Implantable device, circuit board, power supply protection method, computer device and storage medium

Abstract

The invention provides implantable equipment, a circuit board, a power supply protection method, computer equipment and a storage medium, and relates to the technical field of medical instruments.The implantable equipment comprises an in-vitro device and an in-vivo device, and communication and power supply between the in-vitro device and the in-vivo device are achieved through near field communication. The in-vitro device comprises a display module, the in-vivo device comprises a plurality of magnetic detection antennas and a detection module, the detection module is used for acquiring the magnetic field intensity of each magnetic detection antenna, and the display module is used for displaying the magnetic field intensity. In the process that the user supplies power to the in-vivo device through the in-vitro device, display of the display module is used for indicating the user to move the in-vitro device to a preset charging area according to a preset rule. According to the invention, a traditional magnet design is canceled, a mutual inductance principle is adopted, a positioning indication path is provided for a user through the display module, accurate coil coupling alignment is rapidly realized during charging, and the power supply efficiency is greatly improved.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and particularly to an implantable device, a circuit board, a power supply protection method, a computer device, and a storage medium. Background Art

[0002] A wireless implantable device includes an external device and an internal device. Among them, the internal device is a medical electronic device implanted into the human body through surgery or minimally invasive means, with wireless communication capabilities and wireless charging capabilities.

[0003] The external device includes a transmitting coil, and the internal device includes a receiving coil. During wireless power supply, the current applied to the transmitting coil generates a magnetic field. When the transmitting coil and the receiving coil are aligned, the magnetic field induces a current in the receiving coil in the patient's body to provide charging electrical energy for the internal device.

[0004] Generally speaking, to reduce the surgical trauma and discomfort of patients, the volume of the internal device is small, which leads to a decrease in the coupling ability of the receiving coil and affects the charging efficiency. Summary of the Invention

[0005] The purpose of the present invention is to provide an implantable device, a circuit board, a power supply protection method, a computer device, and a storage medium to overcome the defect that the coupling ability of the receiving coil is reduced and the charging efficiency is affected.

[0006] In a first aspect, the present application proposes an implantable device, which includes: an external device and an internal device; Communication and power supply are achieved between the external device and the internal device through near-field communication; The external device includes a display module, The internal device includes a plurality of magnetic detection antennas and a detection module. The detection module is used to obtain the magnetic field intensity of each magnetic detection antenna, and the display module is used to display the magnetic field intensity; During the process of the user powering the internal device through the external device, the display of the display module is used to instruct the user to move the external device to a preset charging area according to a preset rule.

[0007] In one embodiment, the detection module includes a plurality of comparators; one comparator corresponds to two magnetic detection antennas; Each comparator is used to output the voltage difference between two magnetic detection antennas; Each voltage difference is used to characterize the magnetic field intensity.

[0008] In one embodiment, the display module includes a plurality of indicator lights; both the extracorporeal device and the intracorporeal device include a control module, and the control module of the intracorporeal device is configured to convert the analog signal of the voltage difference into a digital signal; the control module of the extracorporeal device is configured to convert the digital signal into a corresponding control signal according to a preset display logic; The display module displays the magnetic field strength, including: Each of the indicator lights is turned on or off according to the control signal.

[0009] In a second aspect, the present application provides a circuit board, on which the extracorporeal device according to any one of the first aspect is provided.

[0010] In one embodiment, the circuit board includes an antenna area and a component area, and the antenna area is arranged to surround the component area; the extracorporeal device includes a transmitting antenna and a plurality of functional modules; Wherein, the antenna area is used to accommodate the transmitting antenna, and the component area is used to accommodate the components corresponding to each functional module. In one embodiment, the circuit board is four-layered, and the antenna area is arranged on the top layer and the bottom layer of the circuit board; the component area is arranged on the top layer and the bottom layer of the circuit board; The middle two layers of the circuit board are used for wiring. In one embodiment, the transmitting antenna is arranged as a circular trace on the top layer and the bottom layer.

[0011] In one embodiment, the circular trace is four turns. In one embodiment, the line width of the circular trace is 0.15 mm ± 0.5 mm, and the line pitch of the circular trace is 0.15 mm ± 0.5 mm.

[0012] In one embodiment, the thickness of the middle two layers of the circuit board is 0.23 mm ± 0.5 mm.

[0013] In one embodiment, the distance between the outer circle of the component area and the inner circle of the antenna area is 2 mm ± 0.5 mm.

[0014] In a third aspect, the present application further provides a power supply protection method, which is applicable to the implantable device according to any one of the first aspect. The intracorporeal device includes a receiving antenna; the detection module is further configured to detect the current data of the receiving antenna and the temperature data of the intracorporeal device in real time; The control module of the extracorporeal device is further configured to adjust the transmission power according to the current data, the temperature data and a preset transmission logic.

[0015] In one embodiment, the determination method of the preset transmission logic includes: During the process of the external device supplying power to the internal device, comparing the real-time detected current data with a preset current threshold; If the current data is less than or equal to the preset current threshold, increasing the transmission power according to a first preset ratio; If the current data is greater than the preset current threshold, decreasing the transmission power according to a first preset ratio; If the temperature data is greater than or equal to a preset temperature threshold, decreasing the transmission power according to a second preset ratio. In one embodiment, the method further includes: When the user is in a moving state, multiplying a preset power value by a distance coefficient to obtain an initial transmission power and providing it to the internal device; wherein, the distance coefficient is obtained based on the distance between the external device and the internal device, and the moving state is determined based on the magnetic field intensity.

[0016] In a fourth aspect, the present application further provides a computer device. The computer device includes a memory and a processor. The memory stores a computer program, and when the processor executes the computer program, the method steps in the third aspect are implemented.

[0017] In a fifth aspect, the present application further provides a computer-readable storage medium. The computer-readable storage medium stores a computer program, and when the computer program is executed by a processor, the method steps in the third aspect are implemented.

[0018] The above-mentioned implantable device, circuit board, power supply protection method, computer device and storage medium have at least the following advantages: The implantable device of the present application includes an external device and an internal device, and communication and power supply are achieved between the external device and the internal device through near-field communication. The external device includes a display module, and the internal device includes a plurality of magnetic detection antennas and a detection module. The detection module is used to obtain the magnetic field intensity of each magnetic detection antenna, and the display module is used to display the magnetic field intensity. During the process of the user supplying power to the internal device through the external device, the display of the display module is used to instruct the user to move the external device to a preset charging area according to a preset rule. The present application cancels the traditional magnet design, adopts the mutual inductance principle, provides a positioning indication path for the user through the display module, quickly realizes accurate coil coupling alignment during charging, and greatly improves the power supply efficiency. BRIEF DESCRIPTION OF THE DRAWINGS

[0019] Figure 1 It is a schematic structural diagram of an implantable device in one embodiment; Figure 2Schematic diagram of the structure of the extracorporeal device in an embodiment; Figure 3 Schematic diagram of the connection of the magnetic detection antenna in an embodiment; Figure 4 Schematic diagram of a preset rule in an embodiment; Figure 5 Schematic diagram of the structure of the display module in an embodiment; Figure 6 Schematic diagram of the display logic in an embodiment; Figure 7 Schematic diagram of the structure of the circuit board in an embodiment; Figure 8 Flow schematic diagram of the judgment method steps of the transmission logic in an embodiment; Figure 9 Schematic diagram of the temperature rise of the overall power supply environment in an embodiment; Figure 10 Schematic diagram of the temperature rise of the in-vivo device in an embodiment; Figure 11 Internal structure diagram of a computer device in an embodiment. Detailed implementation manners

[0020] The following illustrates the embodiments of the present invention through specific specific examples. Those skilled in the art can easily understand other advantages and effects of the present invention from the content disclosed in this specification. The present invention can also be implemented or applied through other different specific implementation manners. Various details in this specification can also be modified or changed based on different viewpoints and applications without departing from the spirit of the present invention. It should be noted that, without conflict, the following embodiments and the features in the embodiments can be combined with each other.

[0021] For the purpose of illustration, some exemplary embodiments of the present invention are described. It should be understood that the present invention can be implemented in other ways not specifically shown in the drawings.

[0022] Please refer to Figure 1 , in an embodiment, the embodiment of the present application provides an implantable device, including: an extracorporeal device and an in-vivo device, and communication and power supply are realized between the extracorporeal device and the in-vivo device through near field communication (NFC).

[0023] Specifically, the external device includes a transmitting antenna, and the internal device includes a receiving antenna. Both the above-mentioned transmitting antenna and receiving antenna are NFC antennas, which are used for the communication and power supply of implantable devices. Further, the external device also includes multiple functional modules, such as a driving module, a modulation and demodulation module, a power supply module, a control module, etc.; among them, the driving module is used to amplify the signal or electric energy to be transmitted; the modulation and demodulation module is used to implement ASK / PSK modulation (transmission) and demodulation (reception); the power supply module is used to provide a stable working voltage for the external device; the control unit is used to control communication protocols, data processing, user interaction, etc.

[0024] Correspondingly, the internal device also includes multiple functional modules, such as an energy conversion module, a communication module, a control module, a battery, etc.; among them, the energy conversion module is used to convert the received RF energy into appropriate DC electric energy, the communication module is used to demodulate external signals and modulate data to be transmitted; the control module is used to process data; the battery is used to store DC electric energy and supply power to the entire internal device.

[0025] Please refer to Figure 2 , optionally, the external device further includes a display module, and the internal device further includes multiple magnetic detection antennas and a detection module. The magnetic detection antennas are used to locate the position or direction of the external device. In addition, the magnetic detection antennas can also be used for precise control; the detection module is used to obtain the magnetic field intensity of each magnetic detection antenna; the display module is used to display the magnetic field intensity. Exemplarily, in the embodiment of the present application, three magnetic detection antennas are provided, and each magnetic detection antenna is horizontally placed on the same plane and at the same distance from the external device. In addition, due to the small size of the magnetic detection antennas, there will be errors in magnetic induction detection. In the embodiment of the present application, the geometric spacing of each magnetic detection antenna in the horizontal direction on the above-mentioned plane is controlled at about 5 mm. By increasing the spacing of the magnetic detection antennas, the detection fluctuation error is eliminated and the detection accuracy is improved. It should be understood that the parameters such as the size, number of turns, and wire diameter of the above three magnetic detection antennas should be as close as possible.

[0026] Please refer to Figure 3 , optionally, the detection module includes multiple comparators, and one comparator corresponds to two magnetic detection antennas. The output of each comparator is the voltage difference between two magnetic detection antennas, and each voltage difference is used to characterize the magnetic field intensity.

[0027] Exemplarily, taking magnetic detection antenna 1 and magnetic detection antenna 2 as an example, the working principle of the comparator is described. As Figure 3As shown, the magnetic detection antenna 1 and the magnetic detection antenna 2 correspond to the comparator 1, and the comparator 1 finally outputs the voltage difference between the two magnetic detection antennas. It should be noted that before the magnetic detection antenna is connected to the comparator, it also needs to go through processes such as signal amplification, filtering, and rectification. After converting the AC signal of the magnetic detection antenna into a DC voltage signal, it is then connected to the comparator. Specifically in this embodiment, if it is desired that when the voltage of the magnetic detection antenna 1 is greater than the voltage of the magnetic detection antenna 2, the comparator outputs a high level, the magnetic detection antenna 1 should be connected to the non-inverting terminal of the comparator 1, and the magnetic detection antenna 2 should be connected to the inverting terminal of the comparator 2.

[0028] Furthermore, the larger the voltage value of a magnetic detection antenna, the stronger the magnetic field induced by the magnetic detection antenna. By gradually comparing the voltage values of each magnetic detection antenna, it is possible to know which magnetic detection antenna has the strongest magnetic field intensity, and the surrounding area of the position corresponding to this magnetic detection antenna is the optimal charging area.

[0029] During the process of the user powering the in-vivo device through the external device, the display module is used to indicate to the user to move the external device to the preset charging area according to a preset rule.

[0030] Please refer to Figure 4 , Figure 4 shown in the schematic diagram of the preset rule. Among them, the above-mentioned preset rule is determined in advance according to the connection method of the detection module and each magnetic detection antenna, as well as the placement positions of each magnetic detection antenna. Exemplarily, the three magnetic detection antennas are Figure 2 arranged in an L shape as shown in. It should be understood that in actual applications, the placement positions of each magnetic detection antenna can be adjusted according to the product size. The magnetic detection antenna 1 and the magnetic detection antenna 2 correspond to the comparator 1, and the magnetic detection antenna 1 is connected to the non-inverting terminal of the comparator 1, and the magnetic detection antenna 2 is connected to the inverting terminal of the comparator 1; the magnetic detection antenna 2 and the magnetic detection antenna 3 correspond to the comparator 2, and the magnetic detection antenna 2 is connected to the non-inverting terminal of the comparator 3, and the magnetic detection antenna 3 is connected to the inverting terminal of the comparator 3; the magnetic detection antenna 1 and the magnetic detection antenna 3 correspond to the comparator 3, and the magnetic detection antenna 1 is connected to the non-inverting terminal of the comparator 3, and the magnetic detection antenna 3 is connected to the inverting terminal of the comparator 3. For the convenience of description, the magnetic detection antennas 1-3 are respectively denoted as coils 1-3.

[0031] Please refer to Figure 5 and Figure 6 ,optionally, the display module includes multiple indicator lights. Exemplarily, in this embodiment of the application, four indicator lights are provided, and each indicator light is symmetrically arranged in the four directions of up, down, left, and right. Both the external device and the in-vivo device include a control module. The control module of the in-vivo device is used to convert the analog signal of the voltage difference into a digital signal; the control module of the external device is used to according to Figure 6The preset display logic shown converts digital signals into corresponding control signals. Among them, the preset display logic corresponds to the above-mentioned preset rules. Exemplarily, when indicator light 1 is on, it indicates that the output result of comparator 1 is high, that is, the voltage value of magnetic detection antenna 1 is higher than that of magnetic detection antenna 2. At this time, the magnetic field intensity of magnetic detection antenna 1 is greater than that of magnetic detection antenna 2.

[0032] According to Figure 6 the instructions provided in, by turning on or off each indicator light, the external device can be quickly moved to the preset charging area. If it is moved until all indicator lights are off, it means that the preset charging area has been reached.

[0033] It should be noted that in other embodiments, the display module can also use an LCD screen to display the above display logic.

[0034] The above-mentioned implantable device includes an external device and an internal device, and communication and power supply are achieved between the external device and the internal device through near-field communication. The external device includes a display module, and the internal device includes a plurality of magnetic detection antennas and a detection module. Among them, the detection module is used to obtain the magnetic field intensity of each magnetic detection antenna, and the display module is used to display the magnetic field intensity. During the process of the user powering the internal device through the external device, the display of the display module is used to instruct the user to move the external device to the preset charging area according to the preset rules. This application cancels the traditional magnet design and adopts the mutual inductance principle to provide a positioning indication path for the user, quickly realizing accurate coil coupling alignment during charging, and greatly improving the power supply efficiency.

[0035] Based on the same inventive concept, an embodiment of the present application also provides a circuit board, on which the external device involved in the above embodiment is provided.

[0036] Please refer to Figure 7 , optionally, the circuit board includes antenna area 1 and component area 2, and antenna area 1 is arranged around component area 2. Among them, antenna area 1 is used to accommodate the transmitting antenna, and component area 2 is used to accommodate the components corresponding to each functional module.

[0037] Optionally, the circuit board is four-layered. The top layer and the bottom layer are used to place components and conduct wiring, that is, the antenna area is arranged on the top layer and the bottom layer of the circuit board, and the component area is also arranged on the top layer and the bottom layer of the circuit board.

[0038] The middle two layers of the circuit board are used for wiring. Through vias, the wiring on the top layer and / or the bottom layer can extend to the middle two layers. By adopting the above scheme, the four-layer design can increase the spacing between the wiring of the transmitting antennas on the top layer and the bottom layer, thereby increasing the inductance value of the entire transmitting antenna and improving the power supply efficiency of the transmitting antenna.

[0039] Optionally, the transmitting antenna is arranged as a loop trace on the top layer and the bottom layer. By adopting the above solution, the wiring length of the transmitting antenna can be extended within a limited space, the inductance and coupling area of the transmitting antenna can be increased, thereby improving the induction ability. At the same time, the loop trace is arranged around the component area 2, that is, each component is placed inside the transmitting antenna, which can realize the miniaturization of the transmitting antenna. Since the more metal objects there are around the transmitting antenna, the more absorption of wireless power supply will be, resulting in attenuation of the transmitting power. Exemplarily, on the premise that the size of the circuit board is 2×10 mm, the loop trace is set to four turns, and the distance between the outer circle of the component area 2 and the inner circle of the antenna area 1 is set to 2 mm ± 0.5 mm, so as to avoid the efficiency reduction of the transmitting antenna due to the layout of the components. Further, on the premise that the size of the circuit board is 2×10 mm, through multiple tests, the line width of the loop trace is set to 0.15 mm ± 0.5 mm, and the line spacing of the loop trace is set to 0.15 mm ± 0.5 mm; the thickness of the middle two layers of the circuit board is set to 0.23 mm ± 0.5 mm, so as to achieve high transmitting power with a small size and meet the product use requirements.

[0040] For the above circuit board, the external device is arranged on the circuit board, and the circuit board is set to four layers to increase the distance between the top layer and the bottom layer, and at the same time maximize the line width of the transmitting antenna. The increased distance and line width can effectively increase the inductance value of the entire transmitting antenna within a limited space and improve the power supply efficiency.

[0041] Based on the same inventive concept, the embodiment of the present application also provides a power supply protection method, which is applicable to the implantable device involved in the above embodiment. The internal device includes a receiving antenna; the detection module is further configured to detect the current data of the receiving antenna and the temperature data of the internal device in real time.

[0042] The control module of the external device is further configured to adjust the transmitting power according to the current data, the temperature data and the preset transmitting logic.

[0043] Specifically, the current data of the receiving antenna is used to characterize the magnitude of the transmitting power of the external device. If the current data exceeds the preset current threshold, it is considered that the transmitting power is large and the transmitting power should be appropriately reduced; on the contrary, if the current data is less than the preset current threshold, it is considered that the transmitting power is small and the transmitting power can be appropriately increased. It should be understood that the above preset current threshold is determined according to the product model and battery capacity of the implantable device. In addition, the specific data of the preset current threshold is different in different charging stages. Further, the preset current threshold should have a certain range to allow a certain error range.

[0044] The heat of the implantable device mainly comes from the heat generated by the transmitting antenna and the receiving antenna, as well as the energy conversion of its own power consumption. During the charging and use of the in-vivo device, due to the small volume and poor heat dissipation ability of the in-vivo device, the temperature rise of the in-vivo device needs to be strictly controlled. Generally speaking, it should be ensured that the temperature of the in-vivo device during operation does not exceed the human tolerance temperature (42 °C) to prevent local tissue damage.

[0045] The detection module of the in-vivo device obtains the current data of the receiving antenna and the temperature data of the in-vivo device in real time and transmits them to the control module of the external device, so that the control module can adjust the transmission power in a timely manner according to the detection data during the power supply process.

[0046] Please refer to Figure 8 , optionally, the judgment method of the preset transmission logic includes: Step S802, during the power supply of the external device to the in-vivo device, compare the real-time detected current data with the preset current threshold.

[0047] Step S804, if the current data is less than or equal to the preset current threshold, increase the transmission power according to the first preset ratio.

[0048] Step S806, if the current data is greater than the preset current threshold, reduce the transmission power according to the first preset ratio.

[0049] Step S808, if the temperature data is greater than or equal to the preset temperature threshold, reduce the transmission power according to the second preset ratio.

[0050] Specifically, during the power supply process, the higher the transmission power, the faster the temperature rises. Therefore, both the transmission power and the temperature rise should be concerned at the same time. While ensuring the power supply efficiency, the safety of the user should also be ensured. Based on this, before charging, the safe charging current threshold and the received power threshold are determined in advance according to the battery capacity of the in-vivo device, the number of turns of the receiving antenna, and the temperature rise situation, as the preset current threshold and the preset power value. Based on the above preset current threshold, preset power value and actual measurement data, an adaptive charging strategy is executed.

[0051] It should be understood that the first preset ratio and the second preset ratio can be set according to actual needs. Exemplarily, the first preset ratio can be set to 10%, and the second preset ratio can be set to 15%. Further, the above first preset ratio and second preset ratio can be refined. For example, the preset temperature threshold is set to multiple ranges. If it exceeds 30 °C, it is reduced by 15%; if it exceeds 35 °C, it is reduced by 20%; if the temperature data is greater than 40 °C, it is immediately reduced by 50% to achieve precise control.

[0052] Optionally, during the power supply process, the temperature rise trend is also calculated based on the real-time acquired temperature data. If the rise trend exceeds the preset range within a certain period of time, it is considered that the charging is abnormal. At this time, the charging should be stopped immediately and the user should be reminded.

[0053] Exemplarily, at the initial stage of power supply, the preset power value is set to the maximum allowable power to supply power to the in-vivo device. After the connection between the extracorporeal device and the in-vivo device is stable, the transmission power is gradually reduced in a linearly decreasing manner. After detecting a decay in the received current during the subsequent power supply process, it switches to a fluctuating state, and the transmission power rises and falls with the rise and fall of the current at the receiving end. Among them, the connection being stable means that the extracorporeal device and the in-vivo device are already aligned.

[0054] In the above power supply protection method, during the power supply process, the changes in current and temperature are detected in real time, and the transmission power is adjusted in real time according to the changes to control the temperature rise, ensuring user safety while meeting the charging efficiency. Optionally, the above power supply protection method further includes: When the user is in a moving state, the preset power value is multiplied by a distance coefficient to obtain the initial transmission power and provided to the in-vivo device; wherein, the distance coefficient is obtained based on the distance between the extracorporeal device and the in-vivo device, and the moving state is determined based on the magnetic field strength.

[0055] Specifically, when the user is in a moving state, if an extracorporeal device is used to supply power to an in-vivo device, at this time, the magnetic detection antennas of the in-vivo device are in a jitter state, which will cause fluctuations in the magnetic field strength of each magnetic detection antenna, and the output value of the comparator will be abnormal, thereby causing a deviation in the alignment position of the extracorporeal device and affecting the transmission power. Based on this, the embodiments of the present application consider the overall power supply in combination with the distance factor.

[0056] Optionally, the initial transmission power of the embodiments of the present application is determined based on the preset power value and the distance coefficient, and the transmission power = preset power value × distance coefficient, and the distance coefficient = A × Lg (L / B); where A and B are both constants. Through multiple experiments, it is obtained that the value of A is approximately 0.3 ± 0.1, and the value of B is 6.2 ± 0.5; L is the distance between the extracorporeal device and the in-vivo device, which is measured in advance in the experiment. Generally speaking, for a fixed transmission power, as the distance increases, the coupling degree decreases, and the received voltage or received current of the receiving antenna will decrease; record the received voltage or received current corresponding to different distances under multiple transmission powers and establish a table. Subsequently, through the transmission power, the measured received voltage or received current, and querying the table, the distance value can be obtained. The distance coefficient is a value between 0 and 1. If this value is greater than 1, the implantable device will not work properly.

[0057] It should be noted that during the motion state, the alignment position may deviate, resulting in a reduction in power supply efficiency. The preset power value during the motion state is higher than the preset power value in the static state, for example, increased by 10%.

[0058] During the power supply process in the motion state, adjust the initial transmission power according to the current data of the receiving antenna and the temperature data of the in-vivo device.

[0059] Adopting the above solution, determine the user's usage state through the feedback of the magnetic detection coil, and then determine different power supply strategies according to the usage device, so as to achieve the highest efficiency of transmitting energy and the minimum energy converted into heat. Please refer to Figure 9 and Figure 10 , Figure 9 The figure shows the schematic diagram of the temperature rise of the power supply environment before improvement, Figure 10 The figure shows the schematic diagram of the temperature rise of the in-vivo device after improvement, and Figure 10 is obtained by measuring the implantable device and the circuit board provided in the above embodiment, and based on the adaptive power supply strategy provided in the above power supply protection method. Figure 9 In it, TX is the transmitting antenna and RX is the receiving antenna; the water temperature is the temperature of the human body fluid, which is used to calculate the energy carried away by the liquid. This water temperature will be used as a reference for calculating the absolute temperature rise.

[0060] After measurement, after increasing the spacing and line width, the inductance value of the transmitting antenna is increased from 0.9 μH to 1.3 μH, and the current-carrying capacity is increased by 50%. Further, after measurement, the overall power supply efficiency of the implantable device is also increased from about 8% in the case of the fixed power with conventional alignment to about 13% after adjustment, an increase of about 5%.

[0061] From Figure 9 it can be seen that the temperature rise of TX and RX relative to the water temperature before improvement is about 7°. From Figure 10 it can be seen that after improvement, the temperature rise of the upper surface shell and the side shell of the in-vivo device relative to the water temperature is maintained within 1.4 °C, effectively ensuring the safety of the user.

[0062] The above power supply protection method determines the user's usage status based on the feedback of the magnetic detection coil, and then determines different power supply strategies according to the usage device. If it is detected that the user is in a moving state, during the power supply process, the initial transmission power is determined based on the distance between the external device and the internal device to ensure the efficiency of transmitting energy while reducing the energy converted into heat. Further, during the power supply process, the changes in current and temperature are detected in real time, and the transmission power is adjusted in real time according to the changes to control the temperature rise, ensuring user safety while meeting the charging efficiency. It should be understood that although the steps in the flowcharts involved in the above-described embodiments are shown in sequence according to the arrows, these steps do not necessarily have to be executed in the order indicated by the arrows. Unless there is a clear description in this article, the execution of these steps does not have a strict order limit, and these steps can be executed in other orders. Moreover, at least some of the steps in the flowcharts involved in the above-described embodiments may include multiple steps or multiple stages. These steps or stages do not necessarily have to be executed at the same time, but can be executed at different times. The execution order of these steps or stages does not necessarily have to be sequential, but can be executed alternately or in turn with at least some of the steps or stages in other steps or other steps.

[0063] In a feasible embodiment, a computer device is provided. The computer device can be a terminal, and its internal structure diagram can be as Figure 11 shown. The computer device includes a processor, a memory, an input / output interface, a communication interface, a display unit, and an input device. Among them, the processor, the memory, and the input / output interface are connected through a system bus, and the communication interface, the display unit, and the input device are connected to the system bus through the input / output interface. Among them, the processor of the computer device is used to provide computing and control capabilities. The memory of the computer device includes a non-volatile storage medium and an internal memory. The non-volatile storage medium stores an operating system and a computer program. The internal memory provides an environment for the operation of the operating system and the computer program in the non-volatile storage medium. The input / output interface of the computer device is used to exchange information between the processor and external devices. The communication interface of the computer device is used to communicate with external terminals in a wired or wireless manner. The wireless manner can be achieved through WIFI, a mobile cellular network, NFC (Near Field Communication), or other technologies. When the computer program is executed by the processor, it implements the above power supply protection method. The display unit of the computer device is used to form a visually visible picture, which can be a display screen, a projection device, or a virtual reality imaging device. The display screen can be a liquid crystal display screen or an electronic ink display screen. The input device of the computer device can be a touch layer covering the display screen, or a button, a trackball, or a touchpad provided on the housing of the computer device, or an external keyboard, touchpad, or mouse, etc.

[0064] Those skilled in the art can understand that Figure 11 the structure shown in Figure 11 is only a block diagram of some structures related to the solution of this application, and does not constitute a limitation on the computer device to which the solution of this application is applied. The specific computer device may include more or fewer components than those shown in the figure, or combine some components, or have different component arrangements.

[0065] In a feasible embodiment, a computer device is provided, including a memory and a processor. A computer program is stored in the memory, and when the processor executes the computer program, the method steps in the above power supply protection method are implemented.

[0066] In a feasible embodiment, a computer-readable storage medium is provided, on which a computer program is stored, and when the computer program is executed by a processor, the method steps in the above power supply protection method are implemented.

[0067] In a feasible embodiment, a computer program product is provided, including a computer program, and when the computer program is executed by a processor, the method steps in the above power supply protection method are implemented.

[0068] Those of ordinary skill in the art can understand that all or part of the processes in the above-described embodiment methods can be completed by instructing relevant hardware through a computer program. The computer program can be stored in a non-volatile computer-readable storage medium. When the computer program is executed, it can include the processes of the above-described method embodiments. Among them, any reference to a memory, database, or other medium used in the embodiments provided in the present application can include at least one of non-volatile and volatile memories. Non-volatile memories can include read-only memory (ROM), magnetic tapes, floppy disks, flash memories, optical memories, high-density embedded non-volatile memories, resistive random access memories (ReRAM), magnetoresistive random access memories (MRAM), ferroelectric random access memories (FRAM), phase change memories (PCM), graphene memories, etc. Volatile memories can include random access memory (RAM) or external cache memories, etc. By way of illustration and not limitation, RAM can be in various forms, such as static random access memory (SRAM) or dynamic random access memory (DRAM), etc. The databases involved in the embodiments provided in the present application can include at least one of relational databases and non-relational databases. Non-relational databases can include distributed databases based on blockchain, etc., without limitation. The processors involved in the embodiments provided in the present application can be general-purpose processors, central processing units, graphics processing units, digital signal processors, programmable logic devices, data processing logics based on quantum computing, etc., without limitation.

[0069] The technical features of the above embodiments can be combined arbitrarily. For the sake of brevity of description, not all possible combinations of the technical features in the above embodiments are described. However, as long as there is no contradiction in the combination of these technical features, it should be considered to be within the scope described in this specification.

[0070] The above-described embodiments merely represent several implementation manners of the present application. Their descriptions are relatively specific and detailed, but they should not be construed as limiting the scope of the patent of the present application. It should be noted that for those of ordinary skill in the art, without departing from the concept of the present application, several modifications and improvements can still be made, and these all belong to the protection scope of the present application. Therefore, the protection scope of the present application should be subject to the appended claims.

Claims

1. An implantable device, characterized in that, The device includes: an external device and an internal device; Communication and power supply are achieved between the external device and the internal device through near-field communication; The external device includes a display module, The internal device includes a plurality of magnetic detection antennas and a detection module. The detection module is used to obtain the magnetic field intensity of each magnetic detection antenna, and the display module is used to display the magnetic field intensity; During the process of the user powering the internal device through the external device, the display of the display module is used to instruct the user to move the external device to a preset charging area according to a preset rule.

2. The implantable device according to claim 1, wherein The detection module includes a plurality of comparators; one comparator corresponds to two magnetic detection antennas; Each comparator is used to output the voltage difference between two magnetic detection antennas; Each voltage difference is used to characterize the magnetic field intensity.

3. The implantable device according to claim 2, wherein The display module includes a plurality of indicator lights; both the external device and the internal device include a control module. The control module of the internal device is used to convert the analog signal of the voltage difference into a digital signal; the control module of the external device is used to convert the digital signal into a corresponding control signal according to a preset display logic; The display module displays the magnetic field intensity, including: Each indicator light lights up or goes out according to the control signal.

4. A circuit board, characterized in that, The external device as described in any one of claims 1-3 is provided on the circuit board.

5. The circuit board according to claim 4, wherein The circuit board includes an antenna area and a component area, and the antenna area is arranged to surround the component area; the external device includes a transmitting antenna and a plurality of functional modules; Among them, the antenna area is used to accommodate the transmitting antenna, and the component area is used to accommodate the components corresponding to each functional module.

6. The circuit board according to claim 5, characterized in that, The circuit board is four-layer, and the antenna area is arranged on the top layer and the bottom layer of the circuit board; the component area is arranged on the top layer and the bottom layer of the circuit board; The middle two layers of the circuit board are used for wiring.

7. The circuit board according to claim 6, characterized in that, The transmitting antenna is arranged as a loop trace on the top layer and the bottom layer.

8. The circuit board according to claim 7, characterized in that, The loop trace is four turns.

9. The circuit board according to claim 7, wherein The line width of the loop trace is 0.15mm ± 0.5mm, and the line pitch of the loop trace is 0.15mm ± 0.5mm.

10. The circuit board according to claim 6, characterized in that, The thickness of the middle two layers of the circuit board is 0.23mm ± 0.5mm.

11. The circuit board according to claim 5, characterized in that, The distance between the outer circle of the component area and the inner circle of the antenna area is 2mm ± 0.5mm.

12. A power supply protection method, characterized in that, Applicable to the implantable device as described in any one of claims 1-3, the internal device includes a receiving antenna; the detection module is further used to detect the current data of the receiving antenna and the temperature data of the internal device in real time; The control module of the external device is further used to adjust the transmission power according to the current data, the temperature data and a preset transmission logic.

13. The method according to claim 12, wherein The judgment method of the preset transmission logic includes: During the process of the external device powering the internal device, comparing the current data detected in real time with a preset current threshold; If the current data is less than or equal to the preset current threshold, increase the transmission power according to a first preset ratio; If the current data is greater than the preset current threshold, the transmission power is reduced according to a first preset ratio; If the temperature data is greater than or equal to the preset temperature threshold, the transmission power is reduced according to a second preset ratio.

14. The method according to claim 12, wherein The method further includes: When the user is in a moving state, multiplying a preset power value by a distance coefficient to obtain an initial transmission power to supply power to the in-vivo device; wherein, the distance coefficient is obtained based on the distance between the ex-vivo device and the in-vivo device, and the moving state is determined based on the magnetic field strength.

15. A computer device, comprising a memory and a processor, the memory storing a computer program, characterized in that, When the processor executes the computer program, the steps of the method according to any one of claims 12-14 are implemented.

16. A computer-readable storage medium having a computer program stored thereon, characterized in that, When the computer program is executed by a processor, the steps of the method according to any one of claims 12-14 are implemented.

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