.

[0013] In the above technical solution, step ③ includes the following steps: B1. Acquire external audio through an audio input device and convert it into an external audio signal, and perform preliminary amplification and filtering on the external audio signal to remove obvious noise and interference; B2. Process the external audio and convert it into an external audio digital signal. The sound output by the external audio digital signal through the output device can simulate the sound heard by the hearing aid in actual use. The external audio digital signal is preprocessed. B3. The pre-processed external audio digital signal is output through the output device, allowing the user to hear the simulated hearing aid effect in real time. The fitting personnel analyze and optimize the hearing aid parameters based on the changes in the clarity, loudness, and comfort of the sound heard by the user, and determine the final fitting parameters of the hearing aid. B4. Save and / or export the final fitting parameters to the hearing aid so that the hearing aid can operate according to these parameters.

[0014] In the above technical solution, step ④ includes the following steps: C1. Import the final fitting parameters of the hearing aid from step S3 into the different models of hearing aids to be compared, and set the fitting parameters of the hearing aids according to the final fitting parameters. C2. Place the different models of hearing aids to be compared onto the simulated human ear or standard earmold in sequence, and ensure that the wearing position and angle are consistent with the real-life wearing scenario. Also, assign an independent acquisition channel to each group of hearing aids. C3. Different models of hearing aids uniformly receive test audio played from the same external audio source, and the test audio covers multiple frequency bands, different loudnesses and scenarios; C4. Acquire and play the sound signal emitted by the speaker of the hearing aid by using a high-precision digital microphone set at the tympanic membrane position of a simulated human ear or a standard earmold; C5. The user and / or audiologist record and compare the sound played in step C4, save the recorded information parameters, and then analyze the comparison results to assist in the final fitting of the hearing aid.

[0015] In the above technical solution, step ④ includes the following steps: D1. Import the final fitting parameters of the hearing aid from step S3 into the different models of hearing aids to be compared, and set the fitting parameters of the hearing aids according to the final fitting parameters. D2. Connect the different models of hearing aids to be compared directly to the test audio input module and audio processing module via wireless or wired means. D3. Test audio input module box: All hearing aids send test audio. After receiving the test audio, the hearing aids process the audio signal, which is then received by the audio processing module. The audio processing module restores and plays the audio signal, which is then played in real time through headphones or speakers. D4. The user and / or audiologist record and compare the sounds played in step D3, save the recorded information parameters, and then analyze the comparison results to assist in the final fitting of the hearing aid.

[0016] Due to the application of the above technical solution, the present invention has the following advantages compared with the prior art: 1. This invention utilizes a hearing screening module to perform rapid hearing screening for users, a dynamic environment adaptation module to collect environmental noise and perform gain compensation to ensure optimal hearing performance of the hearing aid in noisy environments, providing a stable auditory experience for audiometry. A real-time effect simulation module directly simulates the sound received by the hearing aid during actual use and plays this sound, allowing the user to hear the simulated hearing aid effect. Based on user feedback, the fitting parameters for the hearing aid are determined. Finally, a sound effect comparison module compares different models of hearing aids to assist in the final fitting process. This effectively improves fitting efficiency and accuracy, and also enhances the user experience. Attached Figure Description

[0017] Figure 1 This is a schematic diagram of the hardware architecture for hearing aid fitting in this invention; Figure 2 This is a flowchart of the hearing aid fitting process in this invention. Detailed Implementation

[0018] The present invention will be further described below with reference to embodiments: Example 1: See Figure 1 , 2 As shown, a hearing aid fitting system includes a hearing screening module, a dynamic environment adaptation module, a real-time effect simulation module, and a sound effect comparison module.

[0019] in, Hearing screening module Used for basic hearing tests, and loads a preset fitting curve based on the screening results; used for user hearing screening via the hearing screening module; Dynamic Environment Adaptation Module It is used to collect the sound spectrum of environmental noise and automatically increase the gain in frequency bands where environmental noise is severely masked, based on the hearing threshold data obtained by the hearing screening module. In the dynamic environment adaptation module, ambient noise signals are collected through a dual-microphone array. The dual-microphone array includes an omnidirectional microphone array and a directional microphone array. The omnidirectional microphone array is used to acquire noise information from all directions, and the directional microphone array is used to acquire noise sources in a predetermined direction and enhance the ability to capture noise in the predetermined direction.

[0020] The bidirectional microphone array continuously and in real time acquires ambient noise signals, and the dynamic environment adaptation module analyzes, extracts features, judges gain adjustment, and calculates gain compensation for the noise signals. The dynamic environment adaptation module dynamically adjusts the gain of each frequency band of the hearing aid based on the changes in ambient noise collected and monitored in real time by the bidirectional microphone array, in order to improve the audibility and clarity of sound in noisy environments and ensure the best hearing effect of the hearing aid.

[0021] Real-time effect simulation module Used to convert external audio signals into audio signals that simulate the hearing aid received in actual use; The real-time effect simulation module collects external audio signals, processes them, and converts them into external audio digital signals. This external audio digital signal simulates the audio signals received by the hearing aid in actual use. By outputting the simulated hearing aid audio signal through an output device, the user hears the simulated hearing aid effect, and the final fitting parameters of the hearing aid are determined based on user feedback.

[0022] Sound effect comparison module It is used to collect sound signals received by different hearing aids and to compare and analyze them.

[0023] The sound effect comparison module is used to import the audio signal parameters used to simulate hearing aids and / or the personalized fitting parameters of hearing aids from the real-time effect simulation module into different models of hearing aids. Different models of hearing aids receive test audio from the same external audio source and collect the differences in sound quality received by the corresponding hearing aids. The sound quality collected by different hearing aids is compared, and the data is stored and analyzed. Alternatively, test audio signals from different hearing aid models can be transmitted via wired or wireless means. Software can then play and collect the test audio from different hearing aids, compare the sound quality played by different hearing aids, and store and analyze the data.

[0024] The present invention also provides a hearing aid fitting assistance method, which applies the above-mentioned hearing aid fitting assistance system, and the steps are as follows: ① Rapid hearing screening: The system performs rapid hearing screening on users based on different frequencies, marks abnormal frequency points, obtains hearing threshold data, forms a complete audiogram draft, and loads the matching preset fitting curve of the hearing aid from the built-in database based on the complete audiogram draft; ② Dynamic environment adaptation: The dynamic environment adaptation module collects the ambient noise spectrum of the fitting environment, and based on the hearing threshold data obtained in step S1, automatically increases the gain of each frequency band of the hearing aid in the frequency band where the ambient noise is severely masked, so as to always maintain the best fitting hearing effect of the hearing aid in subsequent steps. ③ Determination of fitting parameters: External audio is collected through an audio input device, processed and converted into an external audio digital signal. The sound output by the external audio digital signal through the output device can simulate the sound heard by the hearing aid in actual use. The sound of the external audio digital signal is output through the output device so that the user can hear the simulated hearing aid effect. Based on the user feedback, the final fitting parameters of the hearing aid are determined. ④ Hearing aid sound effect comparison: Import the final fitting parameters of the hearing aid in step S3 into different models of hearing aids to be compared, and set the hearing aids according to the final fitting parameters. Different models of hearing aids are used to receive the sound from a unified external sound source, and the sound quality information of the sound received by different models of hearing aids is collected. The sound quality of different models of hearing aids is compared, and the data is stored and analyzed to assist in the final fitting of hearing aids.

[0025] The above-mentioned auxiliary fitting methods can effectively improve fitting efficiency and accuracy, while also enhancing the user experience.

[0026] Example 2: A hearing screening module for a hearing aid fitting system, which is used for basic hearing tests and, based on the screening results, loads a preset fitting curve. The screening steps are as follows: S1. Test sequence and initial parameter settings Test each frequency in a fixed order (500Hz→1000Hz→2000Hz→4000Hz) to avoid interference between frequencies; The initial test tone for each frequency is set to 60dB SPL (moderate loudness, taking into account the perceived probability of users with mild / moderate hearing loss), the signal type is pure tone (sine wave), and the duration is 200ms; S2, Adaptive step-size hearing threshold detection (improved Hughson-Westlake method); Initial assessment: Play a 60dB SPL pure tone. The user responds by pressing a button (the hearing aid fitting assistance system is mainly integrated on the main unit, which is a combination of a computer, a computer and a tablet, or a combination of a computer and some computer accessories, which is also used in other embodiments) to indicate "heard" (press the confirmation button) or "not heard" (no operation timeout, the default is 3 seconds of no response is considered not heard). S3, Dynamic Adjustment Strategy: A) If the user “hears” the current volume → reduce it by 10dB (e.g., 60 → 50dB), repeat the test 3 times (to verify stability); if the user can hear it 3 times in a row, then the initial hearing threshold of the frequency is determined to be ≤ the current volume (record the highest “not heard” volume + 10dB as a temporary threshold, for example, if the user hears it at 50dB 3 times in a row, then the temporary threshold is set to 60dB). B) If the user does not hear the current volume → increase it by 5dB (e.g., 60 → 65dB) until the user first reports that they "heard" (record this volume as a temporary upper limit); Threshold determination: The hearing threshold for each frequency is determined by alternating between 3 and 5 times (unit: dB HL, converted to standard hearing loss value using the built-in hearing level calibration chart). For example: 500Hz hearing threshold = 35dB HL (that is, 35dB lower than the reference sensitivity of normal hearing people at this frequency). S4. Abnormal Frequency Point Marking and Refined Triggering If the hearing threshold at a certain frequency exceeds the preset threshold (e.g., ≥40dB HL, the default upper limit of the threshold for key speech frequency bands), it is marked as an "abnormal frequency point" and enters the 1 / 3 octave band refinement test (subsequent steps); otherwise, it directly enters the preset fitting curve loading stage. S5, Abnormal Frequency Point 1 / 3 Octave Band Refinement Test (for severe / sharp-sloping hearing loss, approximately 1-2 minutes) Objective: To further refine the hearing threshold distribution of abnormal frequency points (such as 4000Hz hearing threshold = 60dB HL) found in the four-point screening (such as 3150Hz, 4000Hz, 5000Hz) in their adjacent frequency bands, so as to more accurately locate the area of ​​sharp drop in hearing loss, and the refined frequency band is limited to the range of 500-4000Hz. S6. Refine frequency band selection Based on the center frequency of the abnormal frequency point (e.g., 4000Hz), select adjacent 1 / 3 octave band frequency points (divided according to IEC 61260 standard and within the range of 500-4000Hz, such as 3150Hz, 4000Hz, and 5000Hz; if 5000Hz is outside the range, select the frequency point closest to 4000Hz and within the range, such as 3900Hz or similar reasonable frequency points) to ensure that all refined frequency points are within 500-4000Hz; S7, High-precision threshold detection Repeat the "adaptive step size test" for each refined frequency point (initial volume is set to the abnormal frequency hearing threshold + 5dB, such as 4000Hz abnormal hearing threshold 60dB HL → initial 65dB SPL), reduce the step size to 2-3dB (to improve resolution), and determine a more accurate hearing threshold through 5-7 interactions (e.g., hearing threshold after refinement at 4000Hz = 62dB HL). S8, Data Integration The refined frequency hearing thresholds are combined with the four-point basic screening results to form a complete draft audiogram covering 500-4000Hz (with a focus on speech frequency bands within this range). S9. Preset fitting curve loading and dynamic environmental gain adjustment (real-time adaptation) Matching initial fitting parameters: Based on the final hearing threshold result, the system loads the matching preset fitting curves (such as international standard formulas such as NAL-NL2, DSL v5.0, or manufacturer-customized curves) from the built-in database and automatically calculates the basic gain values ​​required for each frequency from 500 to 4000 Hz (e.g., 500 Hz hearing threshold 35 dB HL → corresponding gain 20 dB; 4000 Hz hearing threshold 60 dB HL → corresponding gain 45 dB).

[0027] Example 3: A dynamic environment adaptation module for a hearing aid fitting system, which is used to collect the ambient noise spectrum and automatically increase the gain in frequency bands where ambient noise is severely masked, based on the hearing threshold data obtained by the hearing screening module. In the dynamic environment adaptation module, ambient noise signals are collected through a dual-microphone array. The dual-microphone array includes an omnidirectional microphone array and a directional microphone array. The omnidirectional microphone array is used to acquire noise information from all directions, and the directional microphone array is used to acquire noise sources in a predetermined direction and enhance the ability to capture noise in the predetermined direction.

[0028] The bidirectional microphone array continuously and in real time acquires ambient noise signals, and the dynamic environment adaptation module analyzes, extracts features, judges gain adjustment, and calculates gain compensation for the noise signals. The dynamic environment adaptation module dynamically adjusts the gain of each frequency band of the hearing aid based on the changes in ambient noise collected and monitored in real time by the bidirectional microphone array, in order to ensure the best hearing effect of the hearing aid.

[0029] The steps for using the dynamic environment adaptation module are as follows: A1. Simultaneously collect ambient noise signals using a dual-microphone array and convert them into digital signals; Among them, the noise signal of the surrounding environment is collected simultaneously by a dual-microphone array. The omnidirectional microphone is used to obtain noise information from all directions, while the directional microphone can focus on noise sources in a specific direction, thereby enhancing the ability to capture noise in a specific direction. The acquired analog noise signal is converted into a digital signal by an ADC for subsequent processing. The acquisition process continues at a set sampling rate to ensure that changes in environmental noise can be reflected in real time. A2. Data Preprocessing: The acquired digital signals are filtered to remove possible interference signals such as DC offset and low-frequency jitter. A low-pass filter is used to remove high-frequency noise interference, and a high-pass filter is used to remove low-frequency noise interference, thereby improving the accuracy of subsequent analysis. The gain of the filtered signal is adjusted to ensure that the signal strength collected by different microphones is consistent, thus avoiding analysis errors caused by differences in microphone sensitivity. A3. Real-time noise signal analysis and feature extraction (real-time processing): 1 / 3 Octave Band Analysis: A 1 / 3 octave band analysis is performed on the preprocessed noise signal, decomposing the 20Hz-20kHz noise signal into 29 frequency bands. The sound pressure level (SPL) of each band is calculated using algorithms such as Fast Fourier Transform (FFT). The spectral slope of each band is calculated; the spectral slope reflects the trend of noise frequency components with frequency variation and is used to determine the noise type (e.g., steady-state noise has a relatively stable spectral slope, while transient noise has a larger spectral slope variation). By analyzing the spectral slope, a preliminary understanding of the noise characteristics can be obtained. Masking effect calculation: Based on the user's hearing threshold data and the sound pressure level (SPL) of each frequency band, the masking effect value for each frequency band is calculated. (The masking effect refers to the fact that the presence of one sound can affect the audibility of another sound. When the sound pressure level of a frequency band exceeds the hearing threshold of that band, a masking effect will occur. The masking effect value can be represented by the difference between the sound pressure level and the hearing threshold, reflecting the potential impact of noise in that frequency band on hearing perception.)

[0030] A4. Key frequency band gain adjustment: Key frequency bands for speech: Focus on the key frequency bands for speech in the range of 500-4000Hz. This band contains most of the sound information required for speech communication. For each frequency band within this band, determine whether its sound pressure level (SPL) exceeds the hearing threshold +15dB. If the SPL of a certain frequency band exceeds the hearing threshold +15dB, it is considered that there is a serious noise masking effect in this frequency band, and gain adjustment is required to improve the audibility of the sound in this frequency band.

[0031] Non-verbal frequency band assessment: For non-verbal frequency bands (frequency bands other than 500-4000Hz in 20Hz-20kHz), it is also determined whether their SPL exceeds the hearing threshold +15dB. Although non-verbal frequency bands have a relatively small direct impact on verbal communication, excessive noise may still affect the overall auditory experience.

[0032] A5. Gain Compensation Calculation and Application (Real-time Adjustment): Hearing loss gain compensation calculation: For frequency bands that are determined to require gain adjustment, the gain compensation value is calculated according to the formula "hearing loss gain compensation = basic compensation (hearing threshold) + α × (noise masking amount)". The baseline compensation (hearing threshold) is determined based on the user's hearing threshold data and is used to compensate for the user's hearing loss. The noise masking is the difference between the sound pressure level (SPL) and the hearing threshold in that frequency band, reflecting the degree to which noise masks that frequency band. α is the frequency band correlation weighting coefficient, with α=1.2 for speech bands and α=0.8 for non-speech bands.

[0033] Gain Adjustment Application: The calculated gain compensation value is applied to the corresponding frequency band gain settings of the hearing aid. Through the system's digital signal processing (DSP) algorithm, the gain of the hearing aid in each frequency band is adjusted in real time to improve the audibility and clarity of key speech frequencies in noisy environments.

[0034] The gain adjustment process is updated in real time on a millisecond timescale to ensure timely response to changes in ambient noise and provide users with a stable listening experience.

[0035] A6. Continuous monitoring and dynamic adjustment (continuous cycle): Continuous environmental noise monitoring: A dual-microphone array continuously collects environmental noise signals in real time, repeatedly performing the aforementioned noise signal analysis, feature extraction, gain adjustment judgment, and gain compensation calculation processes. As environmental noise changes, such as movement of people, vehicle movement, or the activation of electrical equipment, the frequency components and sound pressure level of the noise change, and the system can detect these changes in a timely manner.

[0036] Dynamic gain adjustment: Based on real-time monitoring of changes in ambient noise, the system dynamically adjusts the gain of each frequency band of the hearing aid. If the spectral characteristics of the ambient noise change, causing the masking effect of certain frequency bands to increase or decrease, the system will correspondingly increase or decrease the gain compensation for that frequency band to maintain optimal hearing performance at all times. Throughout use, the system continuously cycles through this process, ensuring that the hearing aid provides users with a clear and comfortable hearing experience in various complex acoustic environments.

[0037] Example 4: A real-time effect simulation module for a hearing aid fitting system, which is used to convert external audio signals into audio signals that simulate the hearing aid received in actual use.

[0038] The real-time effect simulation module collects external audio signals, processes them, and converts them into external audio digital signals. This external audio digital signal simulates the audio signals received by the hearing aid in actual use. By outputting the simulated hearing aid audio signal through an output device, the user hears the simulated hearing aid effect, and the final fitting parameters of the hearing aid are determined based on user feedback.

[0039] The steps for using the real-time effect simulation module are as follows: B1. Audio Input and Preprocessing: Acquire external audio through audio input devices and convert it into an external audio signal. Perform preliminary amplification and filtering on the external audio signal to remove obvious noise and interference. The audio signal acquisition process involves using an integrated audio input device (such as a microphone) to acquire external audio signals that simulate the sound received by the hearing aid during actual use. The acquired audio signals undergo preliminary amplification and filtering to remove noticeable noise and interference, thereby improving signal quality. Signal format conversion: Converting the acquired analog audio signal into a digital signal for subsequent digital processing. Using an appropriate sampling rate and quantization bit depth ensures signal accuracy and integrity. For example, the sampling rate can be set to 44.1kHz or higher, and the quantization bit depth can be set to 16 bits or 24 bits. B2. Process the external audio and convert it into an external audio digital signal. The sound output by the output device of the external audio digital signal can simulate the sound heard by the hearing aid in actual use. The external audio digital signal is preprocessed. There are two processing schemes for external audio digital signals: Option 1: MCU+FPGA+DSP architecture (latency <5ms, supports millisecond-level gain adjustment feedback) A) Multi-channel parallel processing The FPGA is responsible for dividing the input digital audio signal into multiple channels and distributing the signal to different processing channels to achieve multi-channel parallel processing. Each channel can independently process audio signals of different frequency ranges or types.

[0040] The DSP performs complex digital signal processing on the audio signal of each channel, such as Fast Fourier Transform (FFT) to convert the signal from the time domain to the frequency domain, so as to perform ERB-based analysis and processing.

[0041] The MCU coordinates the work of the FPGA and DSP, controlling the progress and parameter adjustments of the entire processing flow. Based on user operations and real-time feedback, the MCU can adjust the gain parameters of each channel in milliseconds and send adjustment commands to the FPGA and DSP.

[0042] B) Dynamic parameter adjustment and environmental noise compensation based on the ERB band In the frequency domain, the audio signal is divided into ERB (Equivalent Rectangular Bandwidth) frequency bands, and the signal in each ERB frequency band is analyzed and processed.

[0043] Based on the user's hearing loss and environmental noise levels, the gain parameters for each ERB band are dynamically adjusted. Combining the environmental noise masking effect value obtained from the dynamic environment adaptation module, the gain is automatically increased for frequency bands with severe noise masking. The compensation amount is calculated using the formula: "Hearing loss gain compensation = Base compensation (hearing threshold) + α × (noise masking amount)", where α is the frequency band correlation weighting coefficient.

[0044] At the same time, environmental noise compensation is performed on the audio signal to reduce noise interference with the speech signal and improve speech clarity.

[0045] C) Three-tiered weighted compensation strategy The fitting parameters are generated based on a three-level weighted compensation strategy, which dynamically include hearing loss compensation components, psychoacoustic compensation components, and comfort compensation components.

[0046] The hearing loss compensation component compensates for hearing loss at each frequency based on the user's hearing screening results, ensuring that the user can hear sounds of normal intensity.

[0047] The psychoacoustic compensation component takes into account the psychoacoustic characteristics of the human auditory system, such as loudness perception and pitch perception, and makes corresponding adjustments to the audio signal to make the sound more natural and comfortable.

[0048] The comfort compensation component fine-tunes the gain and timbre of the audio signal based on the user's subjective feelings, avoiding excessively loud or muffled sound and improving wearing comfort.

[0049] Option 2: MCU + DSP architecture (latency <80ms, reducing hardware costs through time-sharing processing) A) Time-sharing processing The MCU distributes the input digital audio signals to the DSP for processing according to a certain time sequence. Due to hardware cost limitations, multi-channel parallel processing cannot be implemented. Therefore, a time-division processing approach is adopted to process audio signals of different frequency ranges or types in different time periods.

[0050] After receiving the audio signal assigned by the MCU, the DSP processes the signal according to a predetermined processing flow. First, it performs ERB-based analysis and processing, dividing the signal into different ERB frequency bands.

[0051] B) Dynamic parameter adjustment and environmental noise compensation based on the ERB band Similar to Option 1, the signals of each ERB band are analyzed and processed in the frequency domain. Based on the user's hearing loss and ambient noise levels, the gain parameters of each ERB band are dynamically adjusted to compensate for ambient noise.

[0052] Although the processing speed is relatively slow, with reasonable time allocation and algorithm optimization, audio processing can still be completed within a latency of <80ms.

[0053] C) Three-tiered weighted compensation strategy Similarly, fitting parameters based on a three-level weighted compensation strategy are generated, including hearing loss compensation components, psychoacoustic compensation components, and comfort compensation components. By adjusting the audio signal, hearing loss compensation, psychoacoustic optimization, and comfort enhancement are achieved.

[0054] B3. The pre-processed external audio digital signal is output through the output device, allowing the user to hear the simulated hearing aid effect in real time. The fitting personnel analyze and optimize the hearing aid parameters based on the changes in the clarity, loudness, and comfort of the sound heard by the user, and determine the final fitting parameters of the hearing aid. In this step, the processed external audio digital signal is output through headphones, allowing the user to hear the simulated hearing aid effect in real time. The user can intuitively feel the changes in clarity, loudness, comfort, and other aspects of the sound.

[0055] Meanwhile, users / audiologists can fine-tune the compensation parameters for each frequency using the system's touchscreen and rotary encoder (these two components work in conjunction with the hearing aid fitting assistance system). The touchscreen displays the gain curves and parameter values ​​for each frequency, and users / audiologists can adjust the parameters through clicking, swiping, and other operations. Rotary encoders can be used to precisely adjust parameters such as volume and gain at a specific frequency. The system responds to the user's fine-tuning operations in real time, applies the adjusted parameters to audio processing, and immediately updates the audio output of the headphones.

[0056] During the process of users / audiologists fine-tuning parameters, the system provides real-time feedback on the effects of the adjustments. For example, when a user / audiologist increases the gain of a certain frequency, they can immediately hear the change in the sound at that frequency. Based on the user's feedback, the system can further optimize the processing algorithm and parameter adjustment strategy.

[0057] B4. Save and / or export the final fitting parameters to the hearing aid so that the hearing aid can operate according to these parameters.

[0058] In this step, the user evaluates the audio effect based on their own experience. When the user is satisfied with the simulated hearing aid effect, the final fitting parameters are determined.

[0059] The system can perform comprehensive analysis and optimization of the parameters after user fine-tuning, ensuring the rationality and stability of the parameters.

[0060] The finalized fitting parameters are saved to a local storage device for later use and reference.

[0061] Users can choose to export the fitting parameters to the hearing aid and transmit the parameters to the hearing aid via data cable or wirelessly, so that the hearing aid can operate according to the parameters.

[0062] Example 5: A sound effect comparison module for a hearing aid fitting system, which is used to collect the sound signals received by different hearing aids and compare and analyze them.

[0063] The sound effect comparison module is used to import the audio signal parameters used to simulate hearing aids and / or the personalized fitting parameters of hearing aids from the real-time effect simulation module into different models of hearing aids. Different models of hearing aids receive test audio from the same external audio source and collect the differences in sound quality received by the corresponding hearing aids. The sound quality collected by different hearing aids is compared, and the data is stored and analyzed. The steps for using the sound effects comparison module are as follows: C1. Import the final fitting parameters into the different models of hearing aids to be compared, and set the hearing aids according to the final fitting parameters; Among them, the preliminary preparation includes: importing fitting parameters. Before the formal comparison, the user had already completed the adjustment of personalized fitting parameters (including hearing loss compensation components, psychoacoustic compensation components, and comfort compensation components) through the real-time effect simulation module or other fitting procedures. These parameters had been exported to the multiple hearing aids to be compared via data cable or wirelessly, and each hearing aid had stored the corresponding personalized fitting settings.

[0064] C2. Place the different models of hearing aids to be compared onto the simulated human ear or standard earmold in sequence, and ensure that the wearing position and angle are consistent with the real-life wearing scenario. Also, assign an independent acquisition channel to each group of hearing aids. This step includes: wearing multiple hearing aids and initializing the channels. Hearing aid fixation and earmold fitting: The multiple hearing aids to be compared are sequentially worn on either a simulated human ear or a standard earmold (each hearing aid corresponds to one simulated human ear / earmold, mimicking the structure of a real human ear). The simulated human ear / earmold is fixed to the multi-channel bracket of the device, ensuring that the wearing position and angle are consistent with the actual wearing scenario.

[0065] Channel switching settings: The system assigns an independent acquisition channel to each hearing aid (e.g., channel 1 corresponds to hearing aid A, channel 2 corresponds to hearing aid B). Users / audiologists can manually switch the current hearing aid channel to be compared using the physical knobs or touchscreen buttons on the device panel.

[0066] C3. Test audio playback control Unified input from external audio source: All hearing aids to be compared receive test audio (such as standardized speech, pure tone, and noise mixture signals) played from the same external audio source. The external audio source can be the device's built-in audio storage module (pre-stored with multiple test audios) or an external audio playback device.

[0067] The test audio should cover multiple frequency bands (such as low frequency 125Hz-high frequency 8kHz), different loudness (such as 40dB SPL-70dB SPL), and scenarios (such as speech in a quiet environment and mixed sound in a noisy environment) to comprehensively compare the sound quality, loudness, and noise reduction capabilities of hearing aids.

[0068] Playback Synchronization and Triggering: The system controls the external audio source to synchronously send test audio to all hearing aids, ensuring that each hearing aid receives the same input signal simultaneously, avoiding unfair comparisons due to input differences. Playback is triggered by the user / audiologist via touchscreen buttons or a foot switch, supporting single playback or loop playback modes.

[0069] C4. Sound Acquisition and Signal Processing High-precision digital microphone positioning: A high-precision digital microphone integrated into the system is fixed at the tympanic membrane position (simulating the natural sound-receiving position of the human ear) of each simulated human ear / earmold, with the microphone facing the sound output hole of the hearing aid speaker to ensure that the complete signal of the "actual sound emitted" by the hearing aid is collected.

[0070] The relative positions of the high-precision digital microphone and the hearing aid speaker are fixed to avoid additional errors caused by placement differences.

[0071] Channelized sound acquisition: The digital microphone corresponding to the currently selected hearing aid channel starts working and acquires the sound signal emitted by the hearing aid speaker in real time (microphones of other unselected channels can be muted).

[0072] The data acquisition process synchronously records timestamps and environmental parameters (such as environmental noise intensity) for subsequent analysis and reference.

[0073] C5. Comparison of Listening Tests and Parameter Adjustments Real-time sound output: The collected sound signal from the hearing aid is played in real time through the system's audio output module (such as high-quality headphones or speakers), allowing the user / audiologist to directly hear the effect of the hearing aid "actually producing sound".

[0074] Multi-hearing aid switching comparison: Switch to other hearing aid channels by rotating the physical knob on the device or clicking the channel button on the touch screen (e.g., from "Channel 1 - Hearing A" to "Channel 2 - Hearing Aid B"). After each switch, the system automatically focuses on the microphone signal corresponding to the new channel, collects and plays the output sound of that hearing aid in real time. Users can intuitively compare the differences in sound quality (e.g., clarity, distortion), loudness (e.g., overall gain), and noise reduction capabilities (e.g., speech intelligibility in a noisy background) of different hearing aids under the same test audio.

[0075] Subjective feedback recording: Users / audiologists record the advantages and disadvantages of each hearing aid based on their listening experience (e.g., "Hearing aid C has clearer high frequencies but muffled low frequencies," "Hearing aid D sounds weak after noise reduction"). The system can provide a simple scoring interface or text annotation function to assist in quantifying and comparing results.

[0076] C6. Saving and exporting comparison results Trial listening record storage: The system automatically saves the parameters for each comparison, including: the currently selected hearing aid model, fitting parameter version, test audio type, collection timestamp, and user subjective rating / remarks.

[0077] Data Export: Users / audiologists can export the comparison results as a report file, which includes a summary of the sound quality comparison of each hearing aid, recommendations, etc., to assist in the final decision.

[0078] Example 6: A sound effect comparison module for a hearing aid fitting system, which is used to collect the sound signals received by different hearing aids and compare and analyze them.

[0079] The sound effect comparison module is used to import the audio signal parameters used to simulate hearing aids and / or the personalized fitting parameters of hearing aids from the real-time effect simulation module into different models of hearing aids. Test audio signals from different hearing aid models are transmitted via wired or wireless means. The software plays and collects the test audio from different hearing aids, compares the sound quality played by different hearing aids, and stores and analyzes the data.

[0080] The steps for using the sound effects comparison module are as follows: D1. Import the final fitting parameters of the hearing aids into the different models of hearing aids to be compared, and set the hearing aids according to the final fitting parameters; This step includes: Preliminary preparation: Importing fitting parameters Before the formal comparison, the user had already completed the adjustment of personalized fitting parameters (including hearing loss compensation components, psychoacoustic compensation components, and comfort compensation components) through the real-time effect simulation module or other fitting procedures. These parameters had been exported to the multiple hearing aids to be compared via data cable or wirelessly (such as Bluetooth), and each hearing aid had stored the corresponding personalized fitting settings.

[0081] D2. Connect the different models of hearing aids to be compared directly to the test audio input module and audio processing module via wireless or wired means. This step includes: Multi-hearing aid connection and channel initialization Direct device connection: Connect multiple hearing aids to be compared directly to this fitting assistance system via data cable or wirelessly. Each hearing aid corresponds to an independent signal input channel (e.g., channel 1 corresponds to hearing aid A, and channel 2 corresponds to hearing aid B).

[0082] Channel switching: The system assigns an independent acquisition / playback channel to each hearing aid. Users can manually switch the hearing aid being compared using a physical knob or touchscreen button on the device panel.

[0083] D3. Test audio input module box: All hearing aids send test audio. After receiving the test audio, the hearing aids process the audio signal, which is then received by the audio processing module. The audio processing module restores and plays the audio signal, which is then played in real time through headphones or speakers. This step includes: Test audio playback control: Unified external audio source: All hearing aids receive test audio (such as standardized speech, pure tone, noise mixed signal, etc.) played from the same external audio source. The external audio source can be the device's built-in audio storage module (pre-stored multi-band test audio) or an external device (such as a mobile phone or tablet that transmits audio via wired / wireless connection).

[0084] Audio coverage: The test audio should cover multiple frequency bands (such as low frequency 125Hz-high frequency 8kHz), different loudness (such as 40dB SPL-70dB SPL), and scenarios (such as speech in a quiet environment and mixed sound in a noisy environment) to comprehensively compare the sound quality, loudness, and noise reduction capabilities of hearing aids.

[0085] Synchronous Trigger: The system controls the external audio source to send test audio to all hearing aids simultaneously, ensuring that each hearing aid receives the same input signal at the same time; playback is triggered by the user / audiologist via touch screen button or foot switch, supporting single playback or loop mode.

[0086] Direct signal acquisition and processing: Direct signal input: The hearing aid does not produce sound through its own speaker, but instead outputs the audio signal obtained after receiving and processing the test audio directly to the fitting assistance system via a data cable or wirelessly.

[0087] Internal sound effect playback: After receiving the direct connection signal from each hearing aid, the system restores and plays the signal through the internal audio processing module, displaying the "pure" sound effect of the hearing aid under different fitting parameters (no secondary distortion from the speaker, no environmental noise interference).

[0088] Comparison of listening tests and parameter adjustments: Real-time audio output: The direct signal from the hearing aid in the currently selected channel is processed by the system and played in real time through high-quality headphones or speakers. Users / audiologists can directly hear the original sound effect "internal processed" by the hearing aid (accurately reflecting its algorithm characteristics).

[0089] Multi-device switching comparison: By rotating the physical knob or clicking the channel button on the touch screen, switch to other hearing aid channels (such as switching from "Channel 1 - Hearing A" to "Channel 2 - Hearing Aid B"). The system automatically focuses on the direct connection signal corresponding to the new channel, plays and compares the sound quality differences (such as clarity and distortion), loudness differences (such as overall gain) and noise reduction capabilities (such as speech intelligibility in a noisy background) of different hearing aids in real time.

[0090] Subjective feedback record: Based on the listening experience, users / audiologists record the advantages and disadvantages of each hearing aid. The system provides a simple scoring interface or text notes function to help quantify the results.

[0091] D4. The user and / or audiologist record and compare the sound played in step D3, save the recorded information parameters, and then analyze the comparison results to assist in the final fitting of the hearing aid. This step includes: Saving and exporting comparison results: Trial listening record storage: The system automatically saves the parameters for each comparison, including the currently selected hearing aid model, fitting parameter version, test audio type, collection timestamp, and user subjective rating / remarks.

[0092] Data Export: Users / audiologists can export the comparison results as a report file, which includes a summary of the sound quality comparison of each hearing aid (such as differences in frequency response characteristics, noise reduction algorithm effectiveness rating), recommendations, etc., to assist in the final fitting decision.

[0093] In this invention, Embodiments 2, 3, 4, 5, and 6 can all be integrated into Embodiment 1 (see steps). Figure 2As shown), it is used to achieve high-efficiency and high-precision hearing aid fitting (either of Example 5 and Example 6 can be selected, or the two can be tested in turn to further improve the fitting effect).

[0094] In this invention, a hearing aid-assisted fitting system and fitting method are used, which can effectively improve fitting efficiency, fitting effect, fitting accuracy, and also improve user experience.

[0095] In this invention, when performing assisted fitting of hearing aids, a hardware architecture is required. In one embodiment, this hardware architecture includes a core processing module, an input module, an output module, a storage and configuration module, a human ear model, and a data acquisition module. The input module includes an external audio source / tablet computer, a dual-microphone array, and a direct connection signal from the hearing aid. The external audio source / tablet computer connects the test audio to the audio codec ADC / DAC via an audio input interface. The dual-microphone array is used to acquire ambient noise signals and connects to the audio codec ADC / DAC via the audio input interface. The direct connection signal from the hearing aid connects the audio data from the hearing aid to the MCU via a data interface (partial flow in some embodiments). The headphone output interface in the output module (which can connect to headphones or other speakers, etc.) is used to play out the corresponding audio for listening (flow in some embodiments).

[0096] The human ear model and acquisition module mainly include multiple hearing aid samples (different hearing aids, such as 3 hearing aids) and a microphone array. Each microphone array is used to acquire the sound of one hearing aid sample. The acquired hearing aid signal is transmitted to the audio encoder ADC / DAC in the core processing module, and the MCU+FPGA+DSP in the core processing module work together to perform real-time effect simulation. The corresponding audio is played out for listening through the headphone output interface in the output module (part of the process in some embodiments).

[0097] The touchscreen or rotary knob in the output module connects to the MUC for adjusting volume and other data. It displays the corresponding information via a screen (e.g., LCD). The storage and configuration module connects to the MUC via local memory, fitting parameter database, and other data for storing and retrieving fitting data. (See [link to storage module]). Figure 1 As shown.

[0098] In the description of this invention, it should be understood that the terms "upper," "lower," "top," "bottom," "inner," and "outer," etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings, and are only for the convenience of describing the invention and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation, and therefore should not be construed as a limitation of the invention. In the description of this invention, "a plurality of" means two or more, unless otherwise explicitly specified.

[0099] In this invention, unless otherwise explicitly specified and limited, the terms "installation," "connection," "linking," and "fixing," etc., should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral part; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium. For instance, the two components can be mechanically connected by contact or abutting; they can also be directly hooked or connected by an intermediate medium; or they can refer to the internal communication of two components or the interaction between two components. Those skilled in the art can understand the specific meaning of the above terms in this invention according to the specific circumstances.

Claims

1. A hearing aid fitting assistance system, characterized by: The application relates to an auxiliary hearing aid fitting method and device. The application comprises: a hearing screening module for basic hearing test, and loading preset fitting curves based on screening results; a dynamic environment adaptation module for collecting environmental noise spectrum, and automatically increasing gain in frequency bands seriously masked by environmental noise based on hearing threshold data obtained by the hearing screening module; a real-time effect simulation module for converting external audio signals into audio signals received by a hearing aid in actual use; 2. The hearing aid fitting assistance system according to claim 1, characterized in that: an audio effect comparison module for collecting received sound signals of different hearing aids, and comparing and analyzing the sound signals. In the dynamic environment adaptation module, surrounding environmental noise signals are collected by a double microphone array; 3. The hearing aid fitting assistance system according to claim 2, characterized in that: The double microphone array comprises an omnidirectional microphone array and a directional microphone array, the omnidirectional microphone array is used for acquiring omnidirectional noise information, and the directional microphone array is used for acquiring noise sources in a predetermined direction and enhancing the capturing ability of noise in the predetermined direction. The double microphone array continuously and real-timely collects environmental noise signals, and the dynamic environment adaptation module analyzes the noise signals, extracts features, judges gain adjustment and calculates gain compensation; 4. The hearing aid fitting assistance system according to claim 1, characterized in that: The dynamic environment adaptation module dynamically adjusts the gain of each frequency band of the hearing aid according to the real-time collection and monitoring of environmental noise changes by the double microphone array, so as to ensure the best hearing effect of the hearing aid.

5. The hearing aid fitting assistance system according to claim 1, characterized in that: The real-time effect simulation module collects external audio signals, processes the external audio signals, converts the external audio signals into external audio digital signals, simulates the audio signals received by the hearing aid in actual use, outputs the simulated audio signals of the hearing aid through an output device, enables a user to hear the simulated effect of the hearing aid, and determines the final fitting parameters of the hearing aid according to user feedback. The audio effect comparison module is used for importing the audio signal parameters of the simulated hearing aid and / or the individualized fitting parameters of the hearing aid in the real-time effect simulation module into different types of hearing aids; Different types of hearing aids receive test audio played by the same external sound source and collect the received sound quality differences of the corresponding hearing aids, compare the sound qualities collected by different hearing aids, and store and analyze the data; Or, different types of hearing aids play test audio signals through wired or wireless transmission, collect the test audio of different hearing aids through software, compare the sound qualities played by different hearing aids, and store and analyze the data.

6. An auxiliary hearing aid fitting method, comprising the following steps: ① Hearing rapid screening: rapidly screening the hearing of a user according to different frequencies, marking abnormal frequency points, obtaining hearing threshold data, forming a complete draft of an audiogram, and loading matching preset fitting curves of a hearing aid from a built-in database according to the complete draft of the audiogram; ② Dynamic environment adaptation: collecting environmental noise spectrum of fitting by a dynamic environment adaptation module, and automatically increasing the gain of each frequency band of the hearing aid in frequency bands seriously masked by environmental noise based on the hearing threshold data obtained in step S1, so as to always maintain the best fitting hearing effect of the hearing aid in subsequent steps. ③Determination of the fitting parameters: collecting external audio through an audio input device, processing and converting the external audio into external audio digital signals, the sounds output by the output device based on the external audio digital signals being able to simulate the sounds heard by the hearing aid in actual use, making the user hear the simulated hearing aid effect, and determining the final fitting parameters of the hearing aid according to the user feedback; ④Hearing aid sound effect comparison: importing the final fitting parameters of the hearing aid in step S3 into different types of hearing aids to be compared, and setting the hearing aids according to the final fitting parameters, the different types of hearing aids being used to receive the sounds of a unified external sound source, collecting the sound quality information of the sounds received by the different types of hearing aids, comparing the sound qualities of the different types of hearing aids, and storing and analyzing the data to assist the final fitting of the hearing aid.

7. The hearing aid fitting assistance method according to claim 6, characterized in that: In step ②, the following steps are included: A1, collecting ambient noise signals through a dual-microphone array and converting them into digital signals; A2, data preprocessing: filtering the collected digital signals to remove existing direct current offset and low-frequency jitter interference signals, and adjusting the gain of the filtered digital signals to make the signal strengths collected by the dual-microphone array consistent; A3, real-time analysis of noise signals and real-time extraction of features: analyzing the frequency slope of the preprocessed noise signals in step A2 to preliminarily determine the characteristics of the noise, and calculating the masking effect value according to the user's hearing threshold data and the sound pressure level of each frequency band; A4, gain adjustment of key frequency bands: determining whether there is a noise masking effect in each frequency band within each frequency band, and adjusting the gain of the frequency band with a noise masking effect to improve the audibility of the sound in that frequency band; A5, continuously performing the above steps to achieve continuous monitoring and dynamic adjustment.

8. The hearing aid fitting assistance method according to claim 6, characterized in that: In step ③, the following steps are included: B1, collecting external audio through an audio input device and converting it into external audio signals, and preliminarily amplifying and filtering the external audio signals to remove obvious noise and interference; B2, processing and converting the external audio into external audio digital signals, the sounds output by the output device based on the external audio digital signals being able to simulate the sounds heard by the hearing aid in actual use, and preprocessing the external audio digital signals; B3, outputting the preprocessed external audio digital signals through the output device, and allowing the user to hear the simulated hearing aid effect in real time, the fitting personnel analyzing and optimizing the parameters of the hearing aid according to the changes in the clarity, loudness, and comfort of the sound heard by the user, and determining the final fitting parameters of the hearing aid; B4, saving and / or exporting the final fitting parameters to the hearing aid, so that the hearing aid works according to the parameters.

9. The hearing aid fitting assistance method according to claim 6, characterized in that: In step ④, the following steps are included: C1, importing the final fitting parameters of the hearing aid in step S3 into different types of hearing aids to be compared, and setting the hearing aids according to the final fitting parameters; C2, the different models of hearing aids to be compared are worn on the artificial ear or standard ear mold in turn, and the wearing position and angle are ensured to be consistent with the real scene wearing scene, and each set of hearing aids is assigned an independent acquisition channel; C3, the different models of hearing aids uniformly receive test audio played from the same external sound source, and the test audio covers multiple frequency bands, different loudness and scenes; C4, the sound signal emitted by the loudspeaker of the hearing aid is collected and played through the high-precision digital microphone arranged at the position of the eardrum of the artificial ear or the standard ear mold; C5, the user and / or fitter record, compare and save the recorded information parameters according to the sound played in step C4, and then analyze the comparison results to assist the final fitting of the hearing aid.

10. The hearing aid fitting assistance method according to claim 6, characterized in that: In step ④, the following steps are included: D1, the final fitting parameters of the hearing aid in step S3 are imported into the different models of hearing aids to be compared, and the hearing aids are fitted according to the final fitting parameters; D2, the different models of hearing aids to be compared are respectively connected to the test audio input module and the audio processing module through wireless or wired mode; D3, the test audio input module box sends test audio to all hearing aids, and the audio signal obtained after the hearing aids receive the test audio is received by the audio processing module, and the audio signal is restored and played through the audio processing module, and is played in real time through the earphone or loudspeaker; D4, the user and / or fitter record, compare and save the recorded information parameters according to the sound played in step D3, and then analyze the comparison results to assist the final fitting of the hearing aid.

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