Implantable in-vivo wireless powered receiving module for myocardial contractility modulation

Abstract

The application provides an implantable myocardial contraction adjustment in-vivo wireless power supply receiving module, and relates to the wireless power supply technology field of implantable medical devices, and the module comprises a radio frequency receiving unit, a rectifier filter unit, an energy storage unit, a communication unit and a master control unit; the master control unit dynamically allocates energy according to load demand or energy storage state; the coupling efficiency is evaluated, and the operating parameters of the rectifier filter unit are adjusted according to the coupling efficiency to optimize the receiving efficiency; the actual operating parameters are compared with preset reference, and the reference is dynamically corrected based on the deviation to maintain long-term stability. The application also discloses a corresponding receiving module. The application can efficiently, stably and safely supply power for implantable pulse load devices, and has long-term operation reliability.

Description

Technical Field

[0001] This invention relates to the field of wireless power supply technology for implantable medical devices, and more specifically, to an implantable in vivo wireless power supply receiving module for myocardial contraction regulation. Background Technology

[0002] Implantable cardiac contractility modulators (CCMs) are important medical devices used to improve myocardial function. To reduce implant size and avoid the risk of secondary surgery due to battery replacement, battery-free systems have become a significant development trend, typically relying on external wireless power supply technology. One of the core components of such systems is the implanted wireless power receiver module, which receives radio frequency energy transmitted externally and converts it into stable electrical energy to power the core functional units of the cardiac contractility modulator.

[0003] Existing wireless power receiving modules have several shortcomings. For example, some wireless power systems attempt to optimize transmission efficiency by monitoring the coupling state of energy transmission and adjusting the parameters of the external transmitter accordingly. However, once the receiving module is implanted, the coupling state between the external transmitting coil and the internal receiving coil dynamically changes due to factors such as patient position changes and muscle peristalsis. Furthermore, the absorption and loss of radio frequency energy by internal tissues makes adjustments at the transmitting end insufficient to fully compensate for these effects, resulting in persistently low energy reception efficiency. Excess energy dissipates within the internal tissues, potentially causing local overheating and posing safety hazards. In addition, myocardial contractility modulation devices have pulsed, intermittent operating characteristics, requiring a large instantaneous current during stimulation but consuming almost no energy during the interval. Existing receiving modules often employ fixed energy allocation strategies, which cannot adapt to this dynamic load demand. This can easily lead to insufficient energy during stimulation and interruption, or redundant energy during the interval, resulting in waste and additional heat generation. Simultaneously, fluctuations in external energy transmission or changes in coupling efficiency cause significant fluctuations in the rectified DC voltage output, potentially affecting or even damaging the delicate electronic components of the myocardial contractility modulation device. More importantly, many existing solutions lack real-time monitoring and emergency response mechanisms for key safety indicators such as module overheating and leakage current, making it difficult to meet the high safety requirements of implantable medical devices. Summary of the Invention

[0004] To address the shortcomings of existing technologies, the purpose of this invention is to provide an implantable in vivo wireless power receiving module for myocardial contraction regulation.

[0005] An implantable in vivo wireless power receiving module for myocardial contraction regulation according to the present invention includes: a radio frequency receiving unit, a rectification and filtering unit, an energy storage unit, a communication unit, and a main control unit; The main control unit is connected to the radio frequency receiving unit, the rectification and filtering unit, the energy storage unit, and the communication unit, respectively. The communication unit is configured to obtain load requirements from an implanted myocardial contraction modulation stimulation module. The main control unit is configured as follows: Based on the received load requirements of the implanted myocardial contraction regulation stimulation module and / or the energy storage status of the energy storage unit, energy is dynamically allocated between the implanted myocardial contraction regulation stimulation module and the energy storage unit. The coupling efficiency of externally emitted energy to the internal wireless power receiving module is evaluated, and the operating parameters of the rectifier and filter unit are adjusted according to the coupling efficiency to optimize the energy receiving efficiency. The actual operating parameters of the in-body wireless power receiving module are compared with a preset reference parameter to obtain the operating state deviation. Based on the operating state deviation, the preset reference parameter is dynamically corrected to maintain long-term operating stability. The methods for evaluating coupling efficiency include: Receive information about the coupling offset between the external transmitting coil and the internal receiving coil in the internal wireless power receiving module; calculate the coupling efficiency based on the operating temperature of the internal wireless power receiving module and / or the coupling offset information.

[0006] Furthermore, the main control unit is also configured as follows: The system monitors the operating temperature, leakage current, and / or output voltage of the in-body wireless power receiving module in real time, and triggers emergency handling when the monitored values ​​exceed a preset safety threshold.

[0007] Furthermore, methods for adjusting operating parameters based on coupling efficiency include: Based on the coupling efficiency, the conduction timing of the rectifier circuit included in the rectifier filter unit is adjusted.

[0008] Furthermore, the load requirements include the stimulation current, stimulation duration, and / or stimulation frequency of the implanted myocardial contraction regulation stimulation module.

[0009] Furthermore, the reference parameters include a coupling efficiency reference value and / or an energy distribution coefficient.

[0010] Furthermore, the energy storage unit is a supercapacitor.

[0011] Furthermore, the evaluation of coupling efficiency and / or dynamic correction of control reference parameters is implemented using 16-bit fixed-point arithmetic.

[0012] Furthermore, it also includes a safety monitoring unit electrically connected to the main control unit, which includes a temperature sensor, a leakage current sensor, and / or a voltage sensor.

[0013] Compared with the prior art, the present invention has the following beneficial effects: By evaluating coupling efficiency and adaptively adjusting the receiver rectification parameters, combined with a dynamic energy distribution strategy, the energy receiving efficiency and power supply stability are significantly improved, enabling precise matching of the needs of pulsed loads and avoiding treatment interruptions.

[0014] Through comprehensive safety monitoring and emergency response mechanisms, the safe operation of the implanted module was ensured, and the risks of overheating of tissues in the body were reduced.

[0015] Through the closed-loop feedback correction mechanism, performance drift caused by factors such as component aging can be compensated, ensuring the long-term operational reliability of the system and meeting the requirements of long-term implantable medical devices in terms of efficiency, stability, safety and long life. Attached Figure Description

[0016] Other features, objects, and advantages of the present invention will become more apparent from the following detailed description of non-limiting embodiments with reference to the accompanying drawings: Figure 1 This is a schematic diagram of the overall architecture of the implantable wireless power supply system provided in the embodiments of this application.

[0017] Figure 2 This is a hardware block diagram of the in-body wireless power receiving module provided in an embodiment of this application.

[0018] Figure 3 This is a schematic diagram illustrating the process of the main control unit performing adaptive control as provided in an embodiment of this application.

[0019] Figure 4 The timing diagram for dynamic energy allocation signaling interaction provided in the embodiments of this application is shown. Detailed Implementation

[0020] The present invention will now be described in detail with reference to specific embodiments. These embodiments will help those skilled in the art to further understand the present invention, but do not limit the invention in any way. It should be noted that those skilled in the art can make several changes and improvements without departing from the concept of the present invention. These all fall within the protection scope of the present invention.

[0021] Example 1 This embodiment provides an implantable in vivo wireless power receiver module for myocardial contraction regulation. The following will be discussed in conjunction with the attached... Figure 1 , Figure 2 and Figure 3This application provides a comprehensive and detailed description of the overall architecture, hardware composition, and core control process of the technical solution provided.

[0022] Reference Figure 1 , Figure 1 This diagram illustrates the overall architecture of an implantable wireless power supply system applied in one embodiment of this application. Specifically, the system mainly includes an external power supply transmitter module 1 located outside the body and a device implanted inside human tissue 2. The implanted device includes an in-body wireless power supply receiver module 3, which is the core of this application. The in-body wireless power supply receiver module 3 is electrically connected to an implantable myocardial contraction regulation and stimulation module 4, providing it with all the electrical energy required for operation. Correspondingly, the myocardial contraction regulation and stimulation module 4 transmits electrical stimulation signals to specific parts of the heart via myocardial electrodes 5 to regulate myocardial contractility. In the entire system, the function of the external power supply transmitter module 1 is to generate and transmit a high-frequency electromagnetic field externally, while the in-body wireless power supply receiver module 3 is responsible for receiving this energy within the human tissue 2 and efficiently and stably converting it into direct current to drive the myocardial contraction regulation and stimulation module 4.

[0023] Figure 2 This is a hardware structure block diagram of the in-vivo wireless power receiver module 3 in one embodiment of this application. In one embodiment of this application, the in-vivo wireless power receiver module 3 is designed as a highly integrated micro-unit, with an overall size controllable within 10 mm × 8 mm × 3 mm, and is encapsulated using medical-grade biocompatible materials to ensure the safety of long-term implantation. Figure 2 As shown, the in-body wireless power receiving module 3 mainly includes core units such as radio frequency receiving unit 31, rectification and filtering unit 32, energy storage unit 33, main control unit 34, communication unit 35, and safety monitoring unit 36.

[0024] The main control unit 34 serves as the control core of the internal wireless power supply and receiving module 3, connecting and communicating with all other units. As an optional implementation, the main control unit 34 can utilize an ultra-low-power microcontroller, such as the STM32L0 series. This series of microcontrollers features extremely low standby power consumption (e.g., less than 0.8 microamps) and integrates a high-efficiency processor core and rich peripheral interfaces, sufficient to support the complex algorithm calculations and multi-channel sensor data acquisition required in this solution. To further reduce power consumption and improve computational efficiency, all algorithms executed internally by the main control unit 34, especially those involving complex mathematical models, are implemented using 16-bit fixed-point arithmetic, rather than floating-point arithmetic.

[0025] The function of the radio frequency (RF) receiving unit 31 is to capture energy from the electromagnetic field emitted by the externally powered transmitting module 1. In this embodiment, the RF receiving unit 31 includes a miniature planar spiral receiving coil and an LC resonant matching network. The receiving coil can be designed with a diameter of 3 to 5 mm and 8 to 12 turns to achieve good energy reception performance within a compact size. The LC resonant matching network is precisely tuned to the system's wireless power supply operating frequency (e.g., 13.56 MHz) to resonate with the receiving coil, thereby maximizing energy reception efficiency. It is understood that the main control unit 34 can fine-tune the resonant point by controlling the variable capacitor in the matching network.

[0026] The rectifier-filter unit 32 is connected to the output of the RF receiving unit 31. Its function is to convert the received high-frequency AC power into stable, low-ripple DC power to supply the subsequent energy storage unit 33 and the myocardial contraction regulation stimulation module 4. In this embodiment, the rectifier-filter unit 32 includes a high-efficiency full-bridge rectifier circuit and an adaptive filter circuit. The full-bridge rectifier circuit is responsible for converting AC power into pulsating DC power, while the adaptive filter circuit filters the pulsating DC power to smooth the voltage. The main control unit 34 can dynamically adjust the operating parameters of this unit according to the real-time operating status of the system, such as the conduction timing of the switching transistors in the rectifier circuit and the filter capacitor value of the filter circuit, so as to maintain high rectification efficiency and stable voltage output under different input energy and load conditions. Specifically, the goal of this embodiment is to stabilize the output DC voltage at around 5.0 volts, with a fluctuation range of no more than ±0.2 volts and a voltage ripple of less than 50 millivolts.

[0027] The energy storage unit 33 stores the electrical energy output from the rectifier and filter unit 32 and releases it rapidly when needed to meet the pulsed, high-peak-power load demands of the myocardial contraction regulation stimulation module 4. Unlike solutions using chemical batteries, this embodiment preferably employs a miniature, high-capacity supercapacitor as the energy storage unit 33. Supercapacitors have extremely high charge / discharge rates, millions of cycle lives, and a wider operating temperature range, making them ideal as energy buffers for pulsed loads in implantable devices. In this embodiment, an 80 milliwatt-hour supercapacitor can be selected, equipped with necessary overvoltage and undervoltage protection circuits, which are monitored and managed by the main control unit 34.

[0028] The communication unit 35 is responsible for establishing a communication link between the in-body wireless power receiving module 3, the external power transmitting module 1, and the in-body myocardial contraction regulation stimulation module 4. As an optional implementation, the communication unit 35 can be a miniature near-field communication module. Through this communication unit 35, the main control unit 34 can obtain real-time load demand information from the myocardial contraction regulation stimulation module 4, such as the stimulation current, stimulation duration, and stimulation frequency required for the upcoming stimulation. Simultaneously, the main control unit 34 can also send its own operating status, such as coupling efficiency, energy storage status, and safety alarms, to the external power transmitting module 1 to achieve closed-loop coordinated control of the entire system.

[0029] The safety monitoring unit 36 ​​is crucial for ensuring the long-term safe operation of the implantable module. This unit integrates a series of miniature sensors for real-time monitoring of key safety indicators of the module. In this embodiment, the safety monitoring unit 36 ​​includes, but is not limited to, a temperature sensor, a leakage current sensor, and a voltage sensor. The temperature sensor monitors the temperature of the encapsulation surface of the in-vivo wireless power receiver module 3 to prevent local tissue overheating due to energy dissipation; the leakage current sensor monitors for abnormal current leakage from the module into human tissue, a core safety indicator for implantable active medical devices; and the voltage sensor monitors the output voltage of the rectifier filter unit 32 and the terminal voltage of the energy storage unit 33. The main control unit 34 reads the values ​​of these sensors at a very high frequency (e.g., every 10 milliseconds) and compares them with preset safety thresholds. For example, the preset upper limit for module operating temperature is 40 degrees Celsius, and the upper limit for leakage current is 0.1 microamps. Once any monitored value exceeds the safety range, the main control unit 34 will immediately initiate the corresponding emergency response procedure.

[0030] Reference Figure 3 As shown below, the complete working process of the main control unit 34 performing adaptive control in this embodiment will be described in detail below.

[0031] First, in step S101, the system initializes. After the internal wireless power receiving module 3 is activated by the energy field of the external power transmitting module 1, the main control unit 34 begins executing the initialization procedure. During this stage, the main control unit 34 reads pre-calibrated reference parameters and control algorithm models from its non-volatile memory. These parameters include, but are not limited to, the reference coupling efficiency η. base (e.g., 0.7), reference rectified output voltage V rec-base (e.g., 5.0 volts), the maximum and minimum safe energy thresholds E of the energy storage unit 33 max and E min (e.g., 100 mWh and 20 mWh), maximum permissible operating temperature T mod-max (e.g., 40 degrees Celsius), maximum permissible leakage current Ileak-max (e.g., 0.1 microamps) and adjustment coefficients used in various control algorithms, etc.

[0032] After initialization, the system enters the main control loop and calculates the coupling efficiency in step S102. The main control unit 34 obtains the actual power P output by the rectifier and filter unit 32 through its own power monitoring circuit. rec (t), and simultaneously obtains its current transmission power P from the external power supply transmitter module 1 through the communication unit 35. tx (t). Theoretically, coupling efficiency is the ratio of received power to transmitted power. However, an innovation of this application is that the calculation model further considers the influence of dynamic factors within the module. Specifically, the main control unit 34 also obtains the current module operating temperature T from the safety monitoring unit 36. mod (t), and estimates the coupling offset d(t) between the receiving coil and the transmitting coil by analyzing the characteristics of the received signal (or by other sensors). Then, the main control unit 34 uses the following empirical or semi-empirical formula to calculate a more realistic coupling efficiency η(t):

[0033] This formula reflects the physical fact that both increased temperature and increased coupling offset lead to a decrease in coupling efficiency. The calculated coupling efficiency η(t) is an important input for multiple subsequent control loops.

[0034] Subsequently, in step S103, the rectifier turn-on timing is adjusted, which is a key step in optimizing receiver efficiency. The main control unit 34 compares the real-time coupling efficiency η(t) calculated in step S102 with a dynamically updated coupling efficiency benchmark value to obtain the coupling efficiency deviation Δη(t). Based on this deviation, the main control unit 34 adjusts the operating parameters of the rectifier circuit in the rectifier filter unit 32. In this embodiment, a specific adjustment method is to adjust the turn-on timing τ(t) of the switching transistors in the rectifier bridge. For example, the following formula can be used for adjustment:

[0035] Where, τ base This is the reference turn-on timing. The purpose of this adjustment is to actively optimize the rectification process at the receiving end when the coupling efficiency changes, in order to compensate for the change in input energy, thereby maximizing the overall energy conversion efficiency from the receiving coil to the DC output. In addition, the main control unit 34 will also adjust the output voltage ripple V based on the monitored output voltage ripple. rip The filtering parameters of the filter circuit are dynamically adjusted based on the voltage ripple and coupling efficiency deviation Δη(t) (e.g., by controlling the switched capacitor array to change the equivalent filter capacitor value) to further suppress voltage ripple and ensure the stability of the output voltage.

[0036] Subsequently, the process executes step S104 to obtain load requirements. The main control unit 34 actively queries or passively receives load requirement information from the myocardial contraction regulation stimulation module 4 via the communication unit 35. This information is very specific and may include the stimulation current I required for the next pulse or the next set of stimulation pulses. stim (t), stimulation duration t stim and stimulation frequency f stim This allows the main control unit 34 to anticipate upcoming energy consumption.

[0037] Based on the acquired load demand and the system's own state, the process proceeds to step S105, calculating the energy allocation ratio. This is the core decision-making step for achieving dynamic energy allocation. The main control unit 34 will comprehensively consider multiple factors: the upcoming load demand (from I... stim (t) and other parameters reflect the current energy storage state E of energy storage unit 33. sto (t) (obtained by monitoring its terminal voltage), and the current energy input status (reflected by the coupling efficiency η(t)). Then, the main control unit 34 substitutes the values ​​into a dynamic energy distribution formula to calculate two key proportional coefficients: the load power supply ratio K. load (t) and energy storage ratio K sto (t), and K load (t) + K sto (t) = 1. A calculation of K load The specific formula for (t) can be designed as follows:

[0038] Among them, K E It is the energy distribution regulation coefficient, I stim-base It is the reference stimulation current, ΔE sto (t) represents the deviation between the current energy storage and the target energy storage. The formula means that when the load demand (I... stim (t) increases or stores energy (E) sto When (t) is high, the proportion of energy supplied to the load is increased; conversely, the proportion of energy supplied to the load is reduced, and more energy is used for storage.

[0039] After calculating the allocation ratio, energy allocation is performed in step S106. The main control unit 34 controls the power switch inside the rectifier and filter unit 32 to allocate the total rectified output power according to K. load (t) and K sto The proportion of (t) is precisely allocated to the myocardial contraction regulation stimulation module 4 and the energy storage unit 33. For example, when the myocardial contraction regulation device is in standby mode (I stim When (t) is very small, the main control unit 34 calculates K. load (t) may be approximately 0.2, Ksto (t) is approximately 0.8, at which point most of the energy is used to charge the supercapacitor. When the myocardial contraction regulation stimulation module 4 is about to emit a high-intensity stimulation pulse, the main control unit 34 immediately recalculates, obtaining a very high K. load (t) (e.g., 0.7), most of the input energy is directly supplied to the load. At the same time, if the input energy is insufficient to meet the instantaneous peak power, the energy storage unit 33 (supercapacitor) will instantaneously release its stored energy to supplement it.

[0040] In each step of the main loop, step S107 is executed in parallel for real-time safety monitoring. As mentioned earlier, the main control unit 34 continuously acquires temperature, leakage current, and voltage data from the safety monitoring unit 36 ​​and compares them with safety thresholds. Once an anomaly is detected, such as the module temperature exceeding 40 degrees Celsius, the main control unit 34 will immediately trigger an emergency handling mechanism. For example, it may first attempt to request the external power supply transmitter module 1 to reduce its transmission power via the communication unit 35. If the situation does not improve, it may further reduce its own load or temporarily cut off the power supply to the myocardial contraction regulation stimulation module 4 and send an emergency alarm signal to the external power supply transmitter module 1.

[0041] In addition, to ensure the long-term stability of the system, the main control loop also includes a critical closed-loop feedback correction stage, corresponding to... Figure 3 Steps S108 and S109 are described in the text. As the implantation time progresses, the module's components may age (e.g., receiving coil parameter drift, supercapacitor capacity decay), or subtle changes may occur in the internal environment, all of which can cause the initially calibrated reference parameters of the system to become inaccurate. The closed-loop feedback correction mechanism is designed to address this long-term drift. In step S108, the main control unit 34 determines whether correction needs to be performed. This determination can be based on a timer (e.g., performed once per week of operation), or when certain system operating deviations are detected (e.g., deviation of adjusted coupling efficiency Δη(t), deviation of rectified output voltage ΔV). rec (t) or load power supply deviation ΔE load (t) is triggered when it persists and exceeds a certain threshold.

[0042] If correction is deemed necessary, the process proceeds to step S109 to perform closed-loop correction. In this step, the main control unit 34 fine-tunes the core preset benchmark parameters stored in non-volatile memory by substituting specific correction formulas into the system operating state deviation data accumulated over a period of time. For example, if the system continuously detects that, under the same physical coupling conditions, the actually calculated coupling efficiency is always lower than the old benchmark value η... base The correction algorithm will then appropriately lower η. baseSimilarly, if a persistent deviation in the accuracy of energy allocation is detected, the algorithm may fine-tune the energy allocation coefficient K. E In this way, the system can achieve self-recalibration, dynamically correcting these preset reference parameters to compensate for performance drift caused by factors such as component aging, ensuring that the control algorithm always operates in an optimal state throughout the system's lifespan of several years. After calibration, the process returns to step S102, continuing the main control loop using the updated reference parameters.

[0043] Example 2 This embodiment focuses on illustrating how the technical solution provided in this application maintains power supply stability through adaptive optimization when faced with abrupt changes in the energy transmission path (e.g., deterioration of coupling state due to patient movement). This embodiment uses the exact same hardware structure as Embodiment 1, namely... Figure 2 The core of the control process of the in-body wireless power receiver module 3 shown lies in Figure 3 The rapid linkage response between step S102 (calculating coupling efficiency) and step S103 (adjusting rectifier conduction timing) is shown.

[0044] Assuming that under the initial stable operating state, the coupling between the external power supply transmitter module 1 and the internal wireless power supply receiver module 3 is good, and the coupling efficiency η(t) calculated by the main control unit 34 in step S102 is stable at around 0.75. At this time, under the control of the main control unit 34, the rectifier filter unit 32 operates with an optimal reference turn-on timing τ. base During operation, the output DC voltage stabilizes at 5.0 volts.

[0045] Now consider a sudden scenario: a patient suddenly changes their body posture drastically, for example, from lying flat to lying on their side, causing a significant axial and radial offset between the external transmitting coil and the internal receiving coil. This offset severely disrupts the original electromagnetic field coupling, causing a sharp reduction in the energy that the radio frequency receiving unit 31 can capture.

[0046] When the main control unit 34 executes step S102 in its next calculation cycle (e.g., within 10 milliseconds), it will immediately detect this change. Due to the significant reduction in the strength of the received radio frequency signal, its calculated real-time coupling efficiency η(t) may plummet to 0.55. The main control unit 34 compares this newly calculated efficiency value with the coupling efficiency benchmark value maintained internally by the system, which represents the recent stable state (e.g., the previous 0.75), thus obtaining a significant negative coupling efficiency deviation Δη(t).

[0047] Faced with this significant deviation, the main control unit 34 will immediately execute a series of coordinated adaptive adjustment actions, rather than passively waiting or relying solely on possible power compensation from the external transmitter.

[0048] First, and most crucially, is the execution of step S103, which involves adjusting the operating parameters of the rectifier circuit. The main control unit 34 will adjust the parameters according to the aforementioned formula τ(t) = τ base (1 - 0.1 We use Δη(t) to dynamically calculate a new conduction timing τ(t). Since Δη(t) is a large negative value in this scenario, the calculated new conduction timing τ(t) will be significantly larger than the baseline conduction timing τ. base Extending the conduction timing allows the rectifier circuit more time to "draw" energy from the input terminal when the input voltage is low, thus compensating to some extent for the decrease in rectification efficiency caused by the reduced input energy. This is a proactive efficiency optimization performed at the receiving end.

[0049] Secondly, the main control unit 34 also anticipates that a sharp drop in input energy may lead to greater ripple in the rectified DC output voltage. Therefore, it will adjust the parameters of the adaptive filter circuit accordingly. For example, through a C-like... filter (t) = C filter-base + K η The adjustment logic of |Δη(t)| dynamically increases the equivalent capacitance value of the filter circuit. A larger filter capacitor can more effectively smooth the output voltage and suppress voltage ripple that may be aggravated by input instability.

[0050] At the same time, as part of the system's collaborative operation, the main control unit 34 will also send a status signal to the external power supply transmitter module 1 through the communication unit 35. This signal can be decoded into a prompt of "poor coupling, request to check or adjust the position of the external device", providing a basis for intervention for users or medical staff.

[0051] Through the aforementioned series of autonomous adjustments completed within the receiving module at the millisecond level, even in the event of a sudden drop in coupling efficiency of up to 25%, the output DC voltage of the in vivo wireless power receiving module 3 in this embodiment can still be effectively maintained within the target range (e.g., 4.8 volts to 5.2 volts). This ensures that the myocardial contraction regulation stimulation module 4 connected to the back end can obtain a continuous and stable power supply, and its normal operation will not be disturbed by such sudden changes in coupling state. This fully demonstrates the strong robustness and adaptability of the proposed solution to dynamic coupling environments.

[0052] Example 3 This embodiment aims to demonstrate in detail the superiority of the dynamic energy allocation strategy in the technical solution of this application, especially its adaptive capability in dealing with different working modes (i.e., different pulse load requirements) of the myocardial contraction regulation stimulation module. This embodiment also adopts... Figure 2 The core of the control logic of the hardware structure shown lies in Figure 3 Steps S104 (obtain load demand), S105 (calculate energy allocation ratio), and S106 (execute energy allocation) in the process can be combined. Figure 4 The signaling interaction timing diagram shown is used for understanding.

[0053] This embodiment will use two typical scenarios to describe how the main control unit 34 intelligently schedules energy.

[0054] Scenario 1: Low-intensity, intermittent treatment mode. Assume the doctor's order sets the myocardial contractility modulator to operate in a relatively mild treatment mode with a low stimulation frequency (e.g., f...). stim = 1 Hz), and the current for each stimulus is also relatively small (e.g., I stim = 0.2 amperes). In this mode, the myocardial contraction regulation stimulation module 4 sends load demand information containing the above parameters to the main control unit 34 via the communication unit 35 (corresponding to...). Figure 4 The main control unit 34 obtains the Stimulation_Request in step S104, but the content is low load. After obtaining the request, it proceeds to step S105. It will I stim Substituting parameters such as 0.2 amperes into the dynamic energy distribution formula (as described in Example 1), and since the stimulation current of 0.2 amperes is much lower than the average or reference load level of the system, the calculated load power supply ratio K is... load (t) will be a small value, for example, about 0.4. Therefore, in the next step S106, the main control unit 34 will control the power switch to directly supply about 40% of the electrical energy output by the rectifier and filter unit 32 to the myocardial contraction regulation stimulation module 4 (this part of the energy is sufficient to meet its low-power standby and low-intensity stimulation requirements), while the remaining, larger part of the energy (about 60%, i.e., K) will be supplied to the myocardial contraction regulation stimulation module 4. sto (t) ≈ 0.6) is guided to energy storage unit 33 to charge the supercapacitor contained therein. Through this strategy, the system can efficiently store the received energy during low-load intermittent periods, increasing the energy storage level (E) of the supercapacitor. sto (t) is kept at a high level, which is well prepared for possible high-intensity work, while avoiding energy redundancy and unnecessary dissipation at low loads.

[0055] Scenario 2: High-intensity, continuous treatment mode. Now assume that, based on the patient's condition, the doctor adjusts the treatment plan to a high-intensity mode, requiring the myocardial contraction modulation stimulation module 4 to perform high-frequency (e.g., f...) stimulation. stim = 5 Hz), large current (e.g., I stim= 0.5 amperes) of stimulation. The myocardial contraction regulation stimulation module 4 will apply this new high-load request (such as Figure 4 The Stimulation_Request (as shown in the diagram) is sent to the main control unit 34 via communication unit 35. Upon receiving the request, the main control unit 34 immediately recalculates in step S105. Because I... stim = 0.5 amps is a load demand significantly higher than the baseline value. Substituting this into the formula, the calculated load supply ratio K load (t) will become very high, for example, about 0.8. During energy distribution in step S106, the main control unit 34 controls the power switch to directly and preferentially supply most (80%) of the energy output from the rectifier-filter unit 32 to the myocardial contraction regulation stimulation module 4 to meet its high-power operation requirements. However, in some extreme cases, even if all the received energy is supplied to the load, it may not be able to meet the instantaneous power at the peak of the stimulation pulse. At this time, the energy storage unit 33 (supercapacitor) plays the role of an "energy buffer." The main control unit 34 simultaneously controls the discharge path from the supercapacitor to the load, and the supercapacitor instantaneously releases its pre-stored energy, which is superimposed with the energy from the rectifier to jointly meet the peak power requirements of the load, achieving a "peak shaving and valley filling" effect. During continuous high-intensity operation, the energy stored in the supercapacitor E... sto (t) will gradually decrease. The main control unit 34 will continuously monitor E. sto The state of (t) (corresponding to) Figure 4 (Internal monitoring in Energy_Storage_Status). When it detects that the energy storage level is below the preset minimum safety threshold E... min In order to ensure the reliability of subsequent stimulation, the main control unit 34 will actively send a "request to increase power" signal to the external power supply transmitter module 1 through the communication unit 35 (corresponding to...). Figure 4 (Power_Boost_Request in the code). After receiving this signal, the external module can increase its transmission power accordingly, thereby increasing the energy input of the internal module and providing more resources for the energy scheduling of the main control unit 34.

[0056] This embodiment can seamlessly switch between different treatment modes, efficiently storing energy under low load and reliably providing peak power under high load through "direct input + energy storage supplementation". It perfectly adapts to the pulsed and dynamically changing load characteristics of the myocardial contraction regulation device, fundamentally solving the problem of energy supply and demand imbalance and ensuring the continuity and reliability of treatment.

[0057] Example 4 This embodiment focuses on how the technical solution of this application uses a closed-loop feedback correction mechanism to ensure the performance stability and reliability of the implanted module during long-term operation. This is crucial to ensuring that an implantable medical device can reach its designed service life (e.g., more than 5 years). This embodiment is still based on... Figure 2 The hardware structure, whose core algorithm logic corresponds to Figure 3 Steps S108 (determine if closed-loop calibration is needed) and S109 (perform closed-loop calibration) are included in the calculation.

[0058] Assume that the in vivo wireless power receiver module 3 of this application has been implanted in a patient and has been operating stably for 3 years. Over such a long period of time, the electronic components constituting the module will inevitably experience performance parameter drift due to aging.

[0059] For example, the inductance and quality factor of the receiving coil in the RF receiving unit 31 may undergo slight but permanent changes due to long-term stress, minor deformation, or temperature cycling of the material, which will cause a shift in its resonant frequency. As a result, even if the physical positions and orientations of the external power supply transmitting module 1 and the internal wireless power supply receiving module 3 are exactly the same as those calibrated at the factory, the actual energy transmission coupling efficiency will be systematically lower than the initial state.

[0060] For example, the equivalent series resistance of the supercapacitor in energy storage unit 33 increases slowly with the number of cycles, and its effective capacity also decreases to some extent. This results in different rates of change of its terminal voltage and energy loss compared to the initial state under the same charging and discharging current.

[0061] If the control algorithm relies entirely on fixed reference parameters (such as η) programmed at the factory... base , K E If these hardware parameters drift due to aging, the error between the algorithm model's prediction and the actual physical process will become increasingly larger, ultimately causing the overall performance of the system (such as energy receiving efficiency, distribution accuracy, and stability) to continue to decline.

[0062] The closed-loop feedback correction mechanism in this application is designed to solve this problem. The main control unit 34 is configured not only as an executor, but also as a learner and corrector.

[0063] Its working process is as follows: Every day the module is running, the main control unit 34 executes its main control loop. During this process, it continuously calculates the "deviations" of various operating states. For example, in step S103, it calculates the real-time coupling efficiency deviation Δη(t); after step S106, it can calculate the load power supply deviation ΔE by comparing the expected energy distribution results with the actual energy storage changes. load(t).

[0064] In the short term, these deviation values ​​may fluctuate due to instantaneous changes in the external environment, which is normal. However, the closed-loop feedback correction algorithm (step S109) focuses on the long-term trend of these deviations. The main control unit 34 records the average or some weighted integral value of these key deviation values ​​in its internal memory at a low frequency (e.g., hourly or daily).

[0065] After several days or weeks of continuous monitoring and data accumulation, if the algorithm of the main control unit 34 detects that the coupling efficiency deviation Δη(t) consistently and systematically exhibits a small negative value (e.g., an average value of -0.03), this forms a clear "deviation pattern." The algorithm can then infer that the coupling state is not temporarily poor, but rather that the reference value η used by the system to calculate the coupling efficiency is... base In itself, it is already "outdated" and too expensive compared to the current aging hardware.

[0066] At this point, the judgment condition of step S108 is met, and the main control unit 34 triggers step S109 to perform closed-loop correction. It calls a preset correction formula to update the reference parameters stored in non-volatile memory (such as flash memory). For example, the formula for updating the reference coupling efficiency could be:

[0067] Where, η base-corr (t) is the corrected new reference value, K corr It is a correction gain coefficient less than 1 (to prevent instability caused by overly rapid adjustment), and Δη(t) is the average deviation over a past period. Using this formula, the old η... base It will be replaced by a new, lower value that is more in line with the current hardware situation.

[0068] Similarly, if the algorithm detects a load power supply deviation ΔE load (t) also exhibits a systematic drift, which similarly invokes another correction formula for core parameters in the dynamic energy allocation algorithm, such as the energy allocation coefficient K. E Make minor adjustments:

[0069] Through this periodic self-correction and compensation mechanism based on long-term data trends, the technical solution of this application achieves an adaptive "recalibration." This enables the control system to dynamically track and compensate for performance drift caused by hardware aging. The ultimate result is that even after many years of implantation and changes in component parameters, the overall performance of the entire wireless power receiver module (such as energy reception efficiency, voltage stability, and energy distribution accuracy) can be maintained at near-optimal levels at the time of manufacture, thereby significantly extending the effective lifespan and reliability of the implanted module and demonstrating the system's superior long-term adaptive capability.

[0070] Those skilled in the art will understand that, besides implementing the system and its various devices, modules, and units provided by this invention in the form of purely computer-readable program code, the same functions can be achieved entirely through logical programming of the method steps, making the system and its various devices, modules, and units of this invention function in the form of logic gates, switches, application-specific integrated circuits, programmable logic controllers, and embedded microcontrollers. Therefore, the system and its various devices, modules, and units provided by this invention can be considered as a hardware component, and the devices, modules, and units included therein for implementing various functions can also be considered as structures within the hardware component; alternatively, the devices, modules, and units for implementing various functions can be considered as both software modules implementing the method and structures within the hardware component.

[0071] Specific embodiments of the present invention have been described above. It should be understood that the present invention is not limited to the specific embodiments described above, and those skilled in the art can make various changes or modifications within the scope of the claims, which do not affect the essence of the present invention. Unless otherwise specified, the embodiments and features described in this application can be arbitrarily combined with each other.

Claims

1. An implantable in vivo wireless power receiving module for myocardial contraction regulation, characterized in that, include: Radio frequency receiving unit, rectification and filtering unit, energy storage unit, communication unit and main control unit; The main control unit is connected to the radio frequency receiving unit, the rectification and filtering unit, the energy storage unit, and the communication unit, respectively. The communication unit is configured to obtain load requirements from an implanted myocardial contraction modulation stimulation module. The main control unit is configured as follows: Based on the received load requirements of the implanted myocardial contraction regulation stimulation module and / or the energy storage status of the energy storage unit, energy is dynamically allocated between the implanted myocardial contraction regulation stimulation module and the energy storage unit. The coupling efficiency of externally emitted energy to the internal wireless power receiving module is evaluated, and the operating parameters of the rectifier and filter unit are adjusted according to the coupling efficiency to optimize the energy receiving efficiency. The actual operating parameters of the in-body wireless power receiving module are compared with a preset reference parameter to obtain the operating state deviation. Based on the operating state deviation, the preset reference parameter is dynamically corrected to maintain long-term operating stability. The methods for evaluating coupling efficiency include: Receive information about the coupling offset between the external transmitting coil and the internal receiving coil in the internal wireless power receiving module; calculate the coupling efficiency based on the operating temperature of the internal wireless power receiving module and / or the coupling offset information.

2. The implantable in vivo wireless power receiving module for myocardial contraction regulation according to claim 1, characterized in that, The main control unit is also configured to: The system monitors the operating temperature, leakage current, and / or output voltage of the in-body wireless power receiving module in real time, and triggers emergency handling when the monitored values ​​exceed a preset safety threshold.

3. The implantable in vivo wireless power receiving module for myocardial contraction regulation according to claim 1, characterized in that, Methods for adjusting operating parameters based on coupling efficiency include: Based on the coupling efficiency, the conduction timing of the rectifier circuit included in the rectifier filter unit is adjusted.

4. The implantable in vivo wireless power receiving module for myocardial contraction regulation according to claim 1, characterized in that, The load requirements include the stimulation current, stimulation duration, and / or stimulation frequency of the implanted myocardial contraction regulation stimulation module.

5. The implantable in vivo wireless power receiving module for myocardial contraction regulation according to claim 1, characterized in that, The reference parameters include a reference value for coupling efficiency and / or an energy distribution coefficient.

6. The implantable in vivo wireless power receiving module for myocardial contraction regulation according to claim 1, characterized in that, The energy storage unit is a supercapacitor.

7. The implantable in vivo wireless power receiving module for myocardial contraction regulation according to claim 1, characterized in that, The method for evaluating coupling efficiency and / or dynamically correcting control reference parameters is implemented using 16-bit fixed-point arithmetic.

8. The implantable in vivo wireless power receiving module for myocardial contraction regulation according to claim 1, characterized in that, It also includes a safety monitoring unit electrically connected to the main control unit, which includes a temperature sensor, a leakage current sensor and / or a voltage sensor.

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