Digital audio signal debugging device for hearing aids

Abstract

This application relates to a digital audio signal tuning device for a hearing aid, comprising a first communication module, a conversion module, and a second communication module connected in sequence. The first communication module is used to connect to a test device and receive an output signal of a first communication protocol from the test device. The output signal of the first communication protocol is a digital audio signal. The conversion module receives the output signal of the first communication protocol sent by the first communication module, converts the output signal of the first communication protocol into an output signal of a second communication protocol, and sends the output signal of the second communication protocol to the second communication module. The output signal of the second communication protocol is a digital audio signal conforming to the hearing aid's receiving protocol, and the first and second communication protocols are different. The second communication module is used to connect to the hearing aid and send the output signal of the second communication protocol to the hearing aid. This application can reduce or even eliminate noise and distortion during audio signal transmission.

Description

Technical Field

[0001] This application relates to the field of electronic technology, and in particular to a digital audio signal tuning device for a hearing aid. Background Technology

[0002] Currently, most hearing aids are digital. Digital hearing aids typically employ various audio signal processing algorithms, such as multi-channel wide dynamic range compression, noise reduction, and feedback cancellation. Developing the algorithm software on the hearing aid chip requires multiple tests of each implemented code block to ensure it is error-free. This involves processing a small amount of data with the code block to check if the resulting data meets expectations. It also requires playing various specific sounds into the hearing aid microphone to check if the sound output from the hearing aid speaker matches expectations. To ensure the algorithm is implemented correctly on the hearing aid, this process is iterated multiple times until no problems are found.

[0003] Currently, the methods used to develop algorithm software on hearing aid chips have several shortcomings: When testing longer sounds, developers can only do so by playing sound into the hearing aid microphone and recording from the hearing aid speaker. This method involves converting analog electrical signals to digital electrical signals, resulting in noise and distortion in the final audio signal. This noise and distortion make it difficult for algorithm developers to accurately check for errors and flaws in the hearing aid algorithm, and also makes it difficult to judge the degree of improvement. To check for errors and confirm the effect, developers need to perform extensive verification and testing. This extends development time, and the quality of the algorithm software is still difficult to guarantee, making it impossible for developers to accurately determine whether the algorithm processing has fully achieved the expected results. Therefore, ensuring the accuracy of signal transmission during hearing aid tuning is an urgent problem to be solved. Summary of the Invention

[0004] Based on this, this application provides a digital audio signal tuning device for hearing aids to solve the problems existing in the prior art.

[0005] In a first aspect, a digital audio signal tuning device for a hearing aid is provided, the device comprising: a first communication module, a conversion module, and a second communication module connected in sequence;

[0006] The first communication module is used to connect to the test equipment and receive the output signal of the first communication protocol output by the test equipment, wherein the output signal of the first communication protocol is a digital audio signal.

[0007] The conversion module is configured to receive the output signal of the first communication protocol sent by the first communication module, convert the output signal of the first communication protocol into the output signal of the second communication protocol, and send the output signal of the second communication protocol to the second communication module; wherein the output signal of the second communication protocol is a digital audio signal conforming to the hearing aid receiving protocol, and the first communication protocol and the second communication protocol are different;

[0008] The second communication module is used to connect to the hearing aid and send the output signal of the second communication protocol to the hearing aid.

[0009] According to one possible implementation method in an embodiment of this application, the second communication module is further configured to receive a return signal of the second communication protocol returned by the hearing aid, wherein the return signal of the second communication protocol is a digital audio signal;

[0010] The conversion module is further configured to receive the return signal of the second communication protocol sent by the second communication module, convert the return signal of the second communication protocol into the return signal of the first communication protocol, and send the return signal of the first communication protocol to the first communication module; wherein the return signal of the first communication protocol conforms to the digital audio signal of the test equipment receiving protocol;

[0011] The first communication module is further configured to send a return signal of the first communication protocol to the test device, and the test device performs tests on the hearing aid based on the return signal of the first communication protocol.

[0012] According to one possible implementation method in an embodiment of this application, the first communication protocol is the USB protocol, and the second communication protocol is the SAI protocol; the conversion module includes a conversion chip, the conversion chip is configured with USB pins and SAI pins, the USB pins are connected to the first communication module, and the SAI pins are connected to the second communication module.

[0013] According to one possible implementation of this application embodiment, the first communication module includes a USB interface connector, one end of which is connected to the USB interface of the test device, and the other end of which is connected to the USB pin.

[0014] According to one possible implementation method in an embodiment of this application, the first communication module further includes an interface protection unit, which includes a first capacitor, a second capacitor, and a first ferrite bead; the first capacitor, the second capacitor, and the first ferrite bead are connected in parallel, and one end of the parallel connection is connected to the USB interface connector, while the other end is grounded.

[0015] According to one possible implementation of this application embodiment, the first communication module further includes a USB chip unit, the USB chip unit including a first resistor, a second ferrite bead and a USB chip, the first resistor is connected to the second ferrite bead and also connected to the USB chip, the second ferrite bead is connected to the USB interface connector, and the USB chip is connected to the conversion chip.

[0016] According to one possible implementation of an embodiment of this application, the conversion module includes a clock unit, which includes a low-frequency clock unit and / or a high-frequency clock unit;

[0017] The low-frequency clock unit includes a third capacitor, a fourth capacitor, and an oscillator; the third capacitor and the fourth capacitor are connected in parallel, with one end grounded and the other end connected to the oscillator; the oscillator is connected to the conversion chip.

[0018] The high-frequency clock unit includes a fifth capacitor, a second resistor, a crystal oscillator, and a third resistor; the fifth capacitor, the second resistor, the crystal oscillator, and the third resistor are connected in series, the fifth capacitor is grounded, and the third resistor is connected to the conversion chip.

[0019] According to one possible implementation method in an embodiment of this application, the first communication module further includes a first time synchronization unit; one end of the first time synchronization unit is connected to the clock unit, and the other end is connected to the USB chip unit;

[0020] The first time synchronization unit is used to synchronize the current time of the working clock of the test equipment with the current time of the working clock of the clock unit.

[0021] According to one possible implementation method in an embodiment of this application, the second communication module includes a SAI interface connector, one end of which is connected to the SAI interface of the hearing aid, and the other end of which is connected to the SAI pin.

[0022] According to one possible implementation method in an embodiment of this application, the second communication module further includes a second time synchronization unit, one end of which is connected to the clock unit and the other end is connected to the SAI interface connector;

[0023] The second time synchronization unit is used to send the operating clock of the clock unit to the hearing aid through the SAI interface connector, and the hearing aid operates based on the time provided by the operating clock.

[0024] According to the technical content provided in the embodiments of this application, this application provides a digital audio signal debugging device for hearing aids, including a first communication module, a conversion module, and a second communication module connected in sequence. The first communication module can receive digital audio signals of a first communication protocol output by a test device and convert them into digital audio signals of a second communication protocol that meet the hearing aid's receiving conditions through the conversion module. In the audio signal processing path, all links are digital signal transmissions, which reduces or even eliminates noise and distortion in the audio signal transmission process, and significantly improves the accuracy of signal transmission during hearing aid debugging. Attached Figure Description

[0025] Figure 1 This is one of the structural block diagrams of the digital audio signal tuning device for a hearing aid in the embodiments of this application;

[0026] Figure 2 This is a second structural block diagram of the digital audio signal tuning device for the hearing aid in this application embodiment;

[0027] Figure 3 This is one of the structural schematic diagrams of the digital audio signal adjustment device for a hearing aid in the embodiments of this application;

[0028] Figure 4 This is a second schematic diagram of the structure of the digital audio signal adjustment device for the hearing aid in the embodiments of this application;

[0029] Figure 5 This is the third schematic diagram of the structure of the digital audio signal adjustment device for the hearing aid in the embodiments of this application;

[0030] Figure 6 This is the fourth schematic diagram of the digital audio signal tuning device for the hearing aid in the embodiments of this application;

[0031] Figure 7 This is the fifth schematic diagram of the digital audio signal adjustment device for the hearing aid in the embodiments of this application. Detailed Implementation

[0032] The present application will be further described in detail below with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative of the present application and are not intended to limit the scope of the present application.

[0033] Figure 1 A schematic diagram of a digital audio signal tuning device for a hearing aid provided in this application embodiment is shown below. Figure 1 As shown, this embodiment provides a digital audio signal adjustment device 100 for a hearing aid. The device includes a first communication module 110, a conversion module 120, and a second communication module 130 connected in sequence. The following describes each module:

[0034] First communication module 110: used to connect to test equipment 200 and receive the output signal of the first communication protocol output by test equipment 200, the output signal of the first communication protocol being a digital audio signal.

[0035] Conversion module 120: is used to receive the output signal of the first communication protocol sent by the first communication module 110, convert the output signal of the first communication protocol into the output signal of the second communication protocol, and send the output signal of the second communication protocol to the second communication module; wherein, the output signal of the second communication protocol is a digital audio signal that conforms to the hearing aid receiving protocol, and the first communication protocol and the second communication protocol are different.

[0036] Second communication module 130: used to connect to hearing aid 300 and send the output signal of the second communication protocol to hearing aid 300.

[0037] Specifically, the digital audio signal debugging device for a hearing aid provided in this embodiment includes a first communication module, a conversion module, and a second communication module connected in sequence. The first communication module is connected to a test device, and the communication protocol between the first communication module and the test device is a first communication protocol. The second communication module is connected to the hearing aid, and the communication protocol between the second communication module and the hearing aid is a second communication protocol, and the first and second communication protocols are different. The conversion module is used for receiving, converting, and transmitting data. The conversion refers to changing the data encapsulation format to conform to the provisions of the first and second communication protocols, without changing the numerical value of the digital audio data itself, ensuring that no noise or distortion is introduced into the digital audio data. The first communication module receives the output signal of the first communication protocol from the test device. The output signal of the first communication protocol is a digital audio signal, and sends it to the conversion module. The conversion module receives the output signal of the first communication protocol sent by the first communication module, converts the output signal of the first communication protocol into an output signal of the second communication protocol that conforms to the hearing aid receiving protocol, and sends the output signal of the second communication protocol to the second communication module. The second communication module sends the output signal of the second communication protocol to the hearing aid.

[0038] As can be seen, the embodiments of this application provide a digital audio signal debugging device for hearing aids, including a first communication module, a conversion module, and a second communication module connected in sequence. The first communication module can receive digital audio signals of a first communication protocol output by a test device and convert them into digital audio signals of a second communication protocol that meet the hearing aid's receiving conditions through the conversion module. In the audio signal processing path, all links are digital signal transmissions, which reduces or even eliminates noise and distortion in the audio signal transmission process and significantly improves the accuracy of signal transmission during hearing aid debugging.

[0039] Furthermore, in existing technologies, when testing the sound of a hearing aid, developers perform sound output to the hearing aid microphone and recording from the hearing aid speaker. In the existing technology path, the "computer speaker-air-hearing aid microphone" stage contains analog signals, while the rest are digital signal stages. During transmission, the audio signal undergoes D / A conversion (conversion from digital electrical signal to analog electrical signal) and electroacoustic conversion (conversion from analog electrical signal to acoustic signal). During the conversion process, due to numerous factors such as signal attenuation, ambient sound interference, circuit thermal noise, and conversion accuracy, the final acquired audio signal will contain noise and distortion. However, in the audio signal processing path of this embodiment, all stages are purely digital. The original stage containing analog signals, "computer speaker-air-hearing aid microphone," has been replaced by a purely digital stage, "first communication module-conversion module-second communication module." After the replacement, all stages of the entire path become purely digital signal stages, allowing the audio signal to pass through all stages without distortion, significantly improving the accuracy of signal transmission during hearing aid adjustment.

[0040] In one embodiment of this application, the second communication module 130 in the digital audio signal debugging device of the hearing aid is further configured to receive a return signal of the second communication protocol returned by the hearing aid 300, wherein the return signal of the second communication protocol is a digital audio signal. The conversion module 120 is further configured to receive the return signal of the second communication protocol sent by the second communication module 130, convert the return signal of the second communication protocol into a return signal of the first communication protocol, and send the return signal of the first communication protocol to the first communication module 110; wherein the return signal of the first communication protocol conforms to the digital audio signal of the receiving protocol of the testing device 200; the first communication module 110 is further configured to send the return signal of the first communication protocol to the testing device 200, and the testing device 200 tests the hearing aid 300 based on the return signal of the first communication protocol.

[0041] Specifically, the device provided in the embodiments of this application also supports a reverse transmission process, that is, the sound signal data is transmitted unchanged from the algorithm code block within the required hearing aid chip to the computer, i.e., the testing device. Furthermore, it can support simultaneous bidirectional transmission, meaning that while the sound data is being transmitted from the computer and testing device to the hearing aid code block via this device, the data processed by the hearing aid code block can be immediately transmitted back to the computer via this device. The specific process is as follows: The second communication module receives a return signal of the second communication protocol from the hearing aid, where the return signal of the second communication protocol is a digital audio signal. The conversion module receives the return signal of the second communication protocol sent by the second communication module, converts the return signal of the second communication protocol into a return signal of the first communication protocol conforming to the receiving protocol of the testing device, and sends the return signal of the first communication protocol to the first communication module; the first communication module sends the return signal of the first communication protocol to the testing device, and the testing device tests the hearing aid based on the return signal of the first communication protocol.

[0042] As can be seen, the embodiments of this application provide a digital audio signal debugging device for hearing aids. This device can receive digital audio signals of a first communication protocol output by a test device via a first communication module and convert them into digital audio signals of a second communication protocol that meet the hearing aid's reception conditions via a conversion module. Simultaneously, it receives digital audio signals of the second communication protocol output by the hearing aid via a second communication module and converts them into digital audio signals of the first communication protocol that meet the test device's reception conditions via a conversion module. This supports simultaneous bidirectional transmission. In the audio signal processing path, all stages involve digital signal transmission, reducing or even eliminating noise and distortion during audio signal transmission, significantly improving the accuracy of signal transmission during hearing aid testing. It allows for quick, comprehensive, and accurate verification of whether the processing results of each algorithm module or code block of the hearing aid for test sound signals of various durations meet expectations. Furthermore, it enables algorithm developers to quickly and accurately check for errors and flaws in the hearing aid algorithm and easily determine the degree of improvement in algorithm performance, thereby significantly shortening development time and correspondingly improving the quality of the algorithm software.

[0043] Furthermore, in existing technologies, the audio signal processing path during hearing aid testing is as follows: digital audio signal playback software - test equipment host - test equipment speaker - air - hearing aid microphone - hearing aid chip - hearing aid algorithm - hearing aid chip - hearing aid horn - air - test equipment microphone - test equipment host - digital audio acquisition software. The audio signal processing path implemented in this embodiment is: digital audio signal playback software - test equipment host - first communication module - conversion module - second communication module - hearing aid chip - hearing aid algorithm - hearing aid chip - second communication module - conversion module - first communication module - test equipment host - digital audio acquisition software. It can be seen that in existing technologies, "test equipment speaker - air - hearing aid microphone" and "hearing aid horn - air - test equipment microphone" are stages containing analog signals, while the rest are digital signal stages. During transmission, the audio signal undergoes D / A conversion and electroacoustic conversion, as well as the reverse electroacoustic conversion and A / D conversion. During these conversion processes, numerous factors such as signal attenuation, environmental noise interference, circuit thermal noise, and conversion accuracy can lead to noise and distortion in the final acquired audio signal. This noise and distortion make it difficult for algorithm developers to accurately check for errors and flaws in the hearing aid algorithm, and to determine the degree of improvement in algorithm performance. To check for errors and confirm effects, developers need to perform extensive verification and testing, thus extending development time while still making it difficult to guarantee the quality of the algorithm software. However, in the audio signal processing path implemented in this embodiment, all stages are purely digital. The stages containing analog signals in the original path have been replaced with purely digital stages: "Second Communication Module - Conversion Module - First Communication Module" and "Second Communication Module - Conversion Module - First Communication Module". After this replacement, all stages in the entire path become purely digital, allowing the audio signal to pass through all stages without distortion, eliminating noise. Furthermore, algorithm developers can quickly and accurately check for errors and flaws in the hearing aid algorithm, and easily determine the degree of improvement in algorithm performance, thereby improving the accuracy of hearing aid testing.

[0044] In one embodiment of this application, the first communication protocol is the USB protocol, and the second communication protocol is the SAI protocol; the conversion module 120 includes a conversion chip 121, which is configured with a USB pin and a SAI pin. The USB pin is connected to the first communication module 110, and the SAI pin is connected to the second communication module 130.

[0045] Specifically, such as Figure 1 As shown, and in combination Figure 2The first communication protocol is the USB protocol, and the second communication protocol is the SAI protocol. The conversion module 120 includes a conversion chip 121, which is an STM32F769NIH chip, to realize data acquisition, conversion, and transmission functions. Figure 2 As shown, the conversion chip 121 is equipped with a USB pin and a SAI pin. The USB pin is connected to the first communication module, and the SAI pin is connected to the second communication module. Specifically, as... Figure 3 As shown, the conversion chip 121 is an STM32F769NIH chip. The conversion chip is equipped with several USB pins and several SAI pins. The USB pins are connected to the first communication module, and the SAI pins are connected to the second communication module.

[0046] In one embodiment of this application, the first communication module 110 includes a USB interface connector 111, one end of which is connected to the USB interface of the test device 200, and the other end of which is connected to a USB pin.

[0047] like Figure 1 As shown, the first communication module 110 includes a USB interface connector 111. One end of the USB interface connector 111 is connected to the USB interface of the test device 200, typically the USB interface of a computer host; the other end of the USB interface connector 111 is connected to the conversion chip 121. Figure 1 The USB interface connector 111 is connected to the conversion chip 121 via the USB chip unit 113. Specifically, as shown... Figure 2 As shown, the other end of the USB interface connector 111 is connected to the USB pin of the conversion chip 121 via the USB chip unit 113. Figure 4 As shown, the USB interface connector 111 uses a MICRO USB connector. Figure 4 The MICRO USB connector is identified by J1. One end of the MICRO USB connector is used to connect to the computer host, and the other end of the MICRO USB connector connects to the USB pin on the STM32F769NIH conversion chip via the USB chip of model USB3320C-EZK.

[0048] In one embodiment of this application, the first communication module 110 further includes an interface protection unit 112, which includes a first capacitor, a second capacitor, and a first ferrite bead. The first capacitor, the second capacitor, and the first ferrite bead are connected in parallel, with one end of the parallel connection connected to the USB interface connector 111 and the other end grounded.

[0049] Specifically, such as Figure 1As shown, the first communication module 110 also includes an interface protection unit 112, used to protect the interface safety when plugging or unplugging the USB interface connector 111. Figure 4 As shown, the interface protection unit 112 includes a first capacitor, a second capacitor, and a first ferrite bead; the first capacitor, the second capacitor, and the first ferrite bead are connected in parallel, and one end of the parallel connection is connected to the USB interface connector 111, while the other end is grounded. Figure 4 In the middle, the first capacitor C42, the second capacitor C43 and the first ferrite bead L5 are connected between the MICRO USB connector and ground to protect the interface when plugging and unplugging the USB data cable.

[0050] In one embodiment of this application, the first communication module 110 further includes a USB chip unit 113, which includes a first resistor, a second ferrite bead, and a USB chip. The first resistor is connected to the second ferrite bead and is also connected to the USB chip. The second ferrite bead is connected to the USB interface connector 111, and the USB chip is connected to the conversion chip 121.

[0051] like Figure 1 As shown, the first communication module 110 also includes a USB chip unit 113. One end of the USB chip unit 113 is connected to the USB interface connector 111; the other end is connected to the conversion chip 121, as shown. Figure 2 As shown, the USB chip unit 113 and the conversion chip 121 are connected via USB pins. Specifically, as... Figure 4 As shown, the USB chip unit 113 includes a first resistor R13, a second ferrite bead L3, and a USB chip. The first resistor R13 is connected to the second ferrite bead L3 and also to the USB chip. The second ferrite bead L3 is connected to the USB interface connector 111, and the USB chip is connected to the conversion chip 121. The second ferrite bead L3 and the first resistor R13 are connected in series between the USB chip and the 5V power supply of the MICRO USB interface (USB interface connector 111) for power supply noise removal and current limiting, protecting system safety. Figure 4 In the USB chip unit 113, ESD protection chips F4 and F5 are also included to prevent damage to the interface from electrostatic discharge during use. The USB chip model selected is USB3320C-EZK chip, which is connected between the MICRO USB interface of J1 and the conversion chip. It is used to convert the ULPI interface provided on the conversion chip to the USB interface to realize high-speed USB communication. Figure 3 In the circuit, resistors R28-30 pull REFSEL0-2 up to the 3.3V power supply to set the chip clock. Resistors R10, R8, capacitor C35, and crystal oscillator X1 form the clock generation unit, which provides the operating clock for the USB chip.

[0052] In one embodiment of this application, the conversion module 120 includes: a clock unit 122, which includes a low-frequency clock unit and / or a high-frequency clock unit; the low-frequency clock unit includes a third capacitor, a fourth capacitor, and an oscillator; the third capacitor and the fourth capacitor are connected in parallel, with one end grounded and the other end connected to the oscillator; the oscillator is connected to the conversion chip 121; the high-frequency clock unit includes a fifth capacitor, a second resistor, a crystal oscillator, and a third resistor; the fifth capacitor, the second resistor, the crystal oscillator, and the third resistor are connected in series, with the fifth capacitor grounded and the third resistor connected to the conversion chip 121.

[0053] like Figure 1 As shown, the conversion module 120 also includes a clock unit 122, which is connected to the conversion chip 121. The clock unit 122 includes a low-frequency clock unit and / or a high-frequency clock unit. Figure 5 As shown, the low-frequency clock unit includes a third capacitor C94, a fourth capacitor C96, and an oscillator Y4. The third capacitor C94 and the fourth capacitor C96 are connected in parallel, with one end grounded and the other end connected to the oscillator Y4. The oscillator Y4 is connected to the conversion chip 121. This low-frequency real-time clock unit provides a low-frequency clock to the conversion chip. The high-frequency clock unit includes a fifth capacitor C45, a second resistor R14, a crystal oscillator X2, and a third resistor R9. These components are connected in series, with the fifth capacitor grounded and the third resistor R9 connected to the conversion chip 121. This high-frequency clock unit provides the master clock to the conversion chip. Figure 5 In this configuration, R94 and C103 are used for system power-on reset time control, and button K1 is connected in parallel with C103 to achieve manual reset function. In one embodiment of this application, the second communication module 130 includes: a SAI interface connector 131, one end of which is connected to the SAI interface of the hearing aid 300, and the other end of which is connected to the SAI pin.

[0054] like Figure 1 As shown, the second communication module 130 includes a SAI interface connector 131. One end of the SAI interface connector 131 is connected to the SAI interface of the hearing aid 300, and the other end of the SAI interface connector 131 is connected to the conversion chip 121. Specifically, as... Figure 2 As shown, the SAI interface connector connects to the SAI pin on the conversion chip 121. Figure 3 As shown, the converter chip 121 is an STM32F769NIH chip. The converter chip is equipped with several USB pins and several SAI pins. The SAI pins are connected to the SAI interface connector.

[0055] In one embodiment of this application, the first communication module 110 further includes: a first time synchronization unit 114; one end of the first time synchronization unit 114 is connected to the clock unit 122, and the other end is connected to the USB chip unit 113; the first time synchronization unit 114 is used to synchronize the current time of the working clock of the test device 200 with the current time of the working clock of the clock unit 122.

[0056] like Figure 1 As shown, the first communication module 110 further includes a first time synchronization unit 114; one end of the first time synchronization unit 114 is connected to the clock unit 122, and the other end is connected to the USB chip unit 113. The first time synchronization unit 114 is used to synchronize the current time of the working clock of the test device 200 with the current time of the working clock of the clock unit 122. Specifically, based on the above embodiments, this application replaces all links containing analog signals in the original audio signal processing path with links containing pure digital signals, realizing that only digital signals exist in the entire audio signal processing path. This ensures in principle that the digital audio signal transmitted from the digital audio signal playback software to the hearing aid algorithm can be completely identical, without any errors or noise. However, pure digitization of all links alone cannot guarantee the stable and reliable long-term operation of the entire audio signal processing process in the real world. After running for a few seconds, tens of seconds, or even a few minutes, the audio signal at the hearing aid algorithm will have some duplicate audio signal sampling points or some audio signal sampling points will be lost compared to the audio signal at the computer. The reason for this phenomenon is clock asynchrony. Because the audio signal processing path involves three independent devices: the testing equipment, the debugger, and the hearing aid. Each device has its own main processor and operates according to its own clock signal. Similar to having three mechanical clocks, the error may not be noticeable in the short term, but after a period of time—such as hours, days, or even years—the three clocks will usually show significant discrepancies. Therefore, ensuring the synchronization of time during the hearing aid debugging signal transmission process and improving the stability of the testing process are problems that need further resolution.

[0057] In this embodiment, one end of the first time synchronization unit 114 is connected to the clock unit 122 of the conversion module, and the other end is connected to the USB chip unit 113. The USB chip unit is connected to the test equipment via a USB interface connector. The digital audio signal debugging device for the hearing aid provided in this embodiment is connected to the test equipment via a standard USB interface and cable. The first time synchronization unit synchronizes the clock unit of the debugging device with the clock of the test equipment based on existing USB transmission technology.

[0058] In one embodiment of this application, the second communication module 130 further includes: a second time synchronization unit 132, one end of which is connected to a clock unit 122 and the other end is connected to a SAI interface connector 131; the second time synchronization unit 132 is used to send the working clock of the clock unit 122 to the hearing aid 300 through the SAI interface connector 131, and the hearing aid 300 operates based on the time provided by the working clock.

[0059] like Figure 1 As shown, one end of the second time synchronization unit 132 is connected to the clock unit 122 of the conversion module 120, and the other end is connected to the hearing aid 300 via the SAI interface connector 131. For example, as Figure 6 As shown, J3 is a SAI interface connector provided in one embodiment of the present invention. The second clock synchronization unit includes signal lines SAI_MCLKA, SAI_SCKA, and SAI_FSA. SAI_MCLKA provides the master clock, SAI_SCKA provides the bit clock, and SAI_FSA provides the synchronization clock. Signal line SAI_SDB provides audio data signal output, SAI_SDA provides audio data signal input, and GND is grounded. Embodiments of this application, through the second clock synchronization unit, for example, the SAI_MCLKA signal line, provide a system clock to the hearing aid device, achieving clock synchronization between the hearing aid digital audio signal debugger and the hearing aid device.

[0060] Existing professional hearing aid chips do not support USB communication, making clock synchronization between the adjustment device and the hearing aid chip difficult to solve. The embodiments of this application provide time to the hearing aid through a second clock synchronization unit, for example, using the SAI_MCLKA signal line as a clock line to provide a clock signal to the hearing aid chip. The hearing aid chip operates according to the clock provided by this clock line, achieving complete synchronization with the clock of the adjustment device. The adjustment device connects to the computer via USB and to the hearing aid via a proprietary SAI connection, achieving clock synchronization among the computer, adjustment device, and hearing aid. This solves the problem of multiple duplicate sampling points or lost sampling points, ensuring stable and reliable operation of the entire audio signal processing process over a long period.

[0061] In some embodiments, the apparatus provided in this application further includes a power module, such as... Figure 4 As shown, the debugging device draws 5V power from the MICRO USB interface shown in J1. Specifically, as... Figure 7As shown, the interface surge protection diode F3 is placed near interface J1 to prevent surge damage during insertion and removal. C111 and C37 are connected between the 5V power supply and ground for power filtering. LED D3 and R17 form a power indicator circuit. In this embodiment of the invention, U6 is a 5V to 3.3V LDO chip, used to convert the 5V power input to obtain the 3.3V power required by the system. U5 is an LDO with a 1.8V output, using a 3.3V power supply as the input power.

[0062] According to the specific embodiments provided in this application, the technical solution provided in this application can have the following advantages:

[0063] The embodiments of this application replace all stages containing analog signals in the original audio signal processing path with stages containing only digital signals, achieving a path where only digital signals exist. This ensures that the digital audio signal is error-free and noise-free when transmitted from the digital audio signal playback software to the hearing aid algorithm. Furthermore, algorithm developers can quickly and accurately check for errors and flaws in the hearing aid algorithm, and easily determine the degree of improvement in algorithm performance, thereby increasing the accuracy of hearing aid testing.

[0064] In the embodiments of this application, the debugging device is connected to the computer via a standard USB interface and cable. The mature USB technology ensures clock synchronization between the debugger and the computer. However, existing professional hearing aid chips do not support USB communication, making clock synchronization between the debugging device and the hearing aid chip difficult to solve. The embodiments of this application provide time to the hearing aid through a second clock synchronization unit, for example, using the SAI_MCLKA signal line as a clock line to provide a clock to the hearing aid chip. The hearing aid chip operates according to the clock provided by this clock line, achieving complete synchronization with the clock of the debugging device. The debugging device connects to the computer via USB and to the hearing aid via a proprietary SAI connection, achieving clock synchronization among the computer, debugging device, and hearing aid. This solves the problem of multiple duplicate sampling points or lost sampling points, ensuring stable and reliable operation of the entire audio signal processing process over a long period.

[0065] The same or similar parts among the above embodiments can be referred to interchangeably. Each embodiment focuses on describing the differences from other embodiments. In particular, the device embodiments are basically similar to the method embodiments, so the description is relatively simple, and the relevant parts can be referred to the description of the method embodiments.

[0066] It should be noted that the embodiments of this application may involve the use of user data. In practical applications, user-specific personal data may be used in the scheme described herein within the scope permitted by applicable laws and regulations, provided that it complies with the applicable laws and regulations of the country (e.g., explicit consent from the user, actual notification to the user, explicit authorization from the user, etc.).

[0067] The specific embodiments described above do not constitute a limitation on the scope of protection of this application. Those skilled in the art should understand that various modifications, combinations, sub-combinations, and substitutions can be made according to design requirements and other factors. Any modifications, equivalent substitutions, and improvements made within the spirit and principles of this application should be included within the scope of protection of this application.

Claims

1. A digital audio signal tuning device for a hearing aid, characterized in that, The device includes a first communication module, a conversion module, and a second communication module connected in sequence. The first communication module is used to connect to the test equipment and receive the output signal of the first communication protocol output by the test equipment, wherein the output signal of the first communication protocol is a digital audio signal. The conversion module is configured to receive the output signal of the first communication protocol sent by the first communication module, convert the output signal of the first communication protocol into the output signal of the second communication protocol, and send the output signal of the second communication protocol to the second communication module; wherein the output signal of the second communication protocol is a digital audio signal conforming to the hearing aid receiving protocol, and the first communication protocol and the second communication protocol are different; The second communication module is used to connect to the hearing aid and send the output signal of the second communication protocol to the hearing aid. The second communication module is further configured to receive a return signal of the second communication protocol returned by the hearing aid, wherein the return signal of the second communication protocol is a digital audio signal; The conversion module is further configured to receive the return signal of the second communication protocol sent by the second communication module, convert the return signal of the second communication protocol into the return signal of the first communication protocol, and send the return signal of the first communication protocol to the first communication module; wherein the return signal of the first communication protocol conforms to the digital audio signal of the test equipment receiving protocol; The first communication module is further configured to send a return signal of the first communication protocol to the test device, and the test device performs tests on the hearing aid based on the return signal of the first communication protocol.

2. The digital audio signal adjustment device for a hearing aid according to claim 1, characterized in that, The first communication protocol is the USB protocol, and the second communication protocol is the SAI protocol; The conversion module includes a conversion chip, which is configured with a USB pin and a SAI pin. The USB pin is connected to the first communication module, and the SAI pin is connected to the second communication module.

3. The digital audio signal adjustment device for a hearing aid according to claim 2, characterized in that, The first communication module includes a USB interface connector, one end of which is connected to the USB interface of the test device, and the other end of which is connected to the USB pin.

4. The digital audio signal adjustment device for a hearing aid according to claim 3, characterized in that, The first communication module further includes an interface protection unit, which includes a first capacitor, a second capacitor, and a first ferrite bead; the first capacitor, the second capacitor, and the first ferrite bead are connected in parallel, and one end of the parallel connection is connected to the USB interface connector, while the other end is grounded.

5. The digital audio signal adjustment device for a hearing aid according to claim 3, characterized in that, The first communication module further includes a USB chip unit, which includes a first resistor, a second ferrite bead, and a USB chip. The first resistor is connected to the second ferrite bead and also to the USB chip. The second ferrite bead is connected to the USB interface connector, and the USB chip is connected to the conversion chip.

6. The digital audio signal adjustment device for a hearing aid according to claim 5, characterized in that, The conversion module includes a clock unit, which includes a low-frequency clock unit and / or a high-frequency clock unit; The low-frequency clock unit includes a third capacitor, a fourth capacitor, and an oscillator; the third capacitor and the fourth capacitor are connected in parallel, with one end grounded and the other end connected to the oscillator; the oscillator is connected to the conversion chip. The high-frequency clock unit includes a fifth capacitor, a second resistor, a crystal oscillator, and a third resistor; the fifth capacitor, the second resistor, the crystal oscillator, and the third resistor are connected in series, the fifth capacitor is grounded, and the third resistor is connected to the conversion chip.

7. The digital audio signal adjustment device for a hearing aid according to claim 6, characterized in that, The first communication module further includes a first time synchronization unit; one end of the first time synchronization unit is connected to the clock unit, and the other end is connected to the USB chip unit; The first time synchronization unit is used to synchronize the current time of the working clock of the test equipment with the current time of the working clock of the clock unit.

8. The digital audio signal adjustment device for a hearing aid according to claim 6, characterized in that, The second communication module includes a SAI interface connector, one end of which is connected to the SAI interface of the hearing aid, and the other end of which is connected to the SAI pin.

9. The digital audio signal adjustment device for a hearing aid according to claim 8, characterized in that, The second communication module further includes a second time synchronization unit, one end of which is connected to the clock unit and the other end of which is connected to the SAI interface connector; The second time synchronization unit is used to send the operating clock of the clock unit to the hearing aid through the SAI interface connector, and the hearing aid operates based on the time provided by the operating clock.

Images