CN112073885A - Bone conduction hearing aid - Google Patents

Abstract

The application discloses bone conduction hearing aid, this bone conduction hearing aid includes: the interface is provided with a charging pin and a burning pin; the processing chip is connected with the burning pin and burns data through the burning pin so as to adjust parameters of the bone conduction hearing aid; the battery management module is connected with the charging pin; the battery is connected with the battery management module and used for supplying power to the bone conduction hearing aid; the battery management module is used for controlling the charging current of the battery. The interface with the charging pin and the burning pin is arranged, and the charging and burning functions of the bone conduction hearing aid are achieved at the same time.

Description

A bone conduction hearing aid

technical field

The present application relates to the field of hearing aids, in particular to a bone conduction hearing aid.

Background technique

Bone conduction hearing aids transmit sound waves through the human skull, bone labyrinth, inner ear lymph, auger, auditory nerve and auditory center by converting sound into mechanical vibrations of different frequencies. Bone conduction hearing aids use bone conduction technology to receive speech, close to the bone, and the sound waves are directly transmitted to the auditory nerve through the bone, so the ears can be opened without damaging the periosteum.

The bone conduction hearing aids in the prior art are usually powered by a button battery, which requires frequent battery replacement and is inconvenient to operate. On the other hand, bone conduction hearing aids require data programming and application programming. Usually, bone conduction hearing aids only have an interface for programming data.

SUMMARY OF THE INVENTION

In order to solve the above-mentioned technical problems in the prior art, a technical solution adopted in this application: a bone conduction hearing aid is provided, and the bone conduction hearing aid comprises:

Interface, with charging pins and programming pins;

The processing chip is connected to the programming pin, and the processing chip burns data through the programming pin to adjust the parameters of the bone conduction hearing aid;

The battery management module is connected to the charging pin;

The battery, connected with the battery management module, is used to supply power to the bone conduction hearing aid;

The battery management module is used to control the charging current of the battery.

Optionally, the interface is a TYPE-C interface, and the TX+ pin, TX- pin, RX+ pin and RX- pin of the TYPE-C interface are programming pins for programming data.

Optionally, the processing chip includes a first processing chip and a second processing chip, the I2C interface of the first processing chip is connected to the TX+ pin and the TX- pin, and the I2C interface of the second processing chip is connected to the RX+ pin and the RX- pin. The pins are connected to enable the first processing chip and the second processing chip to simultaneously program data.

Optionally, the battery is a fast-charging lithium battery, and the battery management module controls the charging current according to the voltage of the battery.

Optionally, the battery management module detects that the voltage of the battery is in the preset first voltage range, and controls the charging current to be the preset first current, so that the battery realizes fast charging; the battery management module detects that the voltage of the battery reaches the preset second voltage range. voltage, and control the charging current to decrease; the battery management module detects that the charging current reaches the preset second current, and controls the battery to stop charging.

Optionally, the bone conduction hearing aid further includes a voltage stabilizer for converting the output voltage of the battery into a voltage stabilized voltage; the input end of the voltage stabilizer is connected to the output end of the battery, and the output end of the voltage stabilizer is respectively connected to the first processor. The input end of the chip is connected to the input end of the second processing chip.

Optionally, the bone conduction hearing aid further comprises:

a power amplifier chip, the input end of the power amplifier chip is respectively connected with the output end of the first processing chip and the output end of the second processing chip, and is used for amplifying the audio signal of the first processing chip and the audio signal of the second processing chip;

The first speaker is connected to the output end of the power amplifier chip, and is used for outputting the audio signal of the first processing chip amplified and processed by the power amplifier chip;

The second speaker is connected to the output end of the power amplifier chip, and is used for outputting the audio signal of the second processing chip amplified and processed by the power amplifier chip.

Optionally, the bone conduction hearing aid further comprises:

a first microphone, connected to the input end of the first processing chip, and inputting the received audio signal to the first processing chip;

The second microphone is connected to the input end of the second processing chip, and inputs the received audio signal to the second processing chip.

Optionally, the interface further includes an identification pin for identifying the functional accessory, so that the bone conduction hearing aid is matched and connected with the functional accessory;

Bone conduction hearing aids further include:

Pull-down resistor, one end of the pull-down resistor is connected to the identification pin, and the other end of the pull-down resistor is grounded.

Optionally, the bone conduction hearing aid further includes a plurality of TVS tubes, one end of the TVS tubes is connected to the programming pin or the charging pin, and the other end of the TVS tubes is grounded for anti-static treatment.

The beneficial effects of the present application are: different from the prior art, the present application realizes the charging and programming functions of the bone conduction hearing aid by setting an interface including a charging pin and a burning pin, so that the charging operation of the bone conduction hearing aid can be achieved. It is convenient and simple; the interface realizes the charging function through the charging pin, and realizes the programming function through the programming pin, and realizes two functions by one interface.

Description of drawings

In order to illustrate the technical solutions in the embodiments of the present application more clearly, the following briefly introduces the drawings that are used in the description of the embodiments. Obviously, the drawings in the following description are only some embodiments of the present application. For those of ordinary skill in the art, other drawings can also be obtained from these drawings without creative effort.

1 is a schematic structural diagram of an embodiment of a bone conduction hearing aid of the present application;

2 is a schematic structural diagram of another embodiment of the bone conduction hearing aid of the present application;

Fig. 3 is the structural representation of the interface in Fig. 2;

FIG. 4 is a wiring definition diagram of the interface in FIG. 2 .

Detailed ways

In order for those skilled in the art to better understand the technical solutions of the present application, the bone conduction hearing aid provided by the present application will be described in further detail below with reference to the accompanying drawings and specific embodiments. It should be understood that the described embodiments are only a part of the embodiments of the present application, but not all of the embodiments. Based on the embodiments in the present application, all other embodiments obtained by those of ordinary skill in the art without creative efforts shall fall within the protection scope of the present application.

The terms "first", "second", etc. in this application are used to distinguish different objects, rather than to describe a specific order. Furthermore, the terms "comprising" and "having" and any variations thereof are intended to cover non-exclusive inclusion. For example, a process, method, system, product or device comprising a series of steps or units is not limited to the listed steps or units, but optionally also includes unlisted steps or units, or optionally also includes For other steps or units inherent to these processes, methods, products or devices.

Please refer to FIG. 1 , which is a schematic structural diagram of an embodiment of the bone conduction hearing aid of the present application. The bone conduction hearing aid 1 includes an interface 10 , a processing chip 20 , a battery management module 30 and a battery 40 .

The interface 10 is provided with a charging pin and a programming pin. Among them, the charging pin is used to supply power to the bone conduction hearing aid 1, and the programming pin is used to program data to adjust the parameters of the bone conduction hearing aid 1, thereby realizing the adaptation between the bone conduction hearing aid 1 and different users.

The processing chip 20 is connected to the interface 10 through programming pins, and programs with unique parameters are programmed through the programming pins. Optionally, the unique parameters may be parameters such as response frequency, sensitivity, signal-to-noise ratio, transient response, and distortion.

The battery management module 30 is connected to the interface 10 through the charging pin, and is used for receiving the input voltage, processing the input voltage, and controlling the charging current of the battery 40 , thereby realizing the charging of the battery 40 . Optionally, the input voltage received by the battery management module 30 is 5V. Optionally, the battery management module 30 in this embodiment may be a BQ24045 module, and in other embodiments, the battery management module 30 may be a battery management module of other types.

The battery 40 is connected to the battery management module 30 and the processing chip 20 respectively. When the battery 40 completes charging through the battery management module 30, the battery 40 stops charging. At the same time, the battery 40 outputs a voltage to the processing chip 20 to provide a working voltage for the processing chip 20 . Optionally, the output voltage of the battery 40 is 1.2V.

In this embodiment, the battery 40 is a fast-charged lithium battery, and the maximum current of the fast-charged lithium battery can reach 3C, where C is the total capacity of the battery. Compared with the ordinary rechargeable lithium battery, the maximum current is increased by 6-15 times. In this way, fast charging of the battery 40 is realized.

Specifically, the charging and discharging process of the battery 40 is as follows:

The battery management module 30 detects that the voltage of the battery 40 is in the preset first voltage range, and controls the charging current to be the preset first current, so that the battery 40 can be rapidly charged. At this time, the battery 40 is in the constant current charging stage, and the charging current is the first current;

The battery management module 30 detects that the voltage of the battery 40 reaches the preset second voltage, and controls the charging current to decrease. At this time, the battery 40 is in the stage of constant voltage charging, and the charging voltage is the second voltage;

The battery management module 30 detects that the charging current reaches the preset second current, and controls the battery 40 to stop charging.

Optionally, the first voltage range may be (0V-4.35V), the second voltage may be 4.35V, the first current may be 540mA, and the second current may be 27mA, that is, the working voltage of the battery 40 is 4.35V, and the cut-off The current is 27mA.

Referring to FIG. 2 in conjunction with FIG. 1 , FIG. 2 is a schematic structural diagram of another embodiment of the bone conduction hearing aid of the present application. The bone conduction hearing aid 1 further includes a voltage regulator 50 , a power amplifier chip 60 , a first speaker 71 , a second speaker 72 , a first microphone 81 and a second microphone 82 , and the processing chip 20 includes a first processing chip 21 and a second processing chip 22 .

The input end of the voltage stabilizer 50 is connected to the output end of the battery 40, and the output end of the voltage stabilizer 50 is respectively connected to the input end of the first processing chip 21 and the input end of the second processing chip 22 for converting the output voltage of the battery 40 into The regulated voltage is output to the first processing chip 21 and the second processing chip 22 to provide working voltages for the first processing chip 21 and the second processing chip 22 .

Since the working voltage of the battery 40 is 4.35V, that is, the output voltage of the battery 40 is 4.35V, and the working voltage of the first processing chip 21 and the second processing chip 22 is 1.2V, the output voltage of the battery 40 cannot be directly used as the first processing chip. The working voltages of the chip 21 and the second processing chip 22 are used, and need to be reduced in voltage. Therefore, in this embodiment, a voltage regulator 50 is provided at the output end of the battery 40 to perform step-down processing on the output voltage of the battery 40 .

The voltage stabilizer 50 in this embodiment is a low dropout linear voltage stabilizer, which can convert an input voltage of 4.35V into an output voltage of 1.2V, so that the output voltage can meet the working voltage of the first processing chip 21 and the second processing chip 22 need.

Optionally, the voltage stabilizer 50 in this embodiment may be a voltage stabilizer of the type NCP163AMX120TBG, and in other embodiments, the voltage stabilizer 50 may be a voltage stabilizer of other types.

The input terminals of the first processing chip 21 and the second processing chip 22 are respectively connected to the output terminals of the first microphone 81 and the second microphone 82 , and the output terminals of the first processing chip 21 and the second processing chip 22 are respectively connected to the input terminals of the power amplifier chip 60 . The output ends of the power amplifier chip 60 are connected to the input ends of the first speaker 71 and the second speaker 72 respectively. Optionally, the power amplifier chip 60 in this embodiment can be a MAX98306 chip, and in other embodiments, the power amplifier chip 60 can be a power amplifier chip of other types.

The first microphone 81 outputs the received audio signal to the first processing chip 21; the first processing chip 21 performs related algorithm processing on the audio signal, and outputs the processed audio signal to the power amplifier chip 60; The signal is amplified; the first speaker 71 outputs the audio signal amplified by the power amplifier chip 60 .

The second microphone 82 outputs the received audio signal to the second processing chip 22; the second processing chip 22 processes the audio signal with a related algorithm, and outputs the processed audio signal to the power amplifier chip 60; The signal is amplified; the second speaker 72 outputs the audio signal amplified by the power amplifier chip 60 .

Optionally, the bone conduction hearing aid 1 further includes a volume button (not shown) for adjusting the volume of the output audio signal.

Referring to FIG. 3-4 in conjunction with FIG. 2 , FIG. 3 is a schematic structural diagram of the interface in FIG. 2 , and FIG. 4 is a wiring definition diagram of the interface in FIG. 2 . The interface 10 in the embodiment of the present application is a TYPE-C interface, which is compatible with pins corresponding to the USB 3.0 protocol.

As shown in Figure 4, the USB3.0 protocol includes pins such as TX1+, TX1-, RX1+, RX1-, TX2+, TX2-, RX2+, RX2-, and VBUS. Among them, the TX1+ pin is connected with the TX2+ pin to form the TX+ pin; the TX1- pin is connected with the TX2- pin to form the TX- pin; the RX1+ pin is connected with the RX2+ pin to form the RX+ pin pin; the RX1-pin is connected with the RX2-pin to form the RX-pin. Specifically, the TX+ pin, TX- pin, RX+ pin and RX- pin correspond to the STXXP1 pin, SSTXN1 pin, SSRXP1 pin and SSRXN1 pin shown in FIG. 3 ; the VBUS pin corresponds to the pin shown in FIG. 3 . the VBUS0 pin.

In this embodiment, the interface 10 uses the TX+ pin, the TX- pin, the RX+ pin and the RX- pin as the programming pins of the TYPE-C interface, and the VBUS0 pin as the charging pin of the TYPE-C interface.

The interface 10 is respectively connected to the first processing chip 21 and the second processing chip 22, and the programming pins of the interface 10 are respectively connected to the I2C interfaces of the first processing chip 21 and the second processing chip 22, so that the first processing chip 21 and the I2C interface of the second processing chip 22 are respectively connected. The second processing chip 22 simultaneously writes data. Specifically, the I2C interface of the first processing chip 21 includes the SCL1 pin and the SAD1 pin, and the I2C interface of the second processing chip 22 includes the SCL2 pin and the SAD2 pin. The TX+ pin and the TX- pin are connected to the SCL1 pin and the SAD1 pin, and the RX+ pin and the RX- pin are connected to the SCL2 pin and the SAD2 pin.

In this implementation, the first processing chip 21 and the second processing chip 22 are specifically E7111 chips. The E7111 chip is highly sensitive to static electricity, so it is necessary to perform anti-static treatment on the E7111 chip. The bone conduction hearing aid 1 further includes a plurality of TVS tubes (transient diodes, Transient Voltage Suppressors), specifically a first TVS tube D1, a second TVS tube D2, a third TVS tube D3, a fourth TVS tube D4 and a fifth TVS tube D5.

As shown in Figure 3, one end of the first TVS tube D1 is connected to the SCL1 pin, one end of the second TVS tube D2 is connected to the SAD1 pin, one end of the third TVS tube D3 is connected to the SCL2 pin, and one end of the fourth TVS tube D4 is connected SAD2 pin, one end of the fifth TVS tube D5 is connected to the VBUS0 pin, and the other ends of the first TVS tube D1, the second TVS tube D2, the third TVS tube D3, the fourth TVS tube D4 and the fifth TVS tube D5 are grounded.

When a large-scale transient interference voltage or pulse current occurs in the circuit due to lightning and various electrical interference, the TVS tube quickly turns into a reverse conduction state in a very short time, and clamps the voltage of the circuit to the required In terms of safety value, it can effectively protect the precision components in the electronic circuit from damage. After the interference pulse passes, the TVS tube turns into the reverse cut-off state again. Since the clamping voltage of the TVS tube is lower than the maximum withstand voltage of the E7111 chip during reverse conduction, it has a protective effect on the E7111 chip.

As shown in FIG. 3 , the interface 10 further includes an identification pin CC1 for identifying the functional accessory, so that the bone conduction hearing aid 1 is matched and connected with the functional accessory. Optionally, the functional accessory may be an external burning device or the like.

The bone conduction hearing aid 1 further includes a pull-down resistor R1, one end of the pull-down resistor R1 is connected to the identification pin CC1, and the other end of the pull-down resistor R1 is grounded. Optionally, the resistance value of the pull-down resistor R1 is 5.1kΩ. In this embodiment, by setting a pull-down resistor R1 at one end of the identification pin CC1, the noise tolerance of the input signal of the bone conduction hearing aid 1 can be improved, and resistance matching can be performed at the same time to enhance the anti-interference ability.

In the present application, the charging and programming functions of the bone conduction hearing aid 1 are realized by setting the interface 10 including the charging pin and the programming pin, so that the charging operation of the bone conduction hearing aid 1 is convenient and simple; the interface 10 is realized by the charging pin. For the charging function, the programming function is realized through the programming pin, and two functions are realized by one interface, so there is no need to set up another charging interface, which reduces the cost.

The above are only the embodiments of the present application, and are not intended to limit the scope of the patent of the present application. Any equivalent structure or equivalent process transformation made by using the contents of the description and drawings of the present application, or directly or indirectly applied in other related technical fields, All are similarly included in the scope of patent protection of the present application.

Claims (10)

1. a bone conduction hearing aid, is characterized in that, comprises: Interface, with charging pins and programming pins; a processing chip, connected with the burning pins, and the processing chip burns data through the burning pins to adjust the parameters of the bone conduction hearing aid; a battery management module, connected to the charging pin; a battery, connected to the battery management module, for supplying power to the bone conduction hearing aid; The battery management module is used to control the charging current of the battery. 2. bone conduction hearing aid according to claim 1, is characterized in that, described interface is TYPE-C interface, the TX+ pin, TX- pin, RX+ pin and RX- pin of described TYPE-C interface For the programming pin, used for programming data. 3. The bone conduction hearing aid according to claim 2, wherein the processing chip comprises a first processing chip and a second processing chip, and the I2C interface of the first processing chip is connected to the TX+ pin and the TX- The I2C interface of the second processing chip is connected to the RX+ pin and the RX- pin, so that the first processing chip and the second processing chip can simultaneously burn data. 4 . The bone conduction hearing aid according to claim 1 , wherein the battery is a fast-charging lithium battery, and the battery management module controls the charging current according to the voltage of the battery. 5 . 5 . The bone conduction hearing aid according to claim 4 , wherein the battery management module detects that the voltage of the battery is in a preset first voltage range, and controls the charging current to be a preset first current, so as to 5 . Make the battery realize fast charging; the battery management module detects that the voltage of the battery reaches a preset second voltage, and controls the charging current to decrease; the battery management module detects that the charging current reaches a preset second voltage The second current controls the battery to stop charging. 6. The bone conduction hearing aid according to claim 1, characterized in that, the bone conduction hearing aid further comprises a voltage stabilizer for converting the output voltage of the battery into a voltage stabilized voltage; The input end of the voltage stabilizer is connected to the output end of the battery, and the output end of the voltage stabilizer is respectively connected to the input end of the first processing chip and the input end of the second processing chip. 7. The bone conduction hearing aid according to claim 6, wherein the bone conduction hearing aid further comprises: A power amplifier chip, the input end of the power amplifier chip is connected to the output end of the first processing chip and the output end of the second processing chip respectively, and is used for connecting the audio signal of the first processing chip and the second processing chip. The audio signal of the processing chip is amplified; a first speaker, connected to the output end of the power amplifier chip, for outputting the audio signal of the first processing chip amplified and processed by the power amplifier chip; The second speaker is connected to the output end of the power amplifier chip, and is used for outputting the audio signal of the second processing chip amplified and processed by the power amplifier chip. 8. The bone conduction hearing aid according to claim 7, wherein the bone conduction hearing aid further comprises: a first microphone, connected to the input end of the first processing chip, and outputting the received audio signal to the first processing chip; The second microphone is connected to the input end of the second processing chip, and outputs the received audio signal to the second processing chip. 9. The bone conduction hearing aid according to claim 8, wherein the interface further comprises identification pins for identifying functional accessories, so that the bone conduction hearing aid is matched and connected with the functional accessories; The bone conduction hearing aid further includes: A pull-down resistor, one end of the pull-down resistor is connected to the identification pin, and the other end of the pull-down resistor is grounded. 10. The bone conduction hearing aid according to claim 9, wherein the bone conduction hearing aid further comprises a plurality of TVS tubes, and one end of the TVS tubes is connected to the programming pin or the charging pin, so that the The other end of the TVS tube is grounded for anti-static treatment.

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