Hearing test method, hearing aid and hearing aid system

Abstract

The invention discloses an audiometry method, a hearing aid and a hearing aid system, and relates to the technical field of hearing aids, the audiometry method is used for the hearing aid, the hearing aid comprises an audio output device and a hearing compensation device, and the audiometry method comprises the following steps: controlling the audio output device to output an audio signal; acquiring a voltage signal, and converting the voltage signal into an ABR detection waveform; inputting the ABR detection waveform into a preset neural network model, and determining hearing loss of the target object; and controlling the hearing compensation device to perform hearing compensation on the ABR detection waveform and then output the ABR detection waveform. The problem that the audiometry mode of an existing hearing aid depends on subjective feedback of a testee or subjective judgment of medical staff and is easily affected by subjective emotion of the testee or the medical staff, and consequently the audiometry precision is low can be solved.

Description

Technical Field

[0001] The present application relates to the technical field of hearing aids, and in particular to an audiometry method, a hearing aid and a hearing aid system. Background Art

[0002] When existing hearing aids are used to test the hearing of some people who have no subjective expression ability, ABR detection is generally used to determine whether the subject can hear the current sound. However, when the subject actively uses the hearing aid for audiometry, after the audiometry is completed, the subject needs to trigger the button on the hearing aid to send feedback to the hearing aid indicating whether the subject can hear the current sound. It can be seen that this audiometry method relies on the subjective feedback of the subject and is easily affected by the subjective emotions of the subject, resulting in low audiometry accuracy; or, when the subject passively uses the hearing aid for audiometry, such as when medical staff actively use hearing aids to test the subject, after the medical staff test the subject, they need to check the data or graphics displayed by the medical instrument to determine whether the subject can hear the current sound. This method relies on the subjective judgment of the medical staff and is easily affected by the subjective emotions of the medical staff, resulting in low audiometry accuracy. Summary of the invention

[0003] The main purpose of this application is to provide an audiometry method, a hearing aid and a hearing aid system, aiming to solve the problem that the audiometry method of the existing hearing aid relies on the subjective feedback of the subject or the subjective judgment of the medical staff, and is easily affected by the subjective emotions of the subject or the medical staff, resulting in low audiometry accuracy.

[0004] To achieve the above object, the present application proposes an audiometry method for a hearing aid, wherein the hearing aid comprises an audio output device and a hearing compensation device, and the audiometry method comprises: Controlling the audio output device to output audio signals; Acquire a voltage signal, and convert the voltage signal into an ABR detection waveform; Input the ABR detection waveform into a preset neural network model to determine the hearing loss of the target subject; The hearing compensation device is controlled to perform hearing compensation on the ABR detection waveform and then output it.

[0005] In one embodiment, the hearing aid further includes an audio acquisition device, and the step of acquiring the voltage signal and converting the voltage signal into an ABR detection waveform includes: Controlling the audio acquisition device to acquire the voltage signal generated by the target object; Calculating a voltage difference between the voltage signal and a preset voltage signal; The voltage difference is converted and output as an ABR detection waveform.

[0006] In one embodiment, after the step of acquiring the voltage signal and converting the voltage signal into an ABR detection waveform, the step further includes: The ABR detection waveform is subjected to noise reduction processing, and the ABR detection waveform after the noise reduction processing is subjected to point sampling processing.

[0007] In one embodiment, the step of controlling the audio output device to output the audio signal includes: The hearing compensation device is controlled to receive the audio signal from the audio output device, and the hearing compensation device is controlled to perform hearing compensation on the audio signal and then output it to the target object.

[0008] In one embodiment, the step of inputting the ABR detection waveform into a preset neural network model to determine the hearing loss of the target object further includes: When the hearing loss of the target object is not within the preset hearing loss range, the method returns to the step of controlling the hearing compensation device to perform hearing compensation on the audio signal and then output it to the target object.

[0009] The present application also proposes a hearing aid, the hearing aid comprising: An audio output device, used for outputting audio signals; A hearing compensation device for performing hearing compensation on the ABR detection waveform; A control device, electrically connected to the audio output device and the hearing compensation device respectively; The control device includes a memory and a processor electrically connected to the memory; The processor, and an audiometry control program stored in the memory and executed by the processor, wherein the audiometry control program implements the audiometry method as described above when executed by the processor.

[0010] In one embodiment, the hearing aid further comprises: An audio collection device, the audio collection device is electrically connected to the control device; The audio acquisition device is used to acquire the voltage signal generated by the target object; The control device is also used to obtain a voltage signal, calculate a voltage difference between the voltage signal and a preset voltage signal, and convert the voltage difference and output an ABR detection waveform.

[0011] In one embodiment, the audio collection device includes a first electrode and a reference electrode electrically connected to the control device; the first electrode is used to collect a voltage signal generated by the target object and output it to the control device; the reference electrode is used to output a preset voltage signal to the control device; And / or, the audio collection device further includes a second electrode electrically connected to the control device, wherein the second electrode is used to collect a voltage signal generated by the target object and output the voltage signal to the control device.

[0012] In one embodiment, the hearing compensation device is electrically connected to the audio output device, and the hearing compensation device is further used to perform hearing compensation on the audio signal output by the audio output device before outputting the audio signal.

[0013] The present application also proposes a hearing aid system, which includes a hearing aid charging box; and / or, the hearing aid as described above, wherein the hearing aid charging box is used to charge the hearing aid.

[0014] The present application provides an audiometry method, which is used for a hearing aid. The hearing aid includes an audio output device and a hearing compensation device. The audio output device is controlled to output an audio signal to perform an audiological test on a target object, and a voltage signal generated by the target object is obtained at the same time. The obtained voltage signal is converted into an ABR detection waveform by using a preset audiological test algorithm and then input into a preset neural network model. The ABR detection waveform is compared with the preset neural network model to determine the hearing loss of the target object. Then, according to the determined hearing loss of the target object, the hearing compensation device is controlled to perform hearing compensation on the ABR detection waveform and then output, so that the target object can hear the sound currently played by the audio output device, thereby meeting the audiometry needs of some people who have no subjective expression ability. At the same time, there is no need for the target object or medical staff to interact with the hearing aid, effectively overcoming the technical defect that the audiometry method of the existing hearing aid depends on the subjective feedback of the subject or the subjective judgment of the medical staff, and is easily affected by the subjective emotions of the subject or the medical staff, resulting in low audiometry accuracy, and effectively improving the audiometry accuracy. BRIEF DESCRIPTION OF THE DRAWINGS

[0015] The accompanying drawings, which are incorporated in and constitute a part of this specification, illustrate embodiments consistent with the present application and, together with the description, serve to explain the principles of the present application.

[0016] In order to more clearly illustrate the embodiments of the present application or the technical solutions in the prior art, the drawings required for use in the embodiments or the description of the prior art will be briefly introduced below. Obviously, for ordinary technicians in this field, other drawings can be obtained based on these drawings without paying any creative labor.

[0017] Figure 1 A flowchart of the audiometry method embodiment 1 of the present application is provided; Figure 2 A flow chart of the second embodiment of the audiometry method of the present application; Figure 3A flowchart of Embodiment 3 of the audiometry method of the present application is provided; Figure 4 A flowchart of Embodiment 4 of the audiometry method of the present application is provided; Figure 5 A flowchart of Embodiment 5 of the audiometry method of the present application is provided; Figure 6 A schematic diagram of a circuit function module provided for the hearing aid embodiment 1 of the present application; Figure 7 A schematic diagram of circuit function modules provided for the hearing aid embodiment 2 of the present application; Figure 8 A schematic diagram of a circuit function module provided for the hearing aid embodiment 3 of the present application; Fig. 9 This is a schematic diagram of the circuit function modules provided in Embodiment 1 of the hearing aid system of the present application.

[0018] Description of Figure Numbers: 100. Hearing aid; 110. Audio output device; 120. Hearing compensation device; 130. Control device; 140. Audio acquisition device; 141. First electrode; 142. Reference electrode; 143. Second electrode; 200. Hearing aid charging box.

[0019] The purpose, features and advantages of this application will be further described in conjunction with the embodiments and with reference to the accompanying drawings. DETAILED DESCRIPTION

[0020] It should be understood that the specific embodiments described herein are only used to explain the technical solutions of the present application and are not used to limit the present application.

[0021] In order to better understand the technical solution of the present application, a detailed description will be given below in conjunction with the accompanying drawings and specific implementation methods.

[0022] When existing hearing aids are used to test the hearing of some people who have no subjective expression ability, ABR detection is generally used to determine whether the subject can hear the current sound. However, when the subject actively uses the hearing aid for audiometry, after the audiometry is completed, the subject needs to trigger the button on the hearing aid to send feedback to the hearing aid indicating whether the subject can hear the current sound. It can be seen that this audiometry method relies on the subjective feedback of the subject and is easily affected by the subjective emotions of the subject, resulting in low audiometry accuracy; or, when the subject passively uses the hearing aid for audiometry, such as when medical staff actively use hearing aids to test the subject, after the medical staff test the subject, they need to check the data or graphics displayed by the medical instrument to determine whether the subject can hear the current sound. This method relies on the subjective judgment of the medical staff and is easily affected by the subjective emotions of the medical staff, resulting in low audiometry accuracy.

[0023] To solve the above problems, the present application provides an audiometry method, please refer to Figure 1 and Figure 6 , Figure 1 This is a flow chart of the first embodiment of the audiometry method of the present application. Figure 6 Schematic diagram of circuit function modules of the first embodiment of the hearing aid 100 of the present application.

[0024] In the embodiment of the present application, the audiometry method is executed on the hearing aid 100. The hearing aid 100 is used to perform ABR testing on the user to determine the hearing level of the user.

[0025] Based on the above, it should be noted that users may include but are not limited to people with hearing impairment. In the embodiments of the present application, the target object is specifically a group of people with hearing impairment and lack of subjective expression ability. ABR is the abbreviation of auditory brainstem response. ABR detection is an auditory brainstem evoked potential test, which is an objective and non-invasive test of hearing. It belongs to short latency potential and is usually used for short sound test. ABR examination can be combined with other audiological examinations, that is, audiological tests, which are mainly used to identify hearing loss, sensorineural deafness, hearing loss, and judgment of the site of hearing loss in people with auditory impairment and lack of subjective expression ability.

[0026] In the embodiment of the present application, the hearing aid 100 mainly uses the above characteristics of ABR detection to determine the hearing loss of the target object, wherein the level of hearing loss of the target object is divided into six levels, namely normal, mild, moderate, moderately severe, severe and profound. The average hearing threshold of normal hearing is not less than minus 10 decibels and not more than 25 decibels. In this case, the target object can hear external sounds and language more clearly; the average hearing threshold of mild hearing loss is not less than 26 decibels and not more than 40 decibels. In this case, the target object has no difficulty in close conversation and it does not affect verbal communication; the average hearing threshold of moderate hearing loss is not less than 41 decibels and not more than 55 decibels. The target object feels that the hearing has decreased, and it is difficult to communicate at close range, and the interlocutor needs to repeat the description; the average hearing threshold of moderate to severe hearing loss is not less than 56 decibels and not more than 70 decibels. The target object has a significant hearing loss and needs the interlocutor to talk loudly to hear; the average hearing threshold of severe hearing loss is not less than 71 decibels and not more than 90 decibels. The target object needs the interlocutor to shout loudly in his ear to hear; the average hearing threshold of extremely severe hearing loss is not less than 91 decibels. If the target object's ears are in a state of extremely severe hearing loss for a long time, he can hardly hear the sound of loud shouting in his ear. It can be seen that as the level of hearing loss increases, the greater the hearing loss of the target object, the more severe the hearing impairment.

[0027] In an embodiment of the present application, the audiometry method comprises steps S10 to A40: Step S10, controlling the audio output device to output an audio signal; Step S20, obtaining a voltage signal, and converting the voltage signal into an ABR detection waveform; In an embodiment of the present application, in order to determine the hearing level of the target object, the hearing aid 100 of the present application stores a preset audiological test algorithm, and can perform an audiological test on the target object. To perform an audiological test, the hearing aid 100 may include but is not limited to an audio output device 110 and a hearing compensation device 120. The audio output device 110 can be implemented by a speaker. The speaker can be an electric speaker, an electromagnetic speaker, a piezoelectric speaker, an electrostatic speaker, etc., which are not specifically limited here. The speaker is used to output the audio of the audiological test, wherein the format of the audio can be at least one of MP3, WAV, WMA, MP2, Flac, MIDI, RA, APE, AAC, CDA, MOV, which are not specifically limited here, and the content of the audio can be at least one of voice sound, music, sound effects and narration, and a channel, which are not specifically limited here. The hearing compensation device 120 can be implemented by a microphone, an amplifier, and a transducer. The microphone is used to receive sound waves, convert them into electrical signals and transmit them to the amplifier; the amplifier is used to process the input electrical signals, extract and amplify useful electrical signals, and suppress useless noise signals to ensure that the sound finally transmitted to the target object is clear and natural, and then output to the transducer; the transducer is composed of headphones or bone vibrators, and is used to convert the amplified strong signals from electrical energy into acoustic signals or kinetic energy output so that the target object can perceive and understand the sound.

[0028] Before the acoustic test, the hearing aid 100 is worn on the ear of the target object, waiting for the next test; when the acoustic test is performed, the hearing aid 100 controls the audio output device 110 to output the stored, specific audio for the audio test for the target object to listen to. It should be understood here that after the target object listens to the audio, a certain voltage signal will be generated in its ear. The hearing aid 100 can collect the voltage signal generated by the ear of the target object and transmit it to the built-in preset audio test algorithm so that the preset audio test algorithm converts the collected voltage signal into the corresponding audio test result. The audio test result is usually a waveform, that is, an ABR detection waveform. The ABR detection waveform includes multiple data, each of which includes time and the potential corresponding to the time. The time included in each data is used to characterize the position of the data in the ABR detection waveform, and the potential corresponding to the time can reflect the hearing level of the target object. After obtaining the potential, the sound intensity that the target object can hear corresponding to the potential can be obtained according to the corresponding relationship between the potential and the sound intensity that the target object can hear in the universal standard, and the hearing level of the target object can be judged according to the sound intensity.

[0029] In a feasible implementation, the ABR detection waveform may specifically be at least one of an acoustic impedance audiometry waveform, an otoacoustic emission detection waveform, and an auditory brainstem evoked potential detection waveform. Among them, acoustic impedance audiometry is usually used to understand and diagnose middle ear inflammation, Eustachian tube function, and stapedius muscle reflex, and is generally used to distinguish conductive hearing loss from mixed hearing loss; otoacoustic emission is an audio energy generated in the cochlea and released into the external auditory canal through the ossicular chain and the tympanic membrane; auditory brainstem evoked potential is an electrical activity of nerve impulses caused by sound stimulation on the brainstem auditory conduction pathway, which can reflect the functional state of the auditory nerve and the lower auditory center, and reflects the potential of the conduction ability of the brainstem auditory pathway.

[0030] Step S30, inputting the ABR detection waveform into a preset neural network model to determine the hearing loss of the target object; In the embodiment of the present application, the preset neural network model is a model preset and stored in the hearing aid 100. Since the preset neural network model can be trained based on the training ABR detection waveform and the hearing loss of the target object corresponding to the training ABR detection waveform, and the training ABR detection waveform is an ABR detection waveform with a known hearing loss level, the preset neural network model can be used to determine the hearing loss of the target object corresponding to the ABR detection waveform based on the ABR detection waveform.

[0031] It can be seen that by adopting this method, there is no need for the target object or medical staff to interact with the hearing aid 100 to determine the hearing level of the target object. This can solve the problem that the audiometry method of the existing hearing aid relies on the subjective feedback of the subject or the subjective judgment of the medical staff, and is easily affected by the subjective emotions of the subject or the medical staff, resulting in low audiometry accuracy, thereby effectively improving the audiometry accuracy.

[0032] Step S40, controlling the hearing compensation device to perform hearing compensation on the ABR detection waveform and then output it.

[0033] In an embodiment of the present application, after determining the hearing loss of the target object, the hearing aid 100 outputs the ABR detection waveform to the hearing compensation device 120, and controls the microphone to convert the ABR detection waveform into an electrical signal and then output it to the amplifier, and controls the amplifier to amplify the electrical signal and then further output it to the transducer, so that the transducer converts the amplified electrical signal into an acoustic signal and then outputs it, so that the target object can hear the sound currently played by the audio output device 110. When the entire audiometry process is completed, the influence of the target object on the audiometry result is reduced, thereby improving the accuracy of the audiometry.

[0034] The present application provides an audiometry method, which is used for a hearing aid 100. The hearing aid 100 includes an audio output device 110 and a hearing compensation device 120. The audio output device 110 is controlled to output an audio signal to perform an audiological test on a target object, and a voltage signal generated by the target object is obtained at the same time. The obtained voltage signal is converted into an ABR detection waveform by using a preset audiological test algorithm and then input into a preset neural network model. The ABR detection waveform is compared with the preset neural network model to determine the hearing loss of the target object. Then, according to the determined hearing loss of the target object, the hearing compensation device 120 is controlled to perform hearing compensation on the ABR detection waveform and then output, so that the target object can hear the sound currently played by the audio output device 110, thereby meeting the audiometry needs of some people who have no subjective expression ability. At the same time, there is no need for the target object or medical staff to interact with the hearing aid 100, effectively overcoming the technical defect that the audiometry method of the existing hearing aid depends on the subjective feedback of the subject or the subjective judgment of the medical staff, and is easily affected by the subjective emotions of the subject or the medical staff, resulting in low audiometry accuracy, and effectively improving the audiometry accuracy.

[0035] In one possible implementation, please refer to Figure 2 and Figure 6 , Figure 2 This is a flow chart of the second embodiment of the audiometry method of the present application. Figure 6 Schematic diagram of circuit function modules of the first embodiment of the hearing aid 100 of the present application.

[0036] In the embodiment of the present application, the hearing aid 100 further includes an audio collection device 140. The audio collection device 140 can be implemented by electrodes. The electrodes are specifically medical electrodes, and their main function is to measure and record electrical signals inside the target object, and to analyze and detect electrical signals at different parts.

[0037] In a feasible implementation, the medical electrode may be at least one of a metal electrode, a thin film electrode, a nanoelectrode and a composite electrode, and the specific details are not limited here.

[0038] Step S20 includes steps S21 to S23: Step S21, controlling the audio acquisition device to acquire a voltage signal generated by a target object; In an embodiment of the present application, when the hearing aid 100 performs acoustic mechanical testing on a target object, the audio collection device 140 is placed on the ear of the target object to collect a voltage signal generated by the target object after hearing the audio, and outputs the collected voltage signal to the hearing aid 100.

[0039] Step S22, calculating a voltage difference between the voltage signal and a preset voltage signal; Step S23, converting the voltage difference and outputting an ABR detection waveform.

[0040] It should be noted that the preset voltage signal is a signal with a specific voltage value pre-stored in the audio collection device 140. When performing an acoustic mechanical test, the audio collection device 140 transmits the stored preset voltage signal to the hearing aid 100, which is not limited by the target object.

[0041] In an embodiment of the present application, the hearing aid 100 receives the voltage signal and the preset voltage signal output by the audio acquisition device 140, and calculates the voltage difference between the voltage signal and the preset voltage signal. Further, the hearing aid 100 converts the calculated voltage difference using a built-in preset audiology test algorithm to obtain an ABR detection waveform.

[0042] It can be seen that the acquisition of ABR detection waveform does not require feedback from the target object, which can directly reduce the feedback interference of the target object and improve the efficiency and accuracy of acoustic mechanical testing.

[0043] In one possible implementation, please refer to Figure 3 and Figure 6 , Figure 3 This is a flow chart of the third embodiment of the audiometry method of the present application. Figure 6 Schematic diagram of circuit function modules of the first embodiment of the hearing aid 100 of the present application.

[0044] In the embodiment of the present application, step S20 further includes step S200: Step S200, performing noise reduction processing on the ABR detection waveform, and performing point sampling processing on the ABR detection waveform after the noise reduction processing.

[0045] In the embodiment of the present application, after obtaining the ABR detection waveform, the hearing aid 100 calls the built-in preset audiology test algorithm, and uses the noise reduction and sampling capabilities of the preset audiology test algorithm to successively perform noise reduction and sampling on the ABR detection waveform, thereby obtaining the processed ABR detection waveform. Through noise suppression and sampling selection, the interference of noise at the audiometry site can be effectively reduced, thereby improving the audiometry accuracy.

[0046] In one possible implementation, please refer to Figure 4 and Figure 7 , Figure 4 This is a flow chart of a fourth embodiment of the audiometry method of the present application. Figure 7 This is a schematic diagram of circuit function modules of a second embodiment of a hearing aid 100 of the present application.

[0047] In the embodiment of the present application, step S10 includes step S100 after step S10: Step S100 , controlling the hearing compensation device to receive an audio signal from an audio output device, and controlling the hearing compensation device to perform hearing compensation on the audio signal and then output the audio signal to a target object.

[0048] It should be noted that the loudness range of the audio output by the audio output device 110 is limited, which causes the waveform of the voltage signal generated when the target object listens to the audio to be intermittent rather than continuous, so that the hearing aid 100 does not obtain a stable voltage signal, affecting the audiometry accuracy.

[0049] In view of this situation, in an embodiment of the present application, the audio output device 110 is electrically connected to the hearing compensation device 120. Through the above electrical connection relationship, when the hearing aid 100 performs an acoustic mechanics test on the target object, the hearing aid 100 first controls the audio output device 110 to output the audio to the hearing compensation device 120, and then controls the hearing compensation device 120 to perform hearing compensation on the received audio and then output it to the target object. Since the loudness range of the audio after hearing compensation is larger than that of the audio before hearing compensation, when the target object hears the audio after hearing compensation, its ear can generate a stable and obvious voltage signal, so that the hearing aid 100 also obtains a stable voltage signal, ensuring the audiometry accuracy.

[0050] In one possible implementation, please refer to Figure 5 and Figure 7 , Figure 5 This is a flowchart of a fifth embodiment of the audiometry method of the present application. Figure 7This is a schematic diagram of circuit function modules of a second embodiment of a hearing aid 100 of the present application.

[0051] In the embodiment of the present application, step S30 includes step S300: Step S300, when the hearing loss of the target object is not within the preset hearing loss range, returning to the step of controlling the hearing compensation device to perform hearing compensation on the audio signal and then output it to the target object.

[0052] It should be noted that the preset hearing loss range is the hearing loss range preset and stored in the hearing aid 100, and is also the optimal hearing loss range of the target object. Within this range, the target object can hear the external sounds clearly to the greatest extent, meeting the needs of conversation and the like.

[0053] Based on the above embodiment, in the embodiment of the present application, after the hearing aid 100 obtains a stable voltage signal, the hearing aid 100 uses the built-in preset audiological test algorithm to convert the voltage signal into an ABR detection waveform, and inputs the ABR detection waveform into a preset neural network model, and determines the hearing loss of the target object through the preset neural network model. When the hearing aid 100 determines that the hearing loss of the target object is not within the preset hearing loss range, it means that the previous hearing compensation device 120 has insufficient hearing compensation for the audio, and fails to meet the listening needs of the target object. In response to this, the hearing aid 100 will return to execute the steps of controlling the hearing compensation device 120 to perform hearing compensation on the audio signal and then output it to the target object, obtain the voltage signal, convert the voltage signal into an ABR detection waveform, input the ABR detection waveform into the preset neural network model, and determine the hearing loss of the target object, until the hearing loss of the target object is within the preset hearing loss range, thereby achieving the hearing fitting of the target object, so that the target object can hear the sound played by the audio output device 110 to the greatest extent, and meet the listening needs.

[0054] The present application also provides a hearing aid 100, please refer to Figure 6 , the hearing aid 100 comprises: An audio output device 110, for outputting audio signals; A hearing compensation device 120, for performing hearing compensation on the ABR detection waveform; A control device 130 electrically connected to the audio output device 110 and the hearing compensation device 120 respectively; The control device 130 includes a memory and a processor electrically connected to the memory; The processor, and an audiometry control program stored in the memory and executed by the processor, wherein the audiometry control program implements the audiometry method as described above when executed by the processor.

[0055] The hearing aid 100 provided in the present application adopts the audiometry method in the above embodiment, which can solve the problem that the audiometry method of the existing hearing aid depends on the subjective feedback of the subject or the subjective judgment of the medical staff, and is easily affected by the subjective emotions of the subject or the medical staff, resulting in low audiometry accuracy. Compared with the prior art, the beneficial effects of the hearing aid 100 provided in the present application are the same as the beneficial effects of the audiometry method provided in the above embodiment, and the other technical features of the hearing aid 100 are the same as the features disclosed in the above embodiment method, which will not be repeated here.

[0056] In one possible implementation, please refer to Figure 6 , the hearing aid 100 further includes: An audio collection device 140, wherein the audio collection device 140 is electrically connected to the control device 130; The audio collection device 140 is used to collect the voltage signal generated by the target object; The control device 130 is further used to obtain a voltage signal, calculate a voltage difference between the voltage signal and a preset voltage signal, and convert the voltage difference and output an ABR detection waveform.

[0057] In an embodiment of the present application, the audio collection device 140 can be implemented by electrodes. The electrodes are specifically medical electrodes, and their main function is to measure and record electrical signals inside the target object, and to analyze and detect electrical signals in different parts. That is, when the hearing aid 100 performs an acoustic mechanical test on the target object, the control device 130 controls the audio output device 110 to output audio. At this time, the audio collection device 140 is placed on the ear of the target object, and is mainly used to collect the voltage signal generated by the ear of the target object after hearing the audio, and output the collected voltage signal to the control device 130.

[0058] It should be noted that, during the acoustic mechanics test, the audio acquisition device 140 is also used to output the stored preset voltage signal to the control device 130. The control device 130 receives the voltage signal output by the audio acquisition device 140 and the preset voltage signal, and calculates the voltage difference between the voltage signal and the preset voltage signal. Furthermore, the control device 130 uses the built-in preset audiological test algorithm to convert the calculated voltage difference to obtain the ABR detection waveform. It can be seen that the acquisition of the ABR detection waveform does not require feedback from the target object, which can directly reduce the feedback interference of the target object and improve the efficiency and accuracy of the acoustic mechanics test.

[0059] In one possible implementation, please refer to Figure 8The audio collection device 140 includes a first electrode 141 and a reference electrode 142 electrically connected to the control device 130; the first electrode 141 is used to collect the voltage signal generated by the target object and output it to the control device 130; the reference electrode 142 is used to output a preset voltage signal to the control device 130.

[0060] There are many forms of implementation of the audio collection device 140. In an embodiment of the present application, the audio collection device 140 includes a first electrode 141 and a reference electrode 142. The first electrode 141 and the reference electrode 142 are electrically connected to the control device 130, respectively. When the target object is audiometrically tested, the first electrode 141 is placed on one of the left ear and the right ear of the target object, and is mainly used to collect the voltage signal generated by one of the left ear and the right ear of the target object after listening to the audio; the reference electrode 142 is placed on the head of the target object, and is mainly used to establish a ground connection and generate a preset voltage signal. The control device 130 receives the voltage signal output by the first electrode 141, and receives the preset voltage signal output by the reference electrode 142. By calculating the voltage difference between the voltage signal and the preset voltage signal, the voltage difference is converted using the built-in preset audiological test algorithm, and the ABR detection waveform representing the hearing level of one of the left ear or the right ear of the target object can be obtained. It can be seen that the hearing levels of the left ear and the right ear of the target object are characterized by the control device 130, which reduces human interference, makes the characterization results more referenceable, and can effectively improve the audiometry accuracy.

[0061] In one possible implementation, please refer to Figure 8 The audio collection device 140 also includes a second electrode 143 electrically connected to the control device 130 , and the second electrode 143 is used to collect the voltage signal generated by the target object and output it to the control device 130 .

[0062] In order to realize the simultaneous audiometry of the left ear and the right ear of the target object, in the embodiment of the present application, the audio collection device 140 further includes a second electrode 143, and the second electrode 143 is electrically connected to the control device 130. When the target object is audiometrically tested, the first electrode 141 is placed on the left ear of the target object, mainly used to collect the voltage signal generated by the left ear after listening to the audio; the second electrode 143 is placed on the right ear of the target object, mainly used to collect the voltage signal generated by the right ear after listening to the audio; the reference electrode 142 is placed on the head of the target object, mainly used to establish a ground connection and generate a preset voltage signal.

[0063] Furthermore, the control device 130 receives the first voltage signal output by the first electrode 141, the second voltage signal output by the second electrode 143, and the preset voltage signal output by the reference electrode 142, and calculates the first voltage difference between the first voltage signal and the preset voltage signal, and the second voltage difference between the second voltage signal and the preset voltage signal, and uses the built-in preset audiological test algorithm to convert the first voltage difference and the second voltage difference respectively, so as to simultaneously obtain the ABR detection waveforms representing the hearing levels of the left ear and the right ear of the target object, realize audiometry of the two ears of the target object in the same time period, and improve the audiometry accuracy of the hearing aid 100 as a whole.

[0064] In one possible implementation, please refer to Figure 7 The hearing compensation device 120 is electrically connected to the audio output device 110, and the hearing compensation device 120 is also used to perform hearing compensation on the audio signal output by the audio output device 110 and then output it.

[0065] It should be noted that the loudness range of the audio output by the audio output device 110 is limited, which causes the waveform of the voltage signal generated when the target object listens to the audio to be intermittent rather than continuous, so that the hearing aid 100 does not obtain a stable voltage signal, affecting the accuracy of audiometry.

[0066] In view of this situation, in an embodiment of the present application, the audio output device 110 is electrically connected to the hearing compensation device 120. Through the above electrical connection relationship, when the hearing aid 100 performs an acoustic mechanics test on the target object, the control device 130 first controls the audio output device 110 to output the audio to the hearing compensation device 120, and then controls the hearing compensation device 120 to perform hearing compensation on the received audio and then output it to the target object. Since the loudness range of the audio after hearing compensation is larger than that of the audio before hearing compensation, when the target object hears the audio after hearing compensation, its ear can generate a stable and obvious voltage signal, so that the control device 130 also obtains a stable voltage signal, ensuring the audiometry accuracy.

[0067] This application also provides a hearing aid system, please refer to Fig. 9 , the hearing aid system includes a hearing aid charging box 200; and / or, the hearing aid 100 as described above, the hearing aid charging box 200 is used to charge the hearing aid 100.

[0068] It is worth noting that, because the hearing aid system of the present invention includes all embodiments of the above-mentioned hearing aid 100, the hearing aid system of the present invention has the beneficial effects of all embodiments of the above-mentioned hearing aid 100, which will not be described in detail here.

[0069] The above descriptions are only some embodiments of the present application, and are not intended to limit the patent scope of the present application. All equivalent structural changes made using the contents of the present application specification and drawings under the technical concept of the present application, or direct / indirect applications in other related technical fields are included in the patent protection scope of the present application.

Claims

1. An audiometry method, characterized in that: For a hearing aid, the hearing aid comprises an audio output device and a hearing compensation device, and the audiometry method comprises: Controlling the audio output device to output audio signals; Acquire a voltage signal, and convert the voltage signal into an ABR detection waveform; Input the ABR detection waveform into a preset neural network model to determine the hearing loss of the target subject; The hearing compensation device is controlled to perform hearing compensation on the ABR detection waveform and then output it.

2. The audiometry method according to claim 1, wherein: The hearing aid further includes an audio acquisition device, and the step of acquiring the voltage signal and converting the voltage signal into an ABR detection waveform includes: Controlling the audio acquisition device to acquire the voltage signal generated by the target object; Calculating a voltage difference between the voltage signal and a preset voltage signal; The voltage difference is converted and output as an ABR detection waveform.

3. The audiometry method according to claim 1, wherein: After the step of acquiring the voltage signal and converting the voltage signal into an ABR detection waveform, the following steps are further included: The ABR detection waveform is subjected to noise reduction processing, and the ABR detection waveform after the noise reduction processing is subjected to point sampling processing.

4. The audiometry method according to claim 1, wherein: The step of controlling the audio output device to output the audio signal comprises: The hearing compensation device is controlled to receive the audio signal from the audio output device, and the hearing compensation device is controlled to perform hearing compensation on the audio signal and then output it to the target object.

5. The audiometry method according to claim 4, characterized in that: After the step of inputting the ABR detection waveform into a preset neural network model to determine the hearing loss of the target object, the method further includes: When the hearing loss of the target object is not within the preset hearing loss range, the method returns to the step of controlling the hearing compensation device to perform hearing compensation on the audio signal and then output it to the target object.

6. A hearing aid, characterized in that: The hearing aid comprises: An audio output device, used for outputting audio signals; A hearing compensation device for performing hearing compensation on the ABR detection waveform; A control device, electrically connected to the audio output device and the hearing compensation device respectively; The control device includes a memory and a processor electrically connected to the memory; The processor, and an audiometry control program stored in the memory and executed by the processor, wherein the audiometry control program implements the audiometry method according to any one of claims 1 to 5 when executed by the processor.

7. The hearing aid according to claim 6, characterized in that The hearing aid further comprises: An audio collection device, the audio collection device is electrically connected to the control device; The audio acquisition device is used to acquire the voltage signal generated by the target object; The control device is also used to obtain a voltage signal, calculate a voltage difference between the voltage signal and a preset voltage signal, and convert the voltage difference and output an ABR detection waveform.

8. The hearing aid according to claim 7, characterized in that The audio collection device comprises a first electrode and a reference electrode electrically connected to the control device; the first electrode is used to collect a voltage signal generated by a target object and output it to the control device; the reference electrode is used to output a preset voltage signal to the control device; And / or, the audio collection device further includes a second electrode electrically connected to the control device, wherein the second electrode is used to collect a voltage signal generated by the target object and output the voltage signal to the control device.

9. The hearing aid according to claim 6, characterized in that The hearing compensation device is electrically connected to the audio output device, and the hearing compensation device is further used to perform hearing compensation on the audio signal output by the audio output device and then output it.

10. A hearing aid system, characterized in that: The hearing aid system comprises a hearing aid charging box; and / or, the hearing aid according to any one of claims 6 to 9, the hearing aid charging box is used to charge the hearing aid.

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