A wireless charging system, method, extracorporeal charging device, and storage medium

Abstract

The application provides a wireless charging system, method, extracorporeal charging device and storage medium, including an implantable medical device and an extracorporeal charging device, the implantable medical device contains a metal shell, and the wireless charging system further includes a control module and a temperature sensing module arranged on the inner surface of the metal shell; the control module is configured to: based on the real-time temperature data of the inner surface of the metal shell collected by the temperature sensing module, calculate the cumulative heat dose index of the equivalent temperature suffered by the tissue in a sampling period; based on the cumulative heat dose index and the preset safety threshold, adjust the transmission power of the extracorporeal charging device to constrain the cumulative heat dose index within the preset safety threshold; through the dynamic power adjustment based on the cumulative heat dose index, the limitation of the instantaneous temperature threshold is broken through on the premise that the thermal tolerance limit of the tissue is not broken through, the cooperative optimization of the charging efficiency and the tissue safety capacity is realized, and the charging continuity and the patient use experience are improved.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, and more particularly to a wireless charging system, method, external charging device, and storage medium. Background Technology

[0002] Currently, implantable neurostimulators combined with wireless power supply technology are widely used in the treatment of neurological diseases. By using an external transmitter to power or charge the device inside the body, the device's lifespan is significantly extended. However, the coil heating during wireless charging can cause the temperature of the implanted device's casing to rise. How to ensure charging efficiency while avoiding thermal damage to surrounding tissues is a key issue in thermal management in this field.

[0003] Currently, wireless charging thermal management typically employs a method based on instantaneous temperature threshold control. This method uses a temperature sensor module installed on the inner surface of the metal casing to monitor the temperature in real time. The control module compares the collected data with a preset threshold and instructs the external charging device to reduce power or suspend charging when the threshold is exceeded. The main drawback of this technical solution is that it relies on an instantaneous temperature threshold as the control basis, forcing frequent power reduction or charging interruptions when the temperature approaches the limit. This results in limited charging efficiency, discontinuous charging process, and a lack of flexibility and dynamic optimization capabilities in the charging strategy. Summary of the Invention

[0004] This application provides a wireless charging system, method, external charging device, and storage medium that, through dynamic power adjustment based on cumulative thermal dose index, overcomes the limitation of instantaneous temperature threshold while ensuring that the tissue thermal tolerance limit is not exceeded, thereby achieving synergistic optimization of charging efficiency and tissue safety capacity, and improving charging continuity and patient experience.

[0005] In a first aspect, embodiments of this application provide a wireless charging system, including an implantable medical device and an external charging device for wireless energy transfer with the implantable medical device. The implantable medical device includes a metal casing. The wireless charging system further includes a control module and a temperature sensing module disposed on the inner surface of the metal casing. The control module is configured to: Based on the real-time temperature data of the inner surface of the metal shell collected by the temperature sensing module, the cumulative heat dose index corresponding to the equivalent temperature of the tissue in the current sampling period is dynamically calculated. Based on the comparison between the cumulative heat dose index and the preset safety threshold, the transmission power of the external charging device is adjusted to constrain the cumulative heat dose index within the preset safety threshold.

[0006] Secondly, embodiments of this application also provide a wireless charging method, applied to the system described in any of the above claims, the method comprising: Based on the real-time temperature data of the inner surface of the metal shell collected by the temperature sensing module, the cumulative heat dose index corresponding to the equivalent temperature of the tissue in the current sampling period is dynamically calculated. Based on the comparison between the cumulative heat dose index and the preset safety threshold, the transmission power of the external charging device is adjusted to constrain the cumulative heat dose index within the preset safety threshold.

[0007] Thirdly, embodiments of this application also provide an external charging device for wireless power transmission to an implantable medical device. The external charging device includes a control module, and the implantable medical device includes a metal housing and a temperature sensing module disposed on the inner surface of the metal housing. The control module is configured to: Based on the real-time temperature data of the inner surface of the metal shell collected by the temperature sensing module, the cumulative heat dose index corresponding to the equivalent temperature of the tissue in the current sampling period is dynamically calculated. Based on the comparison between the cumulative heat dose index and the preset safety threshold, the transmission power of the external charging device is adjusted to constrain the cumulative heat dose index within the preset safety threshold.

[0008] Fourthly, embodiments of this application also provide a storage medium containing computer-executable instructions, which, when executed by a computer processor, are used to perform the functions of any control module as described in any embodiment of this application.

[0009] This application provides a wireless charging system. The method includes: an implantable medical device and an external charging device for wireless energy transmission with the implantable medical device. The implantable medical device includes a metal shell. The wireless charging system further includes: a control module and a temperature sensing module disposed on the inner surface of the metal shell. The control module is configured to: dynamically calculate the cumulative heat dose index corresponding to the equivalent temperature of the tissue in the current sampling period based on the real-time temperature data of the inner surface of the metal shell collected by the temperature sensing module; and adjust the transmission power of the external charging device based on the comparison result of the cumulative heat dose index and a preset safety threshold to constrain the cumulative heat dose index within the preset safety threshold. The technical solution of this application achieves wireless charging thermal management control based on the cumulative thermal dose index corresponding to real-time temperature data by dynamically calculating the index and constraining it within a preset safety threshold. This solves the problems of frequent charging interruptions, low efficiency, and rigid strategies caused by relying on instantaneous temperature thresholds. While ensuring the thermal safety of the implanted tissue, it breaks through the limitation that the outer surface of the device does not exceed the set temperature, improves the continuity and charging speed of the wireless charging process, and enhances the adaptability to different patients' usage habits through dynamic tracking of thermal dose accumulation and adaptive power adjustment, significantly optimizing charging efficiency and user experience. Attached Figure Description

[0010] To more clearly illustrate the technical solutions of the exemplary embodiments of this application, the accompanying drawings used in describing the embodiments are briefly introduced below. Obviously, the accompanying drawings described are only a portion of the embodiments to be described in this application, and not all of them. For those skilled in the art, other drawings can be obtained from these drawings without any creative effort.

[0011] Figure 1 This is a schematic diagram of an implantable neurostimulator provided in an embodiment of this application; Figure 2 This is a schematic diagram of a stimulation electrode involved in an embodiment of this application; Figure 3 The diagram shown is a schematic diagram of a wireless charging system provided in an embodiment of the present invention; Figure 4 This is a flowchart illustrating the functional implementation of the control module of the wireless charging system provided in an embodiment of the present invention. Figure 5 This is a flowchart illustrating the functional implementation of the control module of the wireless charging system provided in an embodiment of the present invention. Figure 6 The diagram shown is a schematic diagram of an external charging device provided in an embodiment of the present invention. Detailed Implementation

[0012] The present application will now be described in further detail with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative of the application and not intended to limit it. Furthermore, it should be noted that, for ease of description, the accompanying drawings show only the parts relevant to the present application, not the entire structure.

[0013] Before introducing this technical solution, we can first illustrate the application scenario. This technical solution can be applied to scenarios that require wireless charging control of implantable medical devices.

[0014] Below, we will first briefly describe one application area of ​​the embodiments of this application. An implantable neurostimulator, as a specific implantable medical device, mainly includes a stimulator implanted in the patient's body and a programmed device placed outside the patient's body. Existing neuromodulation technology mainly involves implanting electrodes at specific locations (i.e., target points) in the body through stereotactic surgery, and then having the stimulator implanted in the patient's body send discharge pulses to the target point via the electrodes, thereby modulating the electrical activity and function of the corresponding neural structures and networks, thereby improving symptoms and relieving pain. The stimulator can be any one of an implantable neurostimulation device, an implantable cardiac stimulation system (also known as a pacemaker), an implantable drug delivery system (IDDS), or a lead adapter. Implantable neurostimulation devices include deep brain stimulation (DBS), cortical nerve stimulation (CNS), spinal cord stimulation (SCS), sacral nerve stimulation (SNS), and vagus nerve stimulation (VNS).

[0015] In some embodiments, the stimulator may include an implantable pulse generator (IPG), electrode leads, and an extension lead disposed between the IPG and the electrode leads, enabling data interaction between the IPG and the electrode leads. The IPG is implanted within the patient's body. Responding to programmed commands from a programmable device, a power supply unit provides controllable electrical stimulation energy to the tissue, delivering one or two controllable electrical stimuli to specific areas of the tissue via the implanted extension lead and electrode leads. The extension lead, used in conjunction with the IPG, serves as a medium for transmitting electrical stimulation signals, conveying the signals generated by the IPG to the electrode leads. The electrode leads deliver electrical stimulation to specific areas of the tissue via their electrode contacts. The stimulator may have one or more electrode leads on one or both sides, with multiple electrode contacts on each lead.

[0016] In other embodiments, the stimulator may consist only of an electrical pulse stimulation device and electrode leads. In this case, the electrical pulse stimulation device may be embedded in the patient's skull, and the electrode leads may be implanted intracranially, with the electrical pulse stimulation device and electrode leads directly connected without the need for extension leads.

[0017] The electrode leads can be neurostimulation electrodes, delivering electrical stimulation to specific areas of tissue within the body via multiple electrode contacts. The stimulator has one or more electrode leads on one or both sides, each with multiple electrode contacts arranged uniformly or non-uniformly around the circumference of the lead. As an example, the electrode contacts can be arranged in a 4x3 array (a total of 12 contacts) around the circumference of the lead. The electrode contacts can serve as stimulation contacts and / or acquisition contacts. They can be in shapes such as sheets, rings, or dots.

[0018] In some possible approaches, the stimulated tissue can be the patient's brain tissue, and the stimulated site can be a specific area of ​​the brain tissue. Generally, the stimulated site differs depending on the patient's disease type, as well as the number of stimulation contacts (single-source or multi-source), the application of one or more specific electrical stimulation signals (single-channel or multi-channel), and the stimulation parameter data. It can be assumed that using multiple stimulation contacts (multi-source, multi-channel) will generate a larger amount of data compared to using a single-source, single-channel approach.

[0019] This application does not limit the applicable disease types, but can be any disease type applicable to deep brain stimulation (DBS), spinal cord stimulation (SCS), pelvic stimulation, gastric stimulation, peripheral nerve stimulation, or functional electrical stimulation. Among these, DBS can be used to treat or manage diseases including, but not limited to: spastic disorders (e.g., epilepsy), pain, migraines, mental illnesses (e.g., major depressive disorder (MDD)), bipolar disorder, anxiety disorders, post-traumatic stress disorder, mild depression, obsessive-compulsive disorder (OCD), behavioral disorders, mood disorders, memory disorders, mental state disorders, mobility disorders (e.g., essential tremor or Parkinson's disease), Huntington's disease, Alzheimer's disease, drug addiction, autism, or other neurological or psychiatric diseases and impairments.

[0020] The technical solutions provided in this embodiment of the invention are mainly applied to the field of implantable neurostimulation systems. A schematic diagram of the implantable neurostimulation system involved in this embodiment is shown below. Figure 1 ,like Figure 1 As shown, the implantable neurostimulation system mainly includes a battery module, a programming device, an electrical pulse stimulation device, stimulation electrodes, and electrode leads. The battery module receives and stores electrical energy emitted by an external power transmitter to power the programming device and the electrical pulse stimulation device. The electrical pulse stimulation device is implanted into the patient's body (e.g., in the chest cavity, skull, etc.). The electrode leads are connected to the electrical pulse stimulation device subcutaneously at one end, and the other end is equipped with a stimulation electrode. A schematic diagram of the stimulation electrodes can be found in [reference needed]. Figure 2 ,like Figure 2As shown, the stimulation electrode 1 includes at least one metal contact that outputs a stimulation source. These metal contacts can be circular rings 2 or directional electrodes 3 composed of multiple segmented electrode contacts. The stimulation electrode is partially implanted into a designated location in the patient's brain (such as nuclei or neural tissue associated with the condition). The doctor sends programming parameters to the electrical pulse stimulation device via a programming device. The electrical pulse stimulation device delivers electrical stimulation to at least one metal contact in the stimulation electrode through electrode wires, causing the at least one metal contact to generate an electric field to treat the corresponding condition.

[0021] During patient treatment using an implantable neurostimulation system, the device relies on a built-in battery module for power. During wireless charging, when the surface temperature of the casing reaches an instantaneous threshold, the system must forcibly pause charging to allow for cooling. This interruption directly impacts charging continuity and user experience. This invention proposes a charging strategy that dynamically and adaptively adjusts the transmission power by introducing a cumulative heat dose index as a control criterion. This strategy achieves a dynamic balance between charging efficiency and heat exposure levels while ensuring tissue thermal safety, effectively improving charging speed, reducing the frequency of overheating-related charging stoppages, and enhancing adaptability to different patients' charging habits. This significantly optimizes charging efficiency and user experience, while also helping to extend the device's battery life.

[0022] Example 1 This embodiment is applicable to situations requiring wireless charging control of implantable medical devices. Figure 3 The diagram shown is a schematic of a wireless charging system provided by an embodiment of the present invention, including an implantable medical device and an external charging device for wireless energy transmission with the implantable medical device. The implantable medical device includes a metal shell, and the wireless charging system further includes a control module and a temperature sensing module disposed on the inner surface of the metal shell.

[0023] Implantable medical devices refer to neurostimulators that are surgically implanted into the patient's body. They consist of a metal casing and rely on wireless power transmission for power or charging. External charging devices are located outside the patient's body and deliver electrical energy to the implantable medical device via wireless power transmission. Temperature sensing modules are sensing units located on the inner surface of the metal casing, used to collect real-time temperature data of the inner surface of the casing.

[0024] The control module is a logic processing unit that dynamically calculates the cumulative heat dose index based on temperature data collected by the temperature sensing module, and adjusts the transmission power of the external charging device according to the comparison result of this index with a preset safety threshold. It should be noted that the control module provided in this embodiment has multiple physical deployment methods: it can exist as a separate functional module completely independent of the external charging device and the implantable medical device, with its own independent hardware carrier and processing logic; it can also be integrated into the original controller of the external charging device, operating as a functional unit of that controller; or it can be integrated into the original controller of the implantable medical device, as part of the internal control architecture of the implantable device for embedded deployment.

[0025] This invention provides a wireless charging system that serves as an overall architecture for wireless power transmission to implantable medical devices. The system includes the implantable medical device and a paired external charging device. The implantable medical device is a neurostimulator surgically implanted into the body. Besides the various functional modules required for therapeutic functions, it also includes a battery module and has a metal casing. The external charging device is a device located outside the patient's body that wirelessly transmits electrical energy to the implantable medical device. The wireless charging system also includes a control module and a temperature sensing module. The temperature sensing module is located on the inner surface of the metal casing of the implantable medical device and is used to collect temperature data from the inner surface of the casing. The control module performs logic processing and power adjustment based on the data collected by the temperature sensing module.

[0026] Based on the above system structure, Figure 4 The flowchart illustrating the implementation function of the control module provided in this embodiment of the invention is as follows: Figure 4 As shown, the control module of the wireless charging system provided in this embodiment of the invention is configured to include the following steps: S110. Based on the real-time temperature data of the inner surface of the metal shell collected by the temperature sensing module, dynamically calculate the cumulative heat dose index corresponding to the equivalent temperature of the tissue in the current sampling period.

[0027] Real-time temperature data refers to the measured values ​​continuously collected and output by the temperature sensing module during wireless charging, reflecting the instantaneous temperature state of the inner surface of the metal casing. The current sampling period refers to a continuous and complete time window selected by the control module during dynamic calculation, used for centralized processing of temperature data within that period. The equivalent temperature experienced by the tissue is a value derived from the real-time temperature data, used to characterize the degree of thermal effect of that temperature on biological tissue.

[0028] The cumulative heat dose index is a quantitative result generated by the control module based on the equivalent temperature and duration of the tissue during the current sampling period. It is used to reflect the cumulative heat exposure level received by the tissue during this period.

[0029] Specifically, the control module uses each current sampling period as the time unit. Based on the real-time temperature data of the inner surface of the metal shell continuously collected by the temperature sensing module within the period, it converts the data into the equivalent temperature experienced by the tissue. Then, based on the value of the equivalent temperature and its duration within the sampling period, it performs cumulative calculations to generate a cumulative heat dose index corresponding to the sampling period.

[0030] For example, during wireless charging, the control module sets a current sampling period of 30 seconds. The temperature sensing module collects real-time temperature data of the inner surface of the metal shell every second and transmits it to the control module. The control module converts the real-time temperature data collected at each time point into the equivalent temperature experienced by the tissue. Assuming that the equivalent temperature experienced by the tissue is maintained at 38°C for the first 15 seconds and rises to 39°C for the next 15 seconds, the control module performs cumulative calculations based on the equivalent temperature value experienced by the tissue for each second within these 30 seconds and its corresponding duration, ultimately generating a cumulative heat dose index representing the total heat exposure of the tissue during these 30-second periods.

[0031] S120. Based on the comparison between the cumulative heat dose index and the preset safety threshold, adjust the transmission power of the external charging device to constrain the cumulative heat dose index within the preset safety threshold.

[0032] The preset safety threshold refers to a pre-set limit on the cumulative thermal dose index, designed to prevent thermal damage to the surrounding biological tissues. The transmission power refers to the power output of the external charging device when wirelessly transmitting energy to the implantable medical device. The control module adjusts the transmission power to control the intensity of wireless charging, thereby keeping the cumulative thermal dose index within the preset safety threshold.

[0033] Specifically, the control module compares the dynamically calculated cumulative heat dose index with a preset safety threshold. Based on the degree of deviation or proximity of the cumulative heat dose index from the preset safety threshold, it generates a corresponding power adjustment command. The external charging device increases, decreases, or stops its transmission power accordingly, thereby changing the intensity of wireless energy transmission, suppressing the upward trend of the cumulative heat dose index, or causing its value to drop. Ultimately, the cumulative heat dose index is always controlled within the allowable range defined by the preset safety threshold throughout the entire charging process.

[0034] For example, during wireless charging, the preset safety threshold set internally by the control module is a fixed value representing the upper limit of tissue safe heat exposure. When charging reaches a certain point, if the cumulative heat dose calculated by the control module has reached 90% of the preset safety threshold, the control module determines that the cumulative heat dose is close to the limit and immediately sends a command to the external charging device to adjust the transmission power from the initial full power to 70% of the full power. After the external charging device executes this adjustment command, the wireless energy transmission intensity decreases, the real-time temperature data growth rate of the inner surface of the metal casing slows down, the equivalent temperature of the tissue decreases accordingly, and the rate of increase of the cumulative heat dose decreases from 5 units per minute to 2 units per minute. When the cumulative heat dose falls back to 80% of the preset safety threshold, the control module compares again and fine-tunes the transmission power from 70% to 80% of the full power, so that the cumulative heat dose remains stable near the preset safety threshold and never exceeds it.

[0035] This application provides a wireless charging system, including an implantable medical device and an external charging device for wireless energy transmission with the implantable medical device. The implantable medical device includes a metal shell. The wireless charging system further includes a temperature sensing module and a control module disposed on the inner surface of the metal shell. The control module is configured to: dynamically calculate a cumulative heat dose index based on real-time temperature data collected by the temperature sensing module on the inner surface of the metal shell; and adjust the transmission power of the external charging device based on the comparison result of the cumulative heat dose index and a preset safety threshold, so as to constrain the cumulative heat dose index within the preset safety threshold. The technical solution of this application, by dynamically calculating the cumulative heat dose index corresponding to the real-time temperature data and constraining the index within the preset safety threshold, realizes wireless charging thermal management control based on the cumulative heat dose threshold. This solves the problems of frequent charging interruptions, low efficiency, and rigid strategies caused by relying on instantaneous temperature thresholds. While ensuring the thermal safety of the tissue surrounding the implant, it breaks through the limitation that the outer surface of the device does not exceed the set temperature, improves the continuity and charging speed of the wireless charging process, and enhances the adaptability to different patient usage habits through dynamic tracking and adaptive power adjustment of heat dose accumulation, significantly optimizing charging efficiency and user experience.

[0036] In this embodiment, optionally, the frequency at which the control module dynamically calculates the cumulative heat dose index based on real-time temperature data is variable. Specifically, it is configured to: update using a first calculation cycle within a preset duration during the initial charging phase or in the first stage where the cumulative heat dose index is lower than the first heat dose threshold; and switch to a second calculation cycle, which is shorter than the first calculation cycle, for updating in the second stage where the cumulative heat dose index exceeds the second heat dose threshold.

[0037] The initial charging preset duration refers to a pre-set time period after the wireless charging process begins, during which the control module uses a specific calculation frequency. The first heat dose threshold is a lower threshold value set to define the low-level stage of the cumulative heat dose index. The first calculation cycle refers to the time interval between each update of the cumulative heat dose index by the control module within the initial charging preset duration or in the first stage where the cumulative heat dose index is below the first heat dose threshold. The second heat dose threshold is a higher threshold value set to define the high-level stage of the cumulative heat dose index. The second calculation cycle refers to the time interval between a single update of the cumulative heat dose index, which is shorter than the first calculation cycle, switched to by the control module in the second stage where the cumulative heat dose index exceeds the second heat dose threshold.

[0038] In this embodiment, the control module can automatically adjust the calculation and update interval of the cumulative heat dose index according to the charging progress or the level of the cumulative heat dose index. Specifically, during the initial preset charging period after the wireless charging process starts, or when the cumulative heat dose index has not yet exceeded the lower threshold, i.e., the first heat dose threshold, and is in the first stage, the control module uses a longer time interval, i.e., the first calculation cycle, to periodically update the cumulative heat dose index; when the cumulative heat dose index rises and exceeds the higher threshold, i.e., the second heat dose threshold, and enters the second stage, the control module switches to a more frequent time interval, i.e., the second calculation cycle, to periodically update the cumulative heat dose index more frequently than the first calculation cycle.

[0039] For example, when wireless charging starts, the control module first enters a preset charging period of 5 minutes. During these 5 minutes, the control module updates the cumulative heat dose index using a first calculation cycle, i.e., once every 2 seconds. After the 5-minute initial charging period ends, the cumulative heat dose index is still below the first heat dose threshold, so the control module continues to update the index every 2 seconds in the first stage. As charging continues, the cumulative heat dose index gradually rises and exceeds the second heat dose threshold. At this point, the control module determines that it has entered the second stage and immediately switches the update frequency from once every 2 seconds in the first calculation cycle to once every 0.5 seconds in the second calculation cycle, which is shorter than the first calculation cycle, to more closely monitor the heat dose growth trend.

[0040] In this embodiment, optionally, the control module is also configured to: reset the cumulative heat dose index to zero at the start of a single charging session, and dynamically set a preset safety threshold based on the current thermal diffusion capacity of the target tissue.

[0041] A single charging session refers to the complete charging service cycle from the establishment of a wireless power transmission connection between the external charging device and the implantable medical device to the end of the charging process and disconnection. Target tissue refers to the biological tissue area surrounding the metal casing of the implantable medical device, in direct contact with or adjacent to the casing surface, that may be affected by heat due to temperature increases during wireless charging. Heat diffusion capability refers to the inherent physical property of the target tissue to conduct, disperse, and carry away locally accumulated heat to its surroundings; this property affects the rate of temperature rise and the rate of heat dose accumulation of the target tissue under the same heating conditions.

[0042] Specifically, resetting the cumulative heat dose index to zero at the start of a single charging session means that at the initial moment each time the external charging device establishes a wireless power transmission connection with the implantable medical device and starts the charging process, the control module resets the cumulative heat dose index calculated in the previous charging process to zero, so that the heat dose calculation for the current charging session starts from zero. Dynamically setting the preset safety threshold based on the target tissue's current heat dissipation capacity means that the control module adjusts and determines the preset safety threshold value applicable to this charging session in real time based on the target tissue's current heat conduction, blood perfusion, and other heat dissipation characteristics, ensuring that this threshold matches the actual heat exposure level that the target tissue can withstand.

[0043] Based on the above embodiments, the control module is configured to dynamically set a preset safety threshold according to the current thermal diffusion capacity of the target tissue in the following ways: (1) Based on the pre-established tissue thermal diffusion model and environmental parameters, assess the current heat dissipation status of the target tissue.

[0044] The tissue heat diffusion model refers to a pre-established mathematical framework used to describe the heat transfer and dissipation patterns of the target tissue under different conditions. Environmental parameters refer to various external factors affecting the heat dissipation capacity of the target tissue, including but not limited to tissue blood perfusion level, initial tissue temperature, and tissue thermal conductivity characteristics. Heat dissipation status refers to the qualitative category assigned by the control module after assessing the current heat dissipation capacity of the target tissue based on the tissue heat diffusion model and environmental parameters.

[0045] Specifically, the control module can call a pre-built tissue thermal diffusion model that can simulate the heat transfer and dissipation laws within the target tissue. At the same time, it can acquire various environmental parameters related to the heat dissipation capacity of the target tissue at the current moment, input these environmental parameters into the tissue thermal diffusion model for calculation, and finally obtain a qualitative or quantitative assessment result that characterizes the heat dissipation capacity of the target tissue under the current conditions, i.e., the current heat dissipation state of the target tissue.

[0046] (2) In response to an event that the heat dissipation state is high, the value of the preset safety threshold is increased accordingly.

[0047] Among them, the high heat dissipation state refers to the heat dissipation state category in which the evaluation results show that the target tissue has a strong heat conduction and dissipation ability and can withstand a high level of heat exposure.

[0048] Specifically, when the control module determines that the current heat dissipation state of the target organization is a high heat dissipation state, the control module adjusts the preset safety threshold applicable to this single charging session to a higher value based on the original benchmark value or the current value, so that the preset safety threshold matches the target organization's current strong heat dissipation capability.

[0049] (3) In response to an event that the heat dissipation state is low, the value of the preset safety threshold is reduced accordingly.

[0050] Among them, the low heat dissipation state refers to the heat dissipation state category in which the assessment results show that the target tissue has a weak ability to conduct and dissipate heat and is more sensitive to heat exposure.

[0051] In practical applications, when the control module determines that the current heat dissipation state of the target tissue is low based on the tissue heat diffusion model and environmental parameters, the control module will lower the value of the preset safety threshold for that single charging session from the original benchmark value or the current value to a lower value, so that the preset safety threshold can adapt to the target tissue's current weak heat diffusion ability.

[0052] In this way, by introducing a tissue thermal diffusion model and environmental parameters, the heat dissipation state of the target tissue is quantitatively evaluated, and the preset safety threshold is dynamically adjusted according to high or low heat dissipation states, ensuring that the preset safety threshold matches the actual thermal tolerance of the target tissue in real time. Appropriately increasing the preset safety threshold under high heat dissipation states avoids excessive limitation of transmission power due to overly strict threshold settings, thereby improving wireless charging efficiency. Actively decreasing the preset safety threshold under low heat dissipation states enhances thermal safety redundancy and prevents excessive heat dose accumulation due to poor tissue heat dissipation. This achieves an adaptive adjustment effect that maximizes charging performance while ensuring the safety of biological tissue.

[0053] Example 2 Based on the foregoing embodiments, this embodiment will provide a more detailed description of S110 and S120, and the specific implementation methods can be found in the technical solution of this embodiment. Technical terms that are the same as or corresponding to those in the above embodiments will not be repeated here.

[0054] Figure 5 The flowchart illustrating the implementation function of the control module provided in this embodiment of the invention is as follows: Figure 5 As shown, the control module of the wireless charging system provided in this embodiment of the invention is configured to include the following steps: S210. Based on real-time temperature data, determine the equivalent body surface temperature of the tissue within the current sampling period.

[0055] Equivalent body surface temperature refers to a standardized temperature value used to characterize the equivalent temperature experienced by the tissue under body surface conditions during the current sampling period.

[0056] Specifically, the control module converts the real-time temperature data of the inner surface of the metal shell collected by the temperature sensing module during the current sampling period into a standardized temperature value that represents the equivalent amount of temperature experienced by the tissue under body surface conditions during that period, through a preset conversion rule or correspondence. This equivalent body surface temperature is used for subsequent heat dose calculation.

[0057] In this embodiment, optionally, the control module is configured to determine the equivalent body surface temperature of the tissue equivalent temperature within the current sampling period by means of: (1) Obtain the real-time temperature measurement value that reflects the temperature state of the inner surface of the metal shell, which is collected by the temperature sensing module.

[0058] Among them, the real-time temperature measurement value refers to the raw value that the temperature sensing module collects and outputs during the actual wireless charging process, which directly reflects the instantaneous temperature of the inner surface of the metal shell.

[0059] Specifically, the control module can receive raw observation data from the temperature sensing module located on the inner surface of the metal shell of the implantable medical device. This data is generated by the module continuously detecting and converting the data during the wireless charging process, and is in the form of an electrical signal representing the instantaneous temperature of the inner surface of the metal shell. This data is the initial measurement result without compensation or correction.

[0060] (2) Based on the pre-calibrated thermal conductivity parameters of the shell and combined with the physical structure model of the metal shell, the real-time temperature measurement value is corrected by thermal conduction compensation to obtain the first temperature value.

[0061] Among them, the shell thermal conductivity parameter refers to the coefficient obtained in advance through experiments or simulation calibration, which describes the thermal conductivity characteristics of the metal shell material itself and the efficiency of heat transfer from the inner surface of the shell to the outer surface or tissue interface.

[0062] The first temperature value refers to the intermediate corrected temperature value, which is closer to the actual temperature of the outer surface of the metal shell or the contact surface of the tissue, calculated by the control module after correcting the real-time temperature measurement value based on the shell's thermal conductivity parameters and the physical structure model of the metal shell, and after compensating for the heat conduction path and heat loss.

[0063] In practical applications, the control module can call a shell thermal conductivity parameter obtained in advance through experimental calibration for the metal shell material and structure of the implantable medical device. At the same time, based on the physical structure model describing the geometry, wall thickness and heat conduction path of the metal shell, the control module can calculate and process the real-time temperature measurement value collected by the temperature sensing module to compensate for the heat loss and conduction delay in the process of heat transfer from the inner surface of the shell to the outer surface or tissue interface, thereby calculating a correction value that is closer to the actual tissue contact surface temperature. This correction value is the first temperature value.

[0064] (3) Based on the first temperature value, determine the equivalent body surface temperature used to characterize the state of the contact surface with human tissue within the current sampling period.

[0065] In this embodiment, the control module, after obtaining the first temperature value after thermal conduction compensation correction, takes the first temperature value as the core input and further processes it into a standard temperature output value that can represent the thermal state of the interface between the metal shell and human tissue in the current sampling period according to the preset conversion rules or mapping relationship. This output value is the equivalent body surface temperature value.

[0066] S220. Determine the corresponding temperature response coefficient based on the temperature range to which the equivalent body surface temperature belongs.

[0067] The temperature response coefficient refers to the coefficient used to quantify the difference in the cumulative contribution of different temperature levels to the heat dose.

[0068] Specifically, the control module pre-divides several continuous equivalent body surface temperature ranges, i.e., temperature intervals, and sets a corresponding temperature response coefficient for each temperature interval. After obtaining the equivalent body surface temperature of the current sampling period, the control module determines which predefined temperature interval the equivalent body surface temperature falls into, and then extracts and uses the temperature response coefficient associated with that temperature interval as the weighting weight for subsequent heat dose calculation.

[0069] S230. Based on the equivalent body surface temperature, the corresponding temperature response coefficient, and the duration of the current sampling period, calculate the unit heat dose increment corresponding to the current sampling period.

[0070] The unit heat dose increment refers to the dose value representing the increase in heat exposure within the current sampling period, calculated based on the equivalent body surface temperature, the temperature response coefficient corresponding to the equivalent body surface temperature, and the duration of the current sampling period.

[0071] Specifically, the control module can use the equivalent body surface temperature determined in the current sampling period, the temperature response coefficient corresponding to the temperature range to which the equivalent body surface temperature belongs, and the duration of the current sampling period itself as input factors. Through preset calculation rules, it can perform comprehensive calculations to finally generate a quantitative value representing the increase in heat exposure dose within the sampling period. This value is the unit heat dose increment.

[0072] S240. Update the cumulative heat dose index by adding the unit heat dose increment corresponding to the current sampling period to the historical cumulative value.

[0073] The historical cumulative value refers to the sum of all unit heat dose increments that have been accumulated up to the start of the current sampling period.

[0074] In this embodiment, at the end of each sampling period, the control module sums the unit heat dose increment calculated in that period with the historical cumulative value of the cumulative heat dose index accumulated from all previous sampling periods, and uses the summation result as the new cumulative heat dose index value at the current moment, thereby realizing continuous iteration and real-time refresh of the cumulative heat dose index.

[0075] For example, the formula for calculating the cumulative heat dose index can be expressed as: In the formula, Indicates the cumulative heat dose index; Indicates the ordinal number of the sampling period; Indicates the total number of sampling periods; Indicates the first Duration of each sampling period; Indicates the first The tissue equivalent temperature within each sampling period, that is, the equivalent body surface temperature obtained after thermal conduction compensation correction and conversion; This represents the temperature response coefficient determined based on the temperature range of the equivalent body surface temperature. It is used to reflect the influence of different temperature levels on the rate of thermal damage accumulation. When the temperature is greater than or equal to 43℃ The value is 0.5, when When the temperature is below 43℃ The value is 0.25.

[0076] S250. When the cumulative heat dose index is lower than the product of the first percentage threshold and the preset safety threshold, control the external charging device to increase the transmission power.

[0077] The first percentage threshold refers to a lower percentage limit of the preset safety threshold, used to determine whether the cumulative heat dose index is in the low range where the transmission power can be increased.

[0078] Specifically, the control module can compare the real-time updated cumulative heat dose index value with a comparison benchmark value, which is calculated by multiplying a preset safety threshold by a first percentage threshold less than one. If the cumulative heat dose index is less than the product result, the control module determines that the current heat dose accumulation level is within the safe range that allows for further increases in wireless energy transmission intensity, and accordingly sends an adjustment command to the external charging device, causing the external charging device to adjust its transmission power to a higher value.

[0079] S260. When the cumulative heat dose index reaches or exceeds the product of the second percentage threshold and the preset safety threshold, control the external charging device to reduce or suspend the transmission power.

[0080] The second percentage threshold refers to a higher percentage limit of the preset safety threshold, and this percentage value is greater than the first percentage threshold. It is used to determine whether the cumulative heat dose index has reached or exceeded the high level range that requires reducing or suspending the transmission power.

[0081] In practical applications, the control module can compare the updated cumulative heat dose index with a product limit obtained by multiplying a preset safety threshold by a second percentage threshold that is greater than the first percentage threshold. If the cumulative heat dose index is greater than or equal to the product limit, the control module determines that the current heat dose accumulation level has entered a high-risk range that requires active suppression of temperature rise, and accordingly sends an adjustment command to the external charging device to reduce its transmission power to a lower value, or, if necessary, reduce the transmission power to zero to completely suspend energy transmission.

[0082] Based on the above embodiments, optionally, when the external charging device pauses its transmission power, the control module is configured to: execute charging restart logic, specifically including: during the pause, continuously or periodically monitoring the real-time temperature data of the inner surface of the metal casing; when the real-time temperature data is lower than a preset activation temperature threshold, or the duration of the charging pause reaches a preset waiting time threshold, restarting the charging session; wherein, when restarting the charging session, the cumulative heat dose index is reset to zero.

[0083] The preset activation temperature threshold is a pre-set lower limit of temperature that the control module refers to during the period when the external charging device pauses its transmission power. It is used to determine whether the inner surface of the metal casing has cooled down to a level where charging can be safely resumed. The preset waiting time threshold is a pre-set lower limit of time that the control module refers to during the period when the external charging device pauses its transmission power. It is used to determine whether to forcibly restart the charging session based on the longest pause time if the temperature fails to drop below the preset activation temperature threshold in time.

[0084] Specifically, after the external charging device reduces its transmission power to zero due to the cumulative heat dose index reaching or exceeding the product of the second percentage threshold and the preset safety threshold, the control module enters a decision-making process to determine when to resume charging. This process includes: throughout the entire period of power transmission suspension, the control module continuously or periodically acquires and monitors the real-time temperature data of the inner surface of the metal casing collected by the temperature sensing module; when the monitoring result meets either of the following two conditions, i.e., the real-time temperature data is lower than the preset activation temperature threshold, or the accumulated time since the power transmission suspension reaches the preset waiting time threshold, the control module sends a command to the external charging device to restart the charging session; it should be noted that at the initial moment of restarting the charging session, the control module resets the previously accumulated heat dose index value to zero, so that the heat dose accumulation of this charging session is recalculated from zero.

[0085] Based on the above embodiments, optionally, when controlling the external charging device to reduce or pause the transmission power, the control module is configured to: execute charging termination judgment logic, specifically including: obtaining the current remaining power of the internal power supply of the implantable medical device; if the current remaining power exceeds a preset sufficient power threshold, controlling the external charging device to stop the current charging session and generating a charging completion prompt; if the current remaining power does not exceed the sufficient power threshold, continuing to perform the operation of reducing or pausing the transmission power.

[0086] The current remaining power refers to the real-time status parameter obtained by the control module from the internal power management unit of the implantable medical device, reflecting the energy capacity stored in the device's battery at the current moment. The preset sufficient power threshold is a pre-set lower limit value used to determine whether the stored power in the internal power supply of the implantable medical device is sufficient to support the device's continuous operation for a period of time as expected.

[0087] Among them, the charging completion prompt refers to the perceptible signal or notification issued by the wireless charging system to the patient or operator when the control module determines that the current remaining power has reached or exceeded the preset power sufficient threshold and decides to stop the current charging session, indicating that the charging is full and the current charging session has officially ended.

[0088] In practical applications, when the external charging device reduces or pauses its transmission power, the control module reads the real-time remaining power level of the implantable medical device's battery from its power management unit. If the remaining power exceeds a preset sufficient power threshold, the control module determines that the implantable medical device has sufficient power and does not need to continue charging. It then sends a termination command to the external charging device, stopping the charging session and disconnecting the wireless power transmission connection. Simultaneously, it generates a charging completion notification to inform the user that charging has ended. If the remaining power does not exceed the preset sufficient power threshold, the control module determines that the device's power is still insufficient and charging cannot be terminated. Therefore, the external charging device continues to reduce or pause its transmission power until the restart conditions are met, at which point it will attempt to resume charging.

[0089] In this embodiment, as an optional embodiment, the power consumption curve of the internal power supply can be predicted based on the treatment program parameters pre-stored in the implantable medical device; the expected time point when the power is expected to drop to the minimum working threshold can be calculated based on the current remaining power and the power consumption curve; and the time point can be used as a suggested next charging time for reminder.

[0090] In other words, the control module reads the treatment program parameters pre-stored in the implantable medical device's memory, which specify the treatment output plan, including stimulation intensity, frequency, and pulse width. Based on these parameters, it analyzes and predicts the discharge rate and power reduction trend of the internal power supply over a future period, generating a curve describing the power consumption curve as the power level decreases over time. Based on the current remaining power and the power consumption curve, it calculates the expected time when the power level will drop to the minimum operating threshold. This means the control module fits the current remaining power value to the power consumption curve to estimate the future time when, under the current treatment program parameters, the internal power supply's power level will drop to the minimum operating threshold required to maintain the device's basic functions. Presenting this time as a suggested next charging time means the control module presents this calculated future time to the patient or operator in a perceptible notification format as a reference time to initiate the next wireless charging cycle before that time.

[0091] The technical solution of this application, when dynamically calculating the cumulative heat dose index, introduces an equivalent body surface temperature as a standardized measure of tissue thermal exposure and dynamically matches the corresponding temperature response coefficient according to its temperature range. This allows the calculation of unit heat dose increment to accurately reflect the nonlinear differences in the contribution of different temperature levels to the cumulative thermal damage of biological tissues. Based on this, the unit heat dose increment calculated in each sampling period is successively accumulated to the historical cumulative value, achieving continuous and high-precision iterative updates of the cumulative heat dose index. Thus, the control module can track the heat dose accumulation process of the tissue in real time and quantitatively throughout the charging process, providing an accurate and reliable data foundation for subsequent transmission power adjustment based on the comparison results of the cumulative heat dose index and the preset safety threshold. This maximizes the power potential of the wireless charging system while strictly adhering to the CEM43 cumulative heat dose safety standard.

[0092] The technical solution of this application embodiment adjusts the transmission power of the external charging device in the following way: setting a first percentage threshold and a second percentage threshold, and constructing a dual-threshold power adjustment range with hysteresis characteristics within a preset safety threshold. When the cumulative heat dose index is lower than the product of the first percentage threshold and the preset safety threshold, the transmission power is actively increased, which can fully release the charging performance when the heat dose reserve is sufficient and shorten the charging time; when the cumulative heat dose index reaches or exceeds the product of the second percentage threshold and the preset safety threshold, the transmission power is promptly reduced or suspended, which can actively suppress the temperature rise when the heat dose is close to the limit and prevent tissue thermal damage. The adjustment dead zone formed between the first percentage threshold and the second percentage threshold effectively avoids frequent fluctuations in the transmission power near the critical point, making the power adjustment process smooth and orderly, and achieving synergistic optimization of charging efficiency and thermal safety while ensuring the safety of biological tissues.

[0093] Example 3 This application provides a wireless charging method, which is applicable to various situations requiring wireless charging control of implantable medical devices. The wireless charging method provided by this invention includes the following steps: S310. Based on the real-time temperature data of the inner surface of the metal shell collected by the temperature sensing module, dynamically calculate the cumulative heat dose index corresponding to the equivalent temperature of the tissue within the current sampling period.

[0094] Specifically, the control module uses each current sampling period as the time unit. Based on the real-time temperature data of the inner surface of the metal shell continuously collected by the temperature sensing module within the period, it converts the data into the equivalent temperature experienced by the tissue. Then, based on the value of the equivalent temperature and its duration within the sampling period, it performs cumulative calculations to generate a cumulative heat dose index corresponding to the sampling period.

[0095] S320. Based on the comparison between the cumulative heat dose index and the preset safety threshold, adjust the transmission power of the external charging device to constrain the cumulative heat dose index within the preset safety threshold.

[0096] Specifically, the control module compares the dynamically calculated cumulative heat dose index with a preset safety threshold. Based on the degree of deviation or proximity of the cumulative heat dose index from the preset safety threshold, it generates a corresponding power adjustment command. The external charging device increases, decreases, or stops its transmission power accordingly, thereby changing the intensity of wireless energy transmission, suppressing the upward trend of the cumulative heat dose index, or causing its value to drop. Ultimately, the cumulative heat dose index is always controlled within the allowable range defined by the preset safety threshold throughout the entire charging process.

[0097] This application provides a wireless charging method applied to a wireless charging system. The wireless charging system includes an implantable medical device and an external charging device for wireless energy transfer with the implantable medical device. The implantable medical device includes a metal shell, and the wireless charging system further includes a temperature sensing module disposed on the inner surface of the metal shell. The method includes: dynamically calculating a cumulative heat dose index based on real-time temperature data of the inner surface of the metal shell collected by the temperature sensing module; and adjusting the transmission power of the external charging device based on the comparison result of the cumulative heat dose index and a preset safety threshold to constrain the cumulative heat dose index within the preset safety threshold. The technical solution of this application achieves wireless charging thermal management control based on the cumulative thermal dose index corresponding to real-time temperature data by dynamically calculating the index and constraining it within a preset safety threshold. This solves the problems of frequent charging interruptions, low efficiency, and rigid strategies caused by relying on instantaneous temperature thresholds. While ensuring the thermal safety of the implanted tissue, it breaks through the limitation that the outer surface of the device does not exceed the set temperature, improves the continuity and charging speed of the wireless charging process, and enhances the adaptability to different patients' usage habits through dynamic tracking of thermal dose accumulation and adaptive power adjustment, significantly optimizing charging efficiency and user experience.

[0098] Example 4 Figure 6The diagram shows an external charging device provided in an embodiment of the present invention. The external charging device is used to wirelessly transmit energy to an implantable medical device. The external charging device includes a control module. The implantable medical device includes a metal shell and a temperature sensing module disposed on the inner surface of the metal shell. The control module is configured to: dynamically calculate the cumulative thermal dose index corresponding to the equivalent temperature of the tissue in the current sampling period based on the real-time temperature data of the inner surface of the metal shell collected by the temperature sensing module; and adjust the transmission power of the external charging device based on the comparison result of the cumulative thermal dose index and a preset safety threshold to constrain the cumulative thermal dose index within the preset safety threshold.

[0099] The external charging device provided in this application embodiment is used for wireless power transmission to implantable medical devices, delivering electrical energy to the implanted medical devices in a non-contact manner to maintain their operation. The external charging device integrates a control module responsible for logic operations and command issuance. The implantable medical device includes a metal shell and a temperature sensing module disposed on the inner surface of the metal shell. In specific applications, the control module can continuously calculate the quantified value of the cumulative heat effect on biological tissue within the currently set time sampling interval, based on the temperature value of the inner surface of the metal shell transmitted in real time by the temperature sensing module, through calculation. Furthermore, the control module can compare the cumulative heat dose index calculated in real time with a preset safety limit, and dynamically adjust the wireless energy emission intensity of the external charging device according to the difference, so that the actual cumulative heat dose index is always controlled within the preset safety limit range, avoiding tissue overheating damage caused by the wireless charging process.

[0100] The technical solution of this application achieves wireless charging thermal management control based on the cumulative thermal dose index corresponding to real-time temperature data by dynamically calculating the index and constraining it within a preset safety threshold. This solves the problems of frequent charging interruptions, low efficiency, and rigid strategies caused by relying on instantaneous temperature thresholds. While ensuring the thermal safety of the implanted tissue, it breaks through the limitation that the outer surface of the device does not exceed the set temperature, improves the continuity and charging speed of the wireless charging process, and enhances the adaptability to different patients' usage habits through dynamic tracking of thermal dose accumulation and adaptive power adjustment, significantly optimizing charging efficiency and user experience.

[0101] Example 5 This application embodiment also provides a storage medium containing computer-executable instructions, which, when executed by a computer processor, are used to perform the functions of a control module of a wireless charging system. The wireless charging system includes an implantable medical device and an external charging device for wireless energy transfer with the implantable medical device. The implantable medical device includes a metal housing. The wireless charging system further includes a control module and a temperature sensing module disposed on the inner surface of the metal housing. The control module is configured to: Based on the real-time temperature data of the inner surface of the metal shell collected by the temperature sensing module, the cumulative heat dose index corresponding to the equivalent temperature of the tissue in the current sampling period is dynamically calculated. Based on the comparison between the cumulative heat dose index and the preset safety threshold, the transmission power of the external charging device is adjusted to constrain the cumulative heat dose index within the preset safety threshold.

[0102] The computer storage medium in this application embodiment can be any combination of one or more computer-readable media. A computer-readable medium can be a computer-readable signal medium or a computer-readable storage medium. A computer-readable storage medium can be, for example,—but not limited to—an electrical, magnetic, optical, electromagnetic, infrared, or semiconductor system, apparatus, or device, or any combination thereof. More specific examples of computer-readable storage media (a non-exhaustive list) include: an electrical connection having one or more wires, a portable computer disk, a hard disk, random access memory (RAM), read-only memory (ROM), erasable programmable read-only memory (EPROM or flash memory), optical fiber, portable compact disk read-only memory (CD-ROM), optical storage device, magnetic storage device, or any suitable combination thereof. In this document, a computer-readable storage medium can be any tangible medium that contains or stores a program that can be used by or in conjunction with an instruction execution system, apparatus, or device.

[0103] Computer-readable signal media may include data signals propagated in baseband or as part of a carrier wave, carrying computer-readable program code. Such propagated data signals may take various forms, including but not limited to electromagnetic signals, optical signals, or any suitable combination thereof. Computer-readable signal media may also be any computer-readable medium other than computer-readable storage media, capable of sending, propagating, or transmitting programs for use by or in connection with an instruction execution system, apparatus, or device.

[0104] Program code contained on a computer-readable medium may be transmitted using any suitable medium, including—but not limited to—wireless, wire, optical fiber, RF, etc., or any suitable combination thereof.

[0105] Computer program code for performing the operations of the embodiments of this application can be written in one or more programming languages ​​or a combination thereof. Programming languages ​​include object-oriented programming languages—such as Java, Smalltalk, and C++—and conventional procedural programming languages—such as C or similar programming languages. The program code can be executed entirely on the user's computer, partially on the user's computer, as a standalone software package, partially on the user's computer and partially on a remote computer, or entirely on a remote computer or server. In cases involving remote computers, the remote computer can be connected to the user's computer via any type of network—including a local area network (LAN) or a wide area network (WAN)—or can be connected to an external computer (e.g., via the Internet using an Internet service provider).

[0106] Note that the above description is merely a preferred embodiment and the technical principles employed in this application. Those skilled in the art will understand that this application is not limited to the specific embodiments described herein, and various obvious changes, readjustments, and substitutions can be made without departing from the scope of protection of this application. Therefore, although this application has been described in detail through the above embodiments, this application is not limited to the above embodiments. Many other equivalent embodiments may be included without departing from the concept of this application, and the scope of this application is determined by the scope of the appended claims.

Claims

1. A wireless charging system, comprising an implantable medical device and an external charging device for wireless power transmission with the implantable medical device, wherein the implantable medical device includes a metal housing, characterized in that, The wireless charging system further includes: a control module and a temperature sensing module disposed on the inner surface of the metal housing, wherein the control module is configured to: Based on the real-time temperature data of the inner surface of the metal shell collected by the temperature sensing module, the cumulative heat dose index corresponding to the equivalent temperature of the tissue in the current sampling period is dynamically calculated. Based on the comparison between the cumulative heat dose index and the preset safety threshold, the transmission power of the external charging device is adjusted to constrain the cumulative heat dose index within the preset safety threshold.

2. The wireless charging system according to claim 1, characterized in that, The control module is configured as follows: At the start of a single charging session, the cumulative heat dose index is reset to zero, and the preset safety threshold is dynamically set based on the target tissue's current heat diffusion capacity.

3. The wireless charging system according to claim 2, characterized in that, The control module is configured to dynamically set the preset safety threshold based on the target tissue's current thermal diffusion capacity in the following ways: Based on a pre-established tissue thermal diffusion model and environmental parameters, assess the current heat dissipation status of the target tissue; In response to an event that the heat dissipation state is high, the value of the preset safety threshold is increased accordingly; In response to an event that the heat dissipation state is low, the value of the preset safety threshold is reduced accordingly.

4. The wireless charging system according to claim 1, characterized in that, The control module is configured to dynamically calculate the cumulative heat dose index corresponding to the equivalent temperature experienced by the tissue within the current sampling period based on the real-time temperature data of the inner surface of the metal casing collected by the temperature sensing module, including: Based on the real-time temperature data, determine the equivalent body surface temperature of the tissue within the current sampling period. Based on the temperature range to which the equivalent body surface temperature belongs, determine the corresponding temperature response coefficient; Based on the equivalent body surface temperature, the corresponding temperature response coefficient, and the duration of the current sampling period, calculate the unit heat dose increment corresponding to the current sampling period; The cumulative heat dose index is updated by adding the unit heat dose increment corresponding to the current sampling period to the historical cumulative value.

5. The wireless charging system according to claim 4, characterized in that, The control module is configured to determine the equivalent body surface temperature of the tissue equivalent temperature within the current sampling period by means of: Acquire real-time temperature measurement values ​​that reflect the temperature state of the inner surface of the metal casing, collected by the temperature sensing module. Based on the pre-calibrated thermal conductivity parameters of the shell and combined with the physical structure model of the metal shell, the real-time temperature measurement value is corrected by thermal conduction compensation to obtain the first temperature value; Based on the first temperature value, the equivalent body surface temperature used to characterize the state of the contact surface with human tissue within the current sampling period is determined.

6. The wireless charging system according to claim 1 or 4, characterized in that, The frequency at which the control module dynamically calculates the cumulative heat dose index based on the real-time temperature data is variable, and is specifically configured as follows: During the initial charging period or in the first stage when the cumulative heat dose index is lower than the first heat agent threshold, the first calculation cycle is used for updating. In the second stage where the cumulative heat dose index exceeds the second heat agent threshold, the system switches to a second calculation cycle, which is shorter than the first calculation cycle, for updating.

7. The wireless charging system according to claim 1, characterized in that, The control module is configured to adjust the transmission power of the external charging device in the following ways: When the cumulative heat dose index is lower than the product of the first percentage threshold and the preset safety threshold, the external charging device is controlled to increase the transmission power. When the cumulative heat dose index reaches or exceeds the product of the second percentage threshold and the preset safety threshold, the external charging device is controlled to reduce or suspend the transmission power; wherein, the second percentage threshold is greater than the first percentage threshold.

8. The wireless charging system according to claim 7, characterized in that, When the external charging device is controlled to pause its transmission power, the control module is configured to execute charging restart logic, specifically including: During the pause, the real-time temperature data of the inner surface of the metal housing is continuously or periodically monitored; When the real-time temperature data is lower than the preset activation temperature threshold, or when the duration of the charging pause reaches the preset waiting time threshold, the charging session is restarted. When restarting the charging session, the cumulative heat dose index is reset to zero.

9. The wireless charging system according to claim 7, characterized in that, When the external charging device is controlled to reduce or pause its transmission power, the control module is configured to execute charging termination judgment logic, specifically including: Obtain the current remaining power of the internal power supply of the implantable medical device; If the current remaining power exceeds a preset sufficient power threshold, the external charging device will stop the current charging session and generate a charging completion notification. If the current remaining battery power does not exceed the sufficient battery power threshold, the operation of reducing or pausing the transmission power will continue.

10. A wireless charging method, characterized in that, Applied to the system according to any one of claims 1 to 9, the method comprises: Based on the real-time temperature data of the inner surface of the metal shell collected by the temperature sensing module, the cumulative heat dose index corresponding to the equivalent temperature of the tissue in the current sampling period is dynamically calculated. Based on the comparison between the cumulative heat dose index and the preset safety threshold, the transmission power of the external charging device is adjusted to constrain the cumulative heat dose index within the preset safety threshold.

11. An external charging device, said external charging device being used for wireless power transmission to an implantable medical device, characterized in that, The external charging device includes a control module, and the implantable medical device includes a metal housing and a temperature sensing module disposed on the inner surface of the metal housing. The control module is configured to: Based on the real-time temperature data of the inner surface of the metal shell collected by the temperature sensing module, the cumulative heat dose index corresponding to the equivalent temperature of the tissue in the current sampling period is dynamically calculated. Based on the comparison between the cumulative heat dose index and the preset safety threshold, the transmission power of the external charging device is adjusted to constrain the cumulative heat dose index within the preset safety threshold.

12. A computer-readable storage medium having a computer program stored thereon, characterized in that, When the computer program is executed by the processor, it implements the functions of the control module as described in any one of claims 1 to 9.

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