Low power hibernate trigger circuit and hearing aid

Abstract

The utility model discloses an embodiment relates to the technical field of hearing aid, concretely relates to a low -power consumption dormancy trigger circuit and hearing aid, the utility model discloses through charging storehouse module and hearing aid module's interface connection transmission communication signal, triggers battery protection circuit cut -off battery power supply and enters the ship mode, utilizes existing interface to realize low -power consumption control, has the advantage that hearing aid can realize fast entering the ship mode, effectively prolongs the standby time of equipment without increasing physical button or special communication component.

Description

Technical Field

[0001] This utility model relates to the field of hearing aid technology, specifically to a low-power sleep trigger circuit and a hearing aid. Background Technology

[0002] Modern hearing aids continue to evolve towards miniaturization and high integration to meet users' needs for privacy and comfort. This results in extremely limited internal space, leaving almost no room after accommodating core components such as the microphone, processor, battery, and receiver. While this highly compact design improves the wearing experience, it also significantly limits functional expansion.

[0003] Specifically, due to the severe lack of internal space for the fabric components, and the equally limited space for the external casing while maintaining a clean and aesthetically pleasing appearance, adding extra physical mechanical buttons or dedicated communication receiving components (such as specific wireless modules or interfaces) to existing hearing aid devices has become extremely difficult, even infeasible, in terms of physical space and structural design. This lack of hardware expansion capabilities directly leads to two key operational problems.

[0004] On the one hand, it is not quick and easy to put the hearing aid into a low-power shipping mode. Shipping mode is crucial for preventing accidental power-on during transportation or warehousing and avoiding battery depletion. The lack of effective additional hardware triggering means that users or operators cannot reliably activate this mode during the shipping preparation phase.

[0005] On the other hand, users cannot independently and directly adjust the volume level or switch listening modes without a smartphone app. Existing limited physical button operations are often complex or unintuitive, while relying on a smartphone app restricts the use by users unfamiliar with smart device operations (such as some elderly people). Furthermore, when the phone is not paired, out of power, or without the app, users will completely lose the ability to quickly adjust the volume and mode, severely impacting the user experience.

[0006] Therefore, under the strict space constraints that prevent the addition of mechanical buttons or communication components, how to enable hearing aids to quickly enter shipping mode and provide convenient independent volume and mode adjustment functions has become an urgent technical challenge. Utility Model Content

[0007] In view of the above problems, this utility model provides a low-power sleep trigger circuit and hearing aid, which solves the problem of how to enable the hearing aid to quickly enter the shipping mode and provide convenient independent volume and mode adjustment functions under the strict space constraints of not being able to add mechanical buttons or communication components in the prior art.

[0008] In a first aspect, this utility model provides a low-power sleep trigger circuit, the circuit comprising: The charging case module includes a main control circuit and a first interface circuit, wherein the first interface circuit is connected to the main control circuit to transmit the communication signal output by the main control circuit; The device includes a hearing aid module, comprising a hearing aid circuit, a first battery, a second interface circuit, and a battery protection circuit. The first end of the second interface circuit is connected to the first interface circuit, and the second end of the second interface circuit is connected to the battery protection circuit to output a communication signal. The battery protection circuit is connected to the first battery and the hearing aid circuit. The battery protection module controls the on / off state of the first battery according to the communication signal, so that the hearing aid module enters the shipping mode.

[0009] In some optional embodiments, the first interface module includes a first positive contact and a first negative contact, and the second interface module includes a second positive contact and a second negative contact; when the hearing aid module is placed into the charging case module, the first positive contact is connected to the second positive contact, and the first negative contact is connected to the second negative contact.

[0010] In some optional embodiments, the battery protection circuit includes a battery protection chip, a first resistor, a second resistor, a third resistor, and a first capacitor; The battery protection chip is provided with a first input terminal, a first ground terminal and a first detection terminal. The first input terminal is connected to the first end of the first resistor and the first end of the first capacitor. The second end of the first resistor is connected to the positive terminal of the first battery. The second end of the first capacitor is connected to the negative terminal of the first battery and the first ground terminal. The first detection terminal is connected to the second positive contact in sequence through a second resistor and a third resistor.

[0011] In some optional embodiments, a charging input module is further included, which includes a charging chip, a first electrostatic transistor, a second capacitor, and a third capacitor; the charging chip is provided with a second input terminal and a second output terminal, the second input terminal is connected to the second positive contact, the first end of the first electrostatic transistor, and the first end of the second capacitor, and the second output terminal is connected to the positive terminal of the first battery and the first end of the third capacitor; the second end of the first electrostatic transistor, the second end of the second capacitor, and the second end of the third capacitor are all connected to the power supply ground.

[0012] In some alternative embodiments, the hearing aid circuit includes a DSP chip, a Hall sensor, and a first power supply chip; The Hall sensor and the first power chip are connected to the positive terminal of the first battery to draw power; the first power chip has a first enable terminal and a third output terminal, and the first enable terminal is connected to the first enable output terminal of the Hall sensor to control the third output terminal to output power to the first power terminal of the DSP chip. The DSP chip also has a pickup input terminal and a power amplifier output terminal. The pickup input terminal is used to connect with a microphone to acquire external audio, and amplify the external audio before outputting it through a speaker connected to the power amplifier output terminal.

[0013] In some optional embodiments, a pickup circuit is also included, which includes a second power chip, a microphone, a second electrostatic tube, a third electrostatic tube, a fourth capacitor, and a fifth capacitor; The second power chip is connected to the positive terminal of the first battery to draw power, and the second power chip is provided with a second enable terminal and a fourth output terminal. The second enable terminal is connected to the second enable output terminal of the Hall sensor to control the fourth output terminal to output power to the second power terminal of the microphone. The pickup output terminal of the microphone is connected to the first terminal of the second electrostatic tube and the first terminal of the fourth capacitor. The second terminal of the fourth capacitor is connected to the pickup input terminal of the DSP chip. The second power supply terminal is also connected to the first terminal of the third electrostatic tube and the first terminal of the fifth capacitor. The second terminals of the second electrostatic tube, the third electrostatic tube, and the fifth capacitor are all connected to the power ground.

[0014] In some alternative embodiments, the main control module includes a main control chip, which has a communication output terminal connected to the first positive contact.

[0015] In some optional embodiments, a signal input circuit is also included, which includes a trigger switch, an electrostatic diode, a sixth capacitor, and a fourth resistor; The first end of the trigger switch is connected to the signal input terminal of the main control chip, the first end of the electrostatic diode, the first end of the sixth capacitor, and the first end of the fourth resistor. The second end of the trigger switch, the second end of the electrostatic diode, and the second end of the sixth capacitor are all connected to the power ground. The second end of the fourth resistor is connected to the power supply of the charging compartment module.

[0016] In some optional embodiments, a power supply circuit is also included, which includes a second battery, a voltage regulator chip, a power management chip, and an LDO chip; The voltage regulator chip is connected to an external power supply, a power management chip, and an LDO chip, and is used to convert the external power supply into a regulated power supply and provide regulated power to the back-end circuit. The power management chip is connected to the second battery and is used to output the regulated power supply to the second battery for charging and to control the second battery for discharging. The LDO chip is connected to the second battery and is used to step down the power supply or regulated power supply of the second battery and output power to the main control module and signal input circuit.

[0017] Secondly, this utility model provides a hearing aid, comprising: A pair of headphones; A charging case, wherein the charging case has a receiving space for accommodating the earphones, and the earphone plug is disposed in the receiving space; The hearing aid also includes the aforementioned low-power sleep trigger circuit.

[0018] Compared with the prior art, the low-power sleep trigger circuit and hearing aid of this utility model have the following advantages: This utility model transmits communication signals through the interface connection between the charging case module and the hearing aid module, triggering the battery protection circuit to cut off the battery power supply and enter the shipping mode. It uses the existing interface to achieve low power control, and has the advantages of enabling the hearing aid to quickly enter the shipping mode without adding physical buttons or dedicated communication components, and effectively extending the standby time of the device.

[0019] The above description is merely an overview of the technical solutions of the present utility model embodiments. In order to better understand the technical means of the present utility model embodiments and to implement them in accordance with the contents of the specification, and to make the above and other objects, features and advantages of the present utility model embodiments more obvious and understandable, specific embodiments of the present utility model are described below. Attached Figure Description

[0020] The accompanying drawings are for illustrative purposes only and are not intended to limit the scope of the invention. Furthermore, the same reference numerals denote the same parts throughout the drawings. In the drawings: Figure 1 This diagram shows a schematic of the low-power sleep trigger circuit of Embodiment 1 provided by the present invention; Figure 2 The circuit diagram of the second interface circuit and the charging input circuit provided in Embodiment 2 of this utility model is shown; Figure 3 The circuit diagram of the battery protection circuit according to Embodiment 2 of this utility model is shown; Figure 4 The circuit schematic diagram of the DSP chip according to Embodiment 2 of this utility model is shown; Figure 5 The circuit diagram of the Hall sensor according to Embodiment 2 of this utility model is shown; Figure 6The circuit schematic of the first power chip provided in Embodiment 2 of this utility model is shown; Figure 7 The circuit schematic of the second power supply chip provided in Embodiment 2 of this utility model is shown; Figure 8 The circuit diagram of the pickup provided in Embodiment 2 of this utility model is shown; Figure 9 The circuit diagram of the first interface circuit provided in Embodiment 3 of this utility model is shown; Figure 10 The circuit diagram of the main control circuit of Embodiment 3 of this utility model is shown; Figure 11 The circuit diagram of the signal input circuit provided in Embodiment 3 of this utility model is shown.

[0021] Figure label: 100. Charging case module; 110. Main control circuit; 120. First interface circuit; 200. Hearing aid module; 210. Hearing aid circuit; 220. Second interface circuit; 230. Battery protection circuit; 240. First battery; J1, Second positive contact; J3, Second negative contact; D1, First electrostatic discharge tube; D2, Second electrostatic discharge tube; D3, Third electrostatic discharge tube; D4, Electrostatic discharge diode; C1, First capacitor; C2, Second capacitor; C3, Third capacitor; C4, Fourth capacitor; C5, Fifth capacitor; C6, Sixth capacitor; R1, First resistor; R2, Second resistor; R3, Third resistor; R4, Fourth resistor; U1, Battery protection chip; U2, Charging chip; U3, DSP chip; U4, Hall sensor; U5, First power supply chip; U6, Second power supply chip; M1, Microphone; MCU, Main control chip; CHL-, First negative contact; CHL_DE, First positive contact; S1, Trigger switch. Detailed Implementation

[0022] Exemplary embodiments of the present invention will now be described in more detail with reference to the accompanying drawings. Although exemplary embodiments of the present invention are shown in the drawings, it should be understood that the present invention may be implemented in various forms and should not be limited to the embodiments set forth herein.

[0023] Example 1: Figure 1This invention illustrates a first embodiment of a low-power sleep trigger circuit, comprising a charging case module 100 and a hearing aid module 200. The charging case module 100 includes a main control circuit 110 and a first interface circuit 120, through which the main control circuit 110 transmits communication signals. The hearing aid module 200 includes a hearing aid circuit 210, a first battery 240, a second interface circuit 220, and a battery protection circuit 230. The second interface circuit 220 receives the communication signal and transmits it to the battery protection circuit 230. The battery protection circuit 230 controls the battery's on / off state based on the communication signal, causing the hearing aid to enter a shipping mode.

[0024] In this embodiment, the charging case module 100 refers to a charging container with signal generation function, which can be implemented using a circuit board with a microcontroller to generate communication signals with specific timing. The main control circuit 110 refers to the signal processing core unit, which can be implemented using an embedded processor and is responsible for generating and outputting control signals. The first interface circuit 120 refers to the physical connection channel, which can be implemented using a metal contact array and is used to establish an electrical connection between the charging case and the hearing aid. The battery protection circuit 230 refers to the power management unit, which can be implemented using a protection chip with logic judgment function and performs a battery disconnection operation by detecting communication signal characteristics.

[0025] Specifically, when the hearing aid is placed in the charging case, the first interface circuit 120 and the second interface circuit 220 form a physical connection. The communication signal generated by the main control circuit 110 is transmitted to the battery protection circuit 230 via contacts. This signal contains a pulse sequence of a specific frequency. The battery protection circuit 230 has a built-in delay detection mechanism. When it continuously receives pulse signals that meet preset conditions, it triggers internal protection logic to cut off the battery power supply. At this time, the hearing aid circuit is completely powered off and enters a zero-power shipping mode. To wake it up, simply remove the hearing aid from the charging case to restore the contact disconnection state.

[0026] Compared to existing technologies, traditional solutions rely on physical buttons or wireless modules to trigger the shipping mode. The former is difficult to implement due to space constraints, while the latter increases hardware costs. This solution achieves dual functionality by reusing the charging interface, maintaining the integrity of the device's appearance while avoiding the need for additional components that would occupy space. A signal triggering mechanism replaces mechanical button operation, improving the reliability of mode switching.

[0027] Through the above technical solution, this utility model achieves reliable triggering of the hearing aid's shipping mode without relying on external smart devices or adding physical buttons. Users only need to place the device in the charging case for it to automatically enter a low-power state, and it immediately resumes normal use after being removed. This design, while maintaining the device's miniaturization, solves the problem of accidental triggering during transportation and storage, and gives users independent operation capabilities.

[0028] Example 2: Based on Embodiment 1, this embodiment proposes a second embodiment of a low-power sleep trigger circuit to further describe the hearing aid module 200.

[0029] In some implementations, see Figure 2 , Figure 9 The first interface module includes a first positive contact CHL_DE and a first negative contact CHL-, and the second interface module includes a second positive contact J1 and a second negative contact J3. When the hearing aid module 200 is placed into the charging case module 100, the first positive contact CHL_DE is connected to the second positive contact J1, and the first negative contact CHL- is connected to the second negative contact J3.

[0030] In this embodiment, the first positive contact CHL_DE refers to the metal contact point in the charging case module 100 used for transmitting communication signals and charging current. Specifically, it can be implemented using a gold-plated copper sheet, with a raised structure on its surface to enhance contact reliability. The second positive contact J1 refers to the metal contact point in the hearing aid module 200 corresponding to the charging case. Specifically, it can be implemented using a flexible copper sheet, which deforms to form a tight contact when the module is placed. The first negative contact CHL- and the second negative contact J3 refer to the grounding circuit contacts between the charging case and the hearing aid module 200. Specifically, they can be planar metal sheet structures, forming a stable circuit through surface contact when the module is placed.

[0031] Specifically, when the hearing aid module 200 is placed in the charging case, the first positive contact CHL_DE and the second positive contact J1 form a signal transmission channel through physical contact, while the first negative contact CHL- and the second negative contact J3 form a closed loop. This contact-based connection eliminates the need for additional wireless communication modules or mechanical buttons, directly utilizing the inherent contact interface between the charging case and the hearing aid to complete signal transmission. The contact layout can be symmetrically arranged along the longitudinal axis of the module, achieving a reliable connection within a limited space. The communication signal generated by the charging case main control circuit 110 is transmitted to the hearing aid module 200 through the positive contact pairs, while the negative contact pairs ensure the integrity of the signal loop.

[0032] Compared to existing technologies, traditional hearing aid activation via shipping mode requires either a dedicated wireless receiver module or an additional physical button. The former occupies internal space and increases power consumption, while the latter compromises the device's aesthetic appearance. This solution reuses the existing contact interface between the charging case and the hearing aid, achieving signal transmission without adding new hardware components. This maintains the device's miniaturization while avoiding increased structural complexity. The contact connection method reduces hardware costs by approximately 60% compared to wireless communication solutions, and the reliability of contact detection is significantly improved compared to capacitive sensing methods.

[0033] Through the above technical solution, this utility model effectively solves the problem of limited internal space in hearing aids preventing the addition of triggering elements. The shipping mode is triggered and signal interaction is completed simply by contact. A connection is automatically established during the normal operation of placing the hearing aid in the charging case, allowing for low-power state switching without additional user intervention. The contact mechanism ensures signal transmission stability while avoiding the continuous power consumption problem of the wireless module, enabling the hearing aid to maintain power for up to 12 months during transportation and storage.

[0034] In such Figure 3 In one embodiment shown, the present invention proposes a battery protection circuit 230 including a battery protection chip U1, a first resistor R1, a second resistor R2, a third resistor R3, and a first capacitor C1. The battery protection chip U1 has a first input terminal U1_VDD, a first ground terminal U1_GND, and a first detection terminal U1_CTL. The first input terminal is connected to the first end of the first resistor R1 and the first end of the first capacitor C1. The second end of the first resistor R1 is connected to the positive terminal of the first battery 240, and the second end of the first capacitor C1 is connected to the negative terminal of the first battery 240 and the first ground terminal. The first detection terminal is connected to a second positive contact J1 sequentially through the second resistor R2 and the third resistor R3. The battery protection chip U1 can be a chip of model WSDF2311A.

[0035] In this embodiment, the battery protection chip U1 refers to an integrated circuit used to monitor the battery voltage and control the battery's on / off state. Specifically, it can be implemented using a dedicated chip with overcharge and over-discharge protection functions, which triggers protection actions upon receiving external signals. The first resistor R1 is a current-limiting element connected between the battery's positive terminal and the chip's input terminal. Specifically, it can be implemented using a surface-mount resistor with a fixed resistance value, used for voltage division and limiting the input current. The second resistor R2 and the third resistor R3 are a voltage divider network connected in series between the detection terminal and the contact. Specifically, they can be implemented using a combination of surface-mount resistors with different resistance values, used to adjust the signal detection threshold. The first capacitor C1 is a filter element connected in parallel across the battery terminals. Specifically, it can be implemented using a ceramic capacitor or an electrolytic capacitor, used to eliminate high-frequency interference and stabilize the supply voltage.

[0036] Specifically, when the charging case module 100 contacts the hearing aid module 200, the communication signal transmitted by the second positive contact J1 is input to the first detection terminal of the battery protection chip U1 through a voltage divider network formed by the second resistor R2 and the third resistor R3. The battery protection chip U1 continuously monitors the level change of this port, and when it detects a preset number of continuous pulse signals, it triggers an internal protection mechanism to disconnect the first battery 240 from the hearing aid circuit. The RC filter network formed by the first capacitor C1 and the first resistor R1 can eliminate voltage fluctuations at the moment of contact, preventing false triggering. The combination of the resistance values ​​of the second resistor R2 and the third resistor R3 can be set to different signal detection sensitivities, ensuring that the protection action is only activated when a valid communication command is received.

[0037] Compared to existing technologies, traditional battery protection circuits 230 typically employ a single sensing resistor or direct signal input, which are prone to malfunctions due to poor contact or environmental interference. This solution, through the synergistic effect of a multi-stage resistor voltage divider network and filter capacitors, achieves accurate delay detection while ensuring reliable signal transmission, avoiding false triggering caused by instantaneous signal fluctuations. The combination of resistor values ​​in the voltage divider network allows for flexible adjustment of the detection threshold according to different application scenarios, enhancing circuit adaptability.

[0038] Through the above technical solution, this utility model effectively solves the problem of false triggering caused by unstable contact during the switching of the hearing aid module 200 in the shipping mode. The coordinated design of the voltage divider network and the filter circuit achieves accurate identification of communication signals. This circuit structure achieves reliable signal detection and delay judgment functions within a limited space, ensuring that the hearing aid module 200 enters a low-power state under correct triggering conditions without adding extra hardware. It also avoids the space occupation problem caused by the complex signal processing circuits in traditional solutions.

[0039] In such Figure 2 In one embodiment shown, this utility model proposes a charging input module, which includes a charging chip U2, a first electrostatic transistor D1, a second capacitor C2, and a third capacitor C3. The charging chip U2 has a second input terminal U2_VCC and a second output terminal U2_BAT. The second input terminal is connected to a second positive contact J1, the first end of the first electrostatic transistor D1, and the first end of the second capacitor C2. The second output terminal is connected to the positive terminal of the first battery 240 and the first end of the third capacitor C3. The second ends of the first electrostatic transistor D1, the second capacitor C2, and the third capacitor C3 are all connected to power ground. The charging chip U2 can be a chip of model HP4059D6-42Y.

[0040] In this embodiment, the charging chip U2 refers to an integrated circuit used to convert external power into a voltage suitable for battery charging. Specifically, it can be implemented using a chip with constant current and constant voltage control functions to achieve a stable charging process. The first electrostatic discharge transistor D1 is a transient voltage suppression device used to suppress electrostatic interference. Specifically, it can be implemented using a bidirectional TVS diode to protect the charging circuit from electrostatic discharge shocks. The second capacitor C2 and the third capacitor C3 are energy storage elements used to filter out high-frequency noise. Specifically, they can be implemented using ceramic capacitors or electrolytic capacitors. The second capacitor C2 is connected between the charging input terminal and ground to eliminate input interference, and the third capacitor C3 is connected between the charging output terminal and ground to smooth the output voltage.

[0041] Specifically, when the hearing aid module 200 is placed in the charging case, the second positive contact J1 forms a physical connection with the first positive contact CHL_DE of the charging case. External charging power is input to the second input terminal of the charging chip U2 through the second positive contact J1. The charging chip U2 converts the input voltage into a charging voltage compatible with the first battery 240 and supplies power to the positive terminal of the first battery 240 through its second output terminal. The first electrostatic discharge tube D1 is connected in parallel between the charging input terminal and ground. When an electrostatic pulse is generated at the moment of contact, its bidirectional conduction characteristic clamps abnormal voltage to a safe range. The second capacitor C2 performs high-frequency filtering on voltage fluctuations at the input terminal, and the third capacitor C3 suppresses voltage ripple at the output terminal. Their combined effect improves the stability of the charging process.

[0042] Compared to existing technologies, traditional charging circuits often lack protection against electrostatic discharge (ESD) interference at the moment of contact, which can easily damage the chip. Furthermore, the lack of a multi-stage filtering structure can lead to charging voltage fluctuations. This solution integrates ESD protection devices and two-stage filtering capacitors, achieving reliable protection of the charging interface and optimized power quality within a limited space. Simultaneously, it utilizes the constant voltage control characteristics of the charging chip U2 to avoid the risk of overcharging.

[0043] Through the above technical solution, this utility model can automatically trigger the charging process when the hearing aid comes into contact with the charging case contacts. It effectively eliminates the damage of electrostatic interference to the charging chip U2 through a multi-level protection structure and uses a filter capacitor bank to maintain a stable charging voltage. Thus, it realizes a safe and efficient charging function in a miniaturized device, solving the charging reliability problem caused by the inability to add an independent protection circuit due to space limitations in the prior art.

[0044] In such Figures 4-6In one embodiment shown, the present invention proposes a hearing aid circuit including a DSP chip U3, a Hall sensor U4, and a first power chip U5; the Hall sensor U4 and the first power chip U5 are connected to the positive terminal of the first battery 240 for power supply; the first power chip U5 has a first enable terminal IN_CHECK1 and a third output terminal U5_VOUT, the first enable terminal IN_CHECK1 is connected to the first enable output terminal U4_OUTS of the Hall sensor U4 to control the third output terminal U5_VOUT to output power to the first power terminal U3_VCC of the DSP chip U3; the DSP chip U3 also has a pickup input terminal MIC+ and a power amplifier output terminal SPK+ / SPK-, the pickup input terminal MIC+ is used to connect with the microphone M1 to obtain external audio, and amplify the external audio and output it through the speaker connected to the power amplifier output terminal SPK+ / SPK-.

[0045] In this embodiment, DSP chip U3 refers to a digital signal processing chip, which can be implemented using a low-power embedded processor, used for noise reduction and dynamic range compression of audio signals. Hall sensor U4 refers to a magnetic field detection device based on the Hall effect, which can be implemented using a surface-mount omnipolar Hall switch, used to sense the charging compartment's closed state and generate a trigger signal. First power chip U5 refers to a voltage conversion device with enable control function, which can be implemented using an LDO regulator with an enable pin, controlling the power supply to DSP chip U3 by receiving the control signal from Hall sensor U4. The first enable pin is the control pin of the power chip, which can control the power output state through logic level signals, automatically cutting off the power supply to DSP chip U3 when the charging compartment is detected to be closed. The third output pin is the voltage output port of the power chip, which can output 1.8V or 3.3V DC voltage to provide operating power to DSP chip U3. The audio input pin is the audio signal receiving interface, which can be connected to an electret microphone via capacitive coupling to convert sound wave signals into electrical signals for input. The power amplifier output terminal refers to the power amplifier circuit interface, which specifically drives a miniature balanced armature receiver to convert the processed audio signal into sound wave output. In a specific example, the DSP chip U3 can be a chip with the model name AUDION4, the Hall sensor U4 can be a chip with the model name KTH1604KTH1604SH-FP4, and the first power supply chip U5 can be a chip with the model name SX01P6CCR.

[0046] Specifically, the Hall sensor U4 detects changes in the magnetic field of the charging case in real time. When the hearing aid module 200 is placed in the charging case, the Hall sensor U4 outputs a level signal to the enable terminal of the first power chip U5. Upon receiving a valid enable signal, the first power chip U5 immediately cuts off the power supply to the DSP chip U3, causing the audio processing circuit to enter a power-off state. When the hearing aid module 200 is removed from the charging case, the Hall sensor U4 detects the disappearance of the magnetic field, triggering the first power chip U5 to reactivate the power supply to the DSP chip U3, restoring the hearing aid circuit to normal operation. When powered on, the DSP chip U3 receives analog audio signals from the microphone through the pickup input terminal. After analog-to-digital conversion, digital filtering, and dynamic compression, the processed digital signal drives the speaker to produce sound through the power amplifier output terminal.

[0047] Compared to existing technologies, traditional hearing aids require a separate physical switch to control the circuit's on / off state, which not only occupies space in the housing but is also inconvenient to operate. This solution, through the linkage control of the Hall sensor U4 and the power chip, achieves automatic detection of the device's status and power management, eliminating the need for any additional mechanical switching components. In existing technologies, the DSP chip U3 often operates in a continuous power supply mode, consuming battery power even when not in use. This solution, however, uses an enable control mechanism to automatically cut off power to the core circuitry when the device is stored, significantly reducing standby power consumption.

[0048] Through the above technical solution, this utility model achieves automatic power-off control of the hearing aid module 200 within the charging case without the need for additional external operating components, effectively solving the problem of difficult activation in shipping mode. Simultaneously, through the coordinated operation of the Hall sensor U4 and the power chip, it ensures that full functionality is immediately restored when the user removes the device, avoiding the cumbersome manual switching process of traditional solutions. The DSP chip U3 receives power only when the device is actually in use, extending battery life and preventing accidental triggering, thus improving power management efficiency while maintaining the device's miniaturization.

[0049] In such Figures 7-8In one embodiment shown, this utility model proposes a low-power sleep trigger circuit, including a pickup circuit. The pickup circuit includes a second power chip U6, a microphone M1, a second electrostatic transistor D2, a third electrostatic transistor D3, a fourth capacitor C4, and a fifth capacitor C5. The second power chip U6 is connected to the positive terminal of the first battery 240 for power supply, and the second power chip U6 is provided with a second enable terminal IN_CHECK2 and a fourth output terminal MIC_BIAS. The second enable terminal IN_CHECK2 is connected to the second enable output terminal U4_O of the Hall sensor U4. The UTN connection controls the fourth output terminal MIC_BIAS to output power to the second power supply terminal M1_VDD of the pickup M1; the pickup output terminal M1_OUT of the pickup M1 is connected to the first terminal of the second electrostatic tube D2 and the first terminal of the fourth capacitor C4, the second terminal of the fourth capacitor C4 is connected to the pickup input terminal of the DSP chip U3, and the second power supply terminal is also connected to the first terminal of the third electrostatic tube D3 and the first terminal of the fifth capacitor C5; the second terminals of the second electrostatic tube D2, the third electrostatic tube D3, and the fifth capacitor C5 are all connected to the power ground.

[0050] In this embodiment, the second power supply chip U6 refers to a voltage conversion device with enable control function, specifically an LDO chip or a DC-DC converter chip, used to provide a stable operating voltage to the microphone M1 when the Hall sensor U4 is triggered. The second electrostatic discharge tube D2 and the third electrostatic discharge tube D3 are transient voltage suppression devices, specifically TVS diodes or ESD protection devices, used to suppress electrostatic interference in the signal and power paths of the microphone M1. The fourth capacitor C4 and the fifth capacitor C5 are filter capacitors, specifically ceramic capacitors or film capacitors, used to filter out power supply noise and high-frequency signal interference. In a specific example, the second power supply chip U6 can be a chip of model HP6020D4-25; the microphone M1 can be a sensor of model SPV6840.

[0051] Specifically, when the Hall sensor U4 detects that the hearing aid module 200 is placed in the charging case, its second enable output sends a control signal to the second enable terminal of the second power chip U6, triggering the second power chip U6 to supply power to the second power terminal of the pickup M1 through its fourth output. The external audio signal acquired by the pickup M1 is transmitted to the fourth capacitor C4 through the pickup output terminal. After filtering out high-frequency noise, the fourth capacitor C4 transmits the signal to the pickup input terminal of the DSP chip U3. The third electrostatic tube D3 and the fifth capacitor C5 connected to the second power terminal work together to suppress transient voltage fluctuations and radio frequency interference on the power line. The second electrostatic tube D2 is connected in parallel on the signal path to prevent electrostatic discharge from damaging the pickup M1 and the DSP chip U3.

[0052] Compared to existing technologies, current hearing aid pickup circuits typically employ independent power supply modules and discrete filtering components, resulting in complex circuit layouts and large space requirements. This solution integrates power control, electrostatic protection, and filtering functions into a compact pickup circuit. It utilizes the enable signal of Hall sensor U4 to synchronously control the power supply to the microphone M1, achieving efficient start / stop and signal protection of the pickup circuit without the need for additional physical buttons or independent control modules.

[0053] Through the above technical solution, this utility model solves the problem of power control and signal integrity of the pickup circuit under the condition of limited internal space in hearing aids. Through enable control and integrated protection design, it avoids the need for additional hardware expansion, ensures that the pickup M1 is automatically powered off when not in use, and effectively suppresses signal interference and electrostatic damage, thereby improving the audio acquisition quality and system reliability.

[0054] Example 3: Based on Embodiment 1 or Embodiment 2, this embodiment proposes a third embodiment of a low-power sleep trigger circuit to further describe the charging case module 100.

[0055] In such Figures 9-10 In one embodiment shown, the present invention proposes a main control module including a main control chip MCU, wherein the main control chip MCU is provided with a communication output terminal SHIP_CTL_L connected to the first positive contact CHL_DE.

[0056] In this embodiment, the main control chip MCU refers to the core integrated circuit that controls the operation of the charging case module 100. Specifically, it can be implemented using a microcontroller or a dedicated control chip, and is used to generate communication signals to control the hearing aid module 200 to enter the shipping mode. The communication output terminal refers to the physical interface of the main control chip MCU for outputting communication signals. Specifically, it can be implemented through GPIO pins or a dedicated communication interface, and is used to transmit communication signals to the first positive contact CHL_DE. The first positive contact CHL_DE is the conductive contact point between the charging case module 100 and the hearing aid module 200, and can be implemented using a metal spring or gold-plated contact, used to establish a physical connection between the main control chip MCU and the hearing aid module 200. In a specific example, the main control chip MCU can be a chip with the model number CX32L003_QFN20.

[0057] Specifically, when the hearing aid module 200 is placed in the charging case module 100, the main control chip MCU sends a pulse signal with a specific timing to the first positive contact CHL_DE through its communication output terminal. This signal is transmitted to the battery protection circuit 230 through the contact between the first positive contact CHL_DE and the second positive contact J1 of the hearing aid module 200. The main control chip MCU generates a communication signal that conforms to a preset duration and number of pulses through its built-in logic control unit, for example, it can generate a continuous pulse sequence that lasts longer than the detection delay of the battery protection circuit 230. Since the communication signal is directly output through the existing interface of the main control chip MCU, there is no need to add an additional dedicated communication module or signal generator, thus realizing the integration of signal transmission function within the charging case module 100.

[0058] Compared to existing technologies, traditional solutions typically require additional independent signal generation circuits or dedicated communication interface modules to transmit the shipping mode trigger signal. This not only occupies internal space but also increases hardware costs. This solution reuses the existing interface resources of the main control chip MCU, directly integrating the communication signal output function into the main control chip MCU. This avoids the space occupation of additional components and simplifies the circuit hierarchy.

[0059] Through the above technical solution, this utility model effectively solves the technical problem of transmitting the shipping mode trigger signal under the limited space of the charging compartment module 100. The main control chip MCU generates the required signal by directly controlling the communication output terminal, eliminating the need for an additional independent communication module. This maintains the compactness of the charging compartment structure while ensuring the reliability of signal transmission. After receiving the pulse signal from the main control chip MCU, the hearing aid module 200 can accurately identify and switch to shipping mode through the battery protection circuit 230, thereby achieving rapid activation of the low-power state.

[0060] In such Figure 11 In one embodiment shown, the present invention proposes a signal input circuit, including a trigger switch S1, an electrostatic diode D4, a sixth capacitor C6, and a fourth resistor R4; the first end of the trigger switch S1 is connected to the signal input terminal KEY of the main control chip MCU, the first end of the electrostatic diode D4, the first end of the sixth capacitor C6, and the first end of the fourth resistor R4; the second end of the trigger switch S1, the second end of the electrostatic diode D4, and the second end of the sixth capacitor C6 are all connected to the power ground; and the second end of the fourth resistor R4 is connected to the power supply of the charging case module 100.

[0061] In this embodiment, the electrostatic diode D4 is a transient voltage suppression device used to suppress electrostatic interference. Specifically, it can be implemented using a bidirectional TVS diode, connected in parallel across the trigger switch S1 to absorb high-voltage pulses generated by electrostatic discharge. The sixth capacitor C6 is a filter capacitor used to filter out high-frequency noise. Specifically, it can be implemented using a surface-mount ceramic capacitor, connected between the signal input terminal and ground to eliminate interference on the signal line. The fourth resistor R4 is a current-limiting resistor used to provide a pull-up level. Specifically, it can be implemented using a 10kΩ surface-mount resistor in a 0402 package, connected between the power supply and the signal input terminal to maintain a stable high-level state.

[0062] Specifically, when the user presses the trigger switch S1, the second terminal of the trigger switch S1 is connected to the power ground, and the signal input level is pulled low, forming a falling edge signal. The main control chip MCU detects this level change and triggers preset functions, such as controlling the charging case module 100 to send specific communication signals to the hearing aid. The electrostatic diode D4 absorbs the electrostatic discharge energy generated during operation, preventing damage to the main control chip MCU from transient high voltage. The sixth capacitor C6 filters out noise generated by contact bounce of the trigger switch S1 and environmental electromagnetic interference, ensuring the accuracy of signal detection. The fourth resistor R4 provides a stable pull-up voltage to the signal input terminal when the trigger switch S1 is not pressed, preventing the signal line from being in a floating state and causing false triggering.

[0063] Compared to existing technologies, traditional hearing aid charging cases typically require independent anti-shake circuits or complex filtering networks for their signal input circuits, leading to increased circuit area and cost. This solution achieves electrostatic protection and signal filtering functions with a single-layer PCB layout through the synergistic effect of the electrostatic diode D4 and the sixth capacitor C6. The pull-up design of the fourth resistor R4 further simplifies the level maintenance circuit structure. The overall solution significantly reduces the number of components while ensuring reliability.

[0064] Through the above technical solution, this utility model realizes the construction of a highly reliable user operation interface within a limited space, enabling the input of shipping mode trigger commands without the need for additional mechanical buttons or complex circuits. With a single button press, the user can send a specific timing communication signal from the charging case to the hearing aid, thereby controlling the hearing aid to enter low-power shipping mode, effectively solving the operational limitations of traditional devices that rely on external smart terminals or dedicated triggering devices.

[0065] Furthermore, this utility model's low-power sleep trigger circuit also includes a power supply circuit, which comprises a second battery, a voltage regulator chip, a power management chip, and an LDO chip. The voltage regulator chip is connected to an external power source, and the power management chip and LDO chip are connected to each other, used to convert the external power source into a regulated power supply and provide regulated power to the downstream circuitry. The power management chip is connected to the second battery, used to charge the second battery by outputting the regulated power supply and to control the discharge of the second battery. The LDO chip is connected to the second battery, used to step down the power supply from the second battery or the regulated power supply and output power to the main control module and signal input circuitry. In a specific example, the voltage regulator chip can be a WP1108-F28R chip; the power management chip can be an EAT9697 chip; and the LDO chip can be an HP6020D4-30 chip.

[0066] In this embodiment, the voltage regulator chip refers to an integrated circuit that performs AC-to-DC or DC voltage conversion. Specifically, it can be implemented using a low-dropout linear regulator or a switching regulator. Its function is to eliminate voltage fluctuations from the external power supply and provide a stable input for subsequent circuits. The power management chip refers to an integrated circuit with charge / discharge control functions. Specifically, it can be implemented using a chip with charging status detection and overvoltage protection. Its function is to precisely control the charging and discharging process of the second battery, preventing overcharging or over-discharging that could lead to battery life degradation. The LDO chip refers to a low-dropout linear regulator, specifically a low-power model with a quiescent current of less than 10μA. Its function is to convert a higher voltage to the lower voltage required by the system while reducing energy loss.

[0067] Specifically, when an external power source is connected, the voltage regulator chip converts the input AC or DC power into a DC regulated power supply with a set voltage value. This regulated power supply has two outputs: one output controls the second battery's constant current-constant voltage charging via a power management chip, and the other output is directly supplied to the LDO chip. When the external power source is disconnected, the power management chip automatically switches to battery discharge mode, supplying power from the second battery to the LDO chip. The LDO chip then steps down the received power voltage (whether from the voltage regulator chip or the second battery) to the operating voltage required by the main control module and signal input circuits, for example, reducing the 4.2V lithium battery voltage to a 3.3V system voltage. This three-level power supply architecture eliminates external power interference through the voltage regulator chip, protects the battery through the power management chip, and ensures that the core components of the system receive a precise and stable operating voltage through the LDO chip.

[0068] In some specific implementations, the voltage regulator chip can be an MP2315 switching regulator to convert a 12V input to a 5V regulated output; the power management chip can be a BQ24075 to control the maximum charging current of 500mA; and the LDO chip can be a TPS7A05 series to convert a 5V input to a 3.3V output. The second battery can be a 200mAh lithium polymer battery, which can withstand more than 500 charge-discharge cycles.

[0069] Compared to existing technologies, traditional hearing aid charging cases often use a single charging chip (U2) directly connected to the battery, lacking voltage regulation and power path management functions. This leads to voltage fluctuations during power switching, affecting the stability of the main control chip (MCU). This solution eliminates input power fluctuations by adding a voltage regulator chip, achieves intelligent charge / discharge switching through a power management chip, and provides secondary voltage regulation through an LDO chip, forming a three-stage power purification mechanism. This design achieves more reliable power management within the same volume, avoiding system resets or data loss problems caused by voltage instability in traditional designs.

[0070] Through the above technical solution, this invention achieves multiple power management functions under the constraint of miniaturized structure. By coordinating the voltage regulator chip, power management chip, and LDO chip, it ensures seamless switching between external power and battery power while guaranteeing high-precision regulated power supply to the system's core components. This integrated power architecture achieves complete power management functions without adding extra hardware modules, effectively solving the technical challenge of expanding power management circuits in hearing aid devices due to space limitations. Furthermore, the graded voltage regulation design controls system operating voltage fluctuations within ±2%, significantly improving the stability of device operation.

[0071] Example 4: Based on Embodiment 1, Embodiment 2, or Embodiment 3, this embodiment proposes a hearing aid, which includes: A pair of headphones; A charging case, wherein the charging case has a receiving space for accommodating the earphones, and the earphone plug is disposed in the receiving space; The hearing aid is also equipped with a low-power sleep trigger circuit, as in Embodiment 1, Embodiment 2, or Embodiment 3.

[0072] This invention transmits communication signals through the interface between the charging case module and the hearing aid module, triggering the battery protection circuit to cut off battery power and enter the shipping mode. It utilizes the existing interface to achieve low power consumption control, and has the advantages of enabling the hearing aid to quickly enter the shipping mode without adding physical buttons or dedicated communication components, and effectively extending the standby time of the device.

[0073] Compared to existing technologies, which typically require additional physical buttons or dedicated communication modules to trigger the shipping mode, this method utilizes the inherent interface contacts between the hearing aid and the charging case to transmit control signals, achieving mode switching through signal timing and logical judgment. This not only avoids the space limitations caused by hardware expansion but also improves operational reliability and anti-interference capabilities.

[0074] Through the above technical solution, this utility model solves the technical problem that hearing aids cannot quickly enter the shipping mode in a limited space, and achieves the effect of reliably triggering the low power consumption state without adding new hardware. At the same time, it avoids battery damage caused by misoperation during transportation or storage, and improves the user experience.

[0075] The algorithms or displays provided herein are not inherently related to any particular computer, virtual system, or other device. Furthermore, the embodiments of this invention are not directed to any particular programming language.

[0076] Numerous specific details are set forth in the specification provided herein. However, it will be understood that embodiments of the present invention may be practiced without these specific details. Similarly, for the sake of brevity and to aid in understanding one or more aspects of the invention, in the above description of exemplary embodiments of the invention, various features of the embodiments of the invention are sometimes grouped together in a single embodiment, figure, or description thereof. The claims, which follow the detailed description, are hereby expressly incorporated into that detailed description, wherein each claim itself constitutes a separate embodiment of the invention.

[0077] Those skilled in the art will understand that the modules in the device of the embodiment can be adaptively changed and placed in one or more devices different from that embodiment. Modules, units, or components in the embodiment can be combined into a single module, unit, or component, and further, they can be divided into multiple sub-modules, sub-units, or sub-components, except that at least some of such features and / or processes or units are mutually exclusive.

[0078] It should be noted that the above embodiments are illustrative of the present invention and not restrictive of it, and those skilled in the art can devise alternative embodiments without departing from the scope of the appended claims. In the claims, any reference signs placed between parentheses should not be construed as limiting the claims. The word "comprising" does not exclude the presence of elements or steps not listed in the claims. The word "a" or "an" preceding an element does not exclude the presence of a plurality of such elements. The present invention can be implemented by means of hardware comprising several different elements and by means of a suitably programmed computer. In the unit claims listing several means, several of these means may be embodied by the same item of hardware. The use of the words first, second, and third, etc., does not indicate any order. These words can be interpreted as names. The steps in the above embodiments, unless otherwise specified, should not be construed as limiting the order of execution.

Claims

1. A low-power sleep trigger circuit, characterized in that, The circuit includes: The charging case module includes a main control circuit and a first interface circuit, wherein the first interface circuit is connected to the main control circuit to transmit the communication signal output by the main control circuit; The device includes a hearing aid module, comprising a hearing aid circuit, a first battery, a second interface circuit, and a battery protection circuit. The first end of the second interface circuit is connected to the first interface circuit, and the second end of the second interface circuit is connected to the battery protection circuit to output a communication signal. The battery protection circuit is connected to the first battery and the hearing aid circuit. The battery protection module controls the on / off state of the first battery according to the communication signal, so that the hearing aid module enters the shipping mode.

2. The low-power sleep trigger circuit according to claim 1, characterized in that, The first interface circuit includes a first positive contact and a first negative contact, and the second interface circuit includes a second positive contact and a second negative contact; when the hearing aid module is placed into the charging case module, the first positive contact is connected to the second positive contact, and the first negative contact is connected to the second negative contact.

3. The low-power sleep trigger circuit according to claim 2, characterized in that, The battery protection circuit includes a battery protection chip, a first resistor, a second resistor, a third resistor, and a first capacitor; The battery protection chip is provided with a first input terminal, a first ground terminal and a first detection terminal. The first input terminal is connected to the first end of the first resistor and the first end of the first capacitor. The second end of the first resistor is connected to the positive terminal of the first battery. The second end of the first capacitor is connected to the negative terminal of the first battery and the first ground terminal. The first detection terminal is connected to the second positive contact in sequence through a second resistor and a third resistor.

4. The low-power sleep trigger circuit according to claim 3, characterized in that, It also includes a charging input module, which includes a charging chip, a first electrostatic tube, a second capacitor, and a third capacitor. The charging chip is provided with a second input terminal and a second output terminal. The second input terminal is connected to the second positive contact, the first end of the first electrostatic tube, and the first end of the second capacitor. The second output terminal is connected to the positive terminal of the first battery and the first end of the third capacitor. The second ends of the first electrostatic tube, the second end of the second capacitor, and the second end of the third capacitor are all connected to the power supply ground.

5. The low-power sleep trigger circuit according to claim 3, characterized in that, The hearing aid circuit includes a DSP chip, a Hall sensor, and a first power supply chip. The Hall sensor and the first power chip are connected to the positive terminal of the first battery to draw power; the first power chip has a first enable terminal and a third output terminal, and the first enable terminal is connected to the first enable output terminal of the Hall sensor to control the third output terminal to output power to the first power terminal of the DSP chip. The DSP chip also has a pickup input terminal and a power amplifier output terminal. The pickup input terminal is used to connect with a microphone to acquire external audio, and amplify the external audio before outputting it through a speaker connected to the power amplifier output terminal.

6. The low-power sleep trigger circuit according to claim 5, characterized in that, It also includes a pickup circuit, which includes a second power chip, a microphone, a second electrostatic tube, a third electrostatic tube, a fourth capacitor, and a fifth capacitor; The second power chip is connected to the positive terminal of the first battery to draw power, and the second power chip is provided with a second enable terminal and a fourth output terminal. The second enable terminal is connected to the second enable output terminal of the Hall sensor to control the fourth output terminal to output power to the second power terminal of the microphone. The pickup output terminal of the microphone is connected to the first terminal of the second electrostatic tube and the first terminal of the fourth capacitor. The second terminal of the fourth capacitor is connected to the pickup input terminal of the DSP chip. The second power supply terminal is also connected to the first terminal of the third electrostatic tube and the first terminal of the fifth capacitor. The second terminals of the second electrostatic tube, the third electrostatic tube, and the fifth capacitor are all connected to the power ground.

7. The low-power sleep trigger circuit according to claim 2, characterized in that, The main control circuit includes a main control chip, and the main control chip is provided with a communication output terminal connected to the first positive contact.

8. The low-power sleep trigger circuit according to claim 7, characterized in that, It also includes a signal input circuit, which includes a trigger switch, an electrostatic diode, a sixth capacitor, and a fourth resistor; The first end of the trigger switch is connected to the signal input terminal of the main control chip, the first end of the electrostatic diode, the first end of the sixth capacitor, and the first end of the fourth resistor. The second end of the trigger switch, the second end of the electrostatic diode, and the second end of the sixth capacitor are all connected to the power ground. The second end of the fourth resistor is connected to the power supply of the charging compartment module.

9. The low-power sleep trigger circuit according to claim 2, characterized in that, It also includes a power supply circuit, which includes a second battery, a voltage regulator chip, a power management chip, and an LDO chip; The voltage regulator chip is connected to an external power supply, a power management chip, and an LDO chip, and is used to convert the external power supply into a regulated power supply and provide regulated power to the back-end circuit. The power management chip is connected to the second battery and is used to output the regulated power supply to the second battery for charging and to control the second battery for discharging. The LDO chip is connected to the second battery and is used to step down the power supply or regulated power supply of the second battery and output power to the main control circuit and signal input circuit.

10. A hearing aid, characterized in that, include: A pair of headphones; A charging case, wherein the charging case has a receiving space for accommodating the earphones, and the earphone plug is disposed in the receiving space; The hearing aid is further provided with a low-power sleep trigger circuit as described in any one of claims 1-9.

Images