Implantable medical instrument, wireless charger and implantable charging system

Abstract

The embodiment of the invention discloses an implantable medical instrument, a wireless charger and an implantable charging system, the implantable medical instrument is charged through the wireless charger, and the implantable medical instrument comprises a first control unit used for switching working modes based on a current signal sending period, in the second working mode, the current signal sending period is updated based on the current charging state information of the energy receiving unit, and a trigger control signal is sent to the wireless communication unit; wherein the first control unit is switched from the second working mode to the first working mode after sending the trigger control completion signal; the wireless communication unit is used for sending the current charging state information to the wireless charger through a wireless communication message when the trigger control signal is received, so that the wireless charger adjusts an emission energy emission parameter based on the current charging state information; and the energy receiving unit is used for receiving and storing the charging energy transmitted by the wireless charger, so that the charging efficiency of the implantable medical instrument is improved, and the power consumption of the instrument is reduced.

Description

Technical Field

[0001] The present invention relates to the technical field of implantable medical devices, and in particular to an implantable medical instrument, a wireless charger, and an implantable charging system. Background Art

[0002] With the advancement of medical technology, implantable medical devices, such as pacemakers and neurostimulators, are becoming increasingly common in clinical settings. These devices typically require long-term power supply, but traditional battery-powered devices have limited lifespans and are difficult to replace.

[0003] In order to solve the problems of limited life and difficulty in replacement of traditional batteries, wireless charging technology is currently commonly used to replenish power for these medical devices. That is, a power receiving end can be configured in the implantable medical device, and the power receiving end can be supplied with power through the power transmitting end outside the body, so that the supplied power can be stored in a storage battery, and the implantable medical device can be powered by the storage battery.

[0004] However, due to the presence of their metal casing, implantable medical devices are prone to electromagnetic shielding effects when charging, resulting in low charging efficiency. In addition, the power receiving end needs to continuously send modulated signals to maintain communication, which requires the control unit of the power receiving end to be in a continuous working state, consuming a large amount of electricity and affecting the battery life of the implantable medical device. Summary of the Invention

[0005] The present invention provides an implantable medical instrument, a wireless charger, and an implantable charging system, so as to provide an implantable medical instrument that can operate efficiently and with low power consumption in a metal implant environment, thereby improving the charging efficiency of the wireless charging system and reducing the power consumption of the instrument itself.

[0006] In a first aspect, an embodiment of the present invention provides an implantable medical instrument, which is charged by a wireless charger. The implantable medical instrument includes: a first control unit, a wireless communication unit, and an energy receiving unit; wherein,

[0007] The first control unit is configured to switch from the first operating mode to the second operating mode based on the current signal transmission cycle, update the current signal transmission cycle based on the current charging state information in the second operating mode, and send a trigger control signal to the wireless communication unit; wherein the first control unit switches from the second operating mode to the first operating mode after completing the sending of the trigger control signal, and the resource consumption corresponding to the first operating mode is less than the resource consumption corresponding to the second operating mode;

[0008] The wireless communication unit is configured to transmit the current charging status information to the wireless charger via a wireless communication message upon receiving the trigger control signal, so that the wireless charger adjusts energy transmission parameters transmitted to the implantable medical device based on the current charging status information;

[0009] The energy receiving unit is used to receive and store the charging energy transmitted by the wireless charger.

[0010] In a second aspect, an embodiment of the present invention further provides a wireless charger, comprising: a second control unit and an energy transmitting unit; wherein,

[0011] The second control unit is configured to receive a wireless communication message sent by a wireless communication unit of the implantable medical instrument, and adjust the energy transmission parameters based on the current charging state information carried in the wireless communication message;

[0012] The energy transmission unit is used to transmit charging energy to the implantable medical device based on the adjusted energy transmission parameters.

[0013] In a third aspect, an embodiment of the present invention further provides an implantable charging system, comprising:

[0014] An implantable medical device comprising any one of the embodiments of the present invention implanted into a user's body; and

[0015] The wireless charger according to any one of the embodiments of the present invention.

[0016] The technical solution of the embodiments of the present invention provides an implantable medical device, a transmitter, and a wireless charging method, wherein the implantable medical device is charged via a wireless charger. The method mainly includes: a first control unit, configured to switch from a first operating mode to a second operating mode based on a current signal transmission cycle, and in the second operating mode, update the current signal transmission cycle based on current charging status information, and send a trigger control signal to a wireless communication unit. After the first control unit sends the trigger control signal, the first operating mode switches to the first operating mode, and the resource consumption corresponding to the first operating mode is less than the resource consumption corresponding to the second operating mode. The wireless communication unit, upon receiving the trigger control signal, transmits the current charging status information to the wireless charger via a wireless communication message, so that the wireless charger adjusts the energy transmission parameters transmitted to the implantable medical device based on the current charging status information. The energy receiving unit, configured to receive and store the charging energy transmitted by the wireless charger, is used to receive and store the charging energy transmitted by the wireless charger. The implantable medical device provided by the technical solution of this embodiment, on the one hand, controls the wireless communication unit to achieve intermittent data communication with the wireless charger. Because the wireless signal has strong penetrating power, it can effectively overcome the shielding effect of the metal shell on electromagnetic waves, thereby improving the energy reception efficiency of the device and thus improving the charging efficiency. On the other hand, the control unit in the implantable medical instrument can periodically switch the working mode, which makes the control unit in the implantable medical instrument in a low-power working mode most of the time, reducing the power consumption of the implantable medical instrument itself, thereby improving the battery life of the implantable medical instrument. BRIEF DESCRIPTION OF THE DRAWINGS

[0017] To more clearly illustrate the technical solutions of the exemplary embodiments of the present invention, the following briefly introduces the drawings required for describing the embodiments. Obviously, the drawings introduced here only illustrate some of the embodiments to be described by the present invention, and are not exhaustive. A person skilled in the art can derive other drawings based on these drawings without inventive effort.

[0018] Figure 1 A schematic diagram of an implantable medical device according to an embodiment of the present invention;

[0019] Figure 2 A schematic diagram of a stimulation electrode according to an embodiment of the present invention;

[0020] Figure 3 A schematic structural diagram of an implantable medical device provided by an embodiment of the present invention;

[0021] Figure 4 A schematic structural diagram of a wireless charger provided by an embodiment of the present invention;

[0022] Figure 5 This is a structural diagram of an implantable charging system provided by an embodiment of the present invention. DETAILED DESCRIPTION

[0023] Below, the present application is further described in conjunction with the accompanying drawings and specific implementation methods. It should be noted that, under the premise of no conflict, the various embodiments or technical features described below can be arbitrarily combined to form new embodiments.

[0024] Before introducing this technical solution, an example application scenario can be first described. This technical solution can be applied in scenarios where implantable medical devices need to be charged and powered by a wireless charging system.

[0025] Below, we first briefly describe one of the application fields (i.e., implantable devices) of the embodiments of the present application. An implantable neural stimulation system (an implantable medical system) mainly includes a stimulator implanted in the patient's body and a programmable device arranged outside the patient's body. Existing neuroregulatory technology mainly involves implanting electrodes at specific locations (i.e., target points) in the body through stereotactic surgery, and the stimulator implanted in the patient's body emits discharge pulses to the target point through the electrodes to regulate the electrical activity and function of the corresponding neural structures and networks, thereby improving symptoms and alleviating pain. Among them, the stimulator can be any one of an implantable neural electrical stimulation device, an implantable cardiac electrical stimulation system (also known as a pacemaker), an implantable drug delivery system (IDDS) and a lead adapter. Implantable neural stimulation devices include, for example, deep brain stimulation (DBS) system, implantable cortical nerve stimulation (CNS) system, implantable spinal cord stimulation (SCS) system, implantable sacral nerve stimulation (SNS) system, implantable vagus nerve stimulation (VNS) system, etc.

[0026] In some embodiments, the stimulator may include an implantable pulse generator (IPG), an electrode wire, and an extension wire arranged between the electrical pulse stimulation device and the electrode wire, and data interaction between the electrical pulse stimulation device and the electrode wire is achieved through the extension wire, and the electrical pulse stimulation device is arranged in the patient's body. In response to the program-controlled instructions sent by the program-controlled device, the energy supply unit provides controllable electrical stimulation energy to the tissue in the body, and delivers one or two controllable specific electrical stimulations to specific areas of the tissue in the body through the implanted extension wire and the electrode wire. The extension wire is used in conjunction with the electrical pulse stimulation device as a transmission medium for the electrical stimulation signal, and transmits the electrical stimulation signal generated by the electrical pulse stimulation device to the electrode wire. The electrode wire delivers electrical stimulation to specific areas of the tissue in the body through the electrode contacts thereon. The stimulator is provided with one or more electrode wires on one side or both sides, and a plurality of electrode contacts are provided on the electrode wire.

[0027] In other embodiments, the stimulator may include only an electrical pulse stimulation device and electrode leads. The electrical pulse stimulation device may be embedded in the patient's skull, and the electrode leads may be implanted in the patient's skull. In this case, the electrical pulse stimulation device and the electrode leads are directly connected, without the need for extension leads.

[0028] The electrode wire can be a nerve stimulation electrode, and the electrode wire delivers electrical stimulation to a specific area of ​​tissue in the body through a plurality of electrode contacts. The stimulator is provided with one or more electrode wires on one side or both sides, and a plurality of electrode contacts are provided on the electrode wire, and the electrode contacts can be arranged uniformly or non-uniformly in the circumference of the electrode wire. As an example, the electrode contacts can be arranged in an array of 4 rows and 3 columns (a total of 12 electrode contacts) in the circumference of the electrode wire. The electrode contacts can serve as stimulation contacts and / or collection contacts. The electrode contacts can, for example, be in the shape of a sheet, a ring, a point, or the like.

[0029] In some possible embodiments, the stimulated tissue in the body can be the patient's brain tissue, and the stimulated site can be a specific site of the brain tissue. When the patient's disease type is different, the stimulated site is generally different, and the number of stimulation contacts used (single source or multiple sources), the use of one or more (single channel or multiple channels) specific electrical stimulation signals, and the stimulation parameter data are also different. It can be considered that when the stimulation contacts used are multi-source, multi-channel (multi-channel), a larger amount of data will be generated compared to a single source, single channel.

[0030] The embodiments of the present application do not limit the types of diseases that can be treated, and can be diseases that are suitable for deep brain stimulation (DBS), spinal cord stimulation (SCS), pelvic stimulation, gastric stimulation, peripheral nerve stimulation, and functional electrical stimulation. Among them, the types of diseases that DBS can be used to treat or manage include, but are not limited to: spastic disorders (e.g., epilepsy), pain, migraine, mental illness (e.g., major depressive disorder (MDD)), bipolar disorder, anxiety, post-traumatic stress disorder, minor depression, obsessive-compulsive disorder (OCD), behavioral disorders, mood disorders, memory disorders, mental state disorders, movement 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 injuries.

[0031] The technical solution provided by the embodiment of the present invention is mainly applied to the field of implantable medical devices. Figure 1 ,like Figure 1 As shown in FIG, the implantable medical device mainly includes a wireless charging receiver, an electric pulse stimulation device, a stimulation electrode, and an electrode wire. The wireless charging receiver can receive and store the electric energy emitted by the external power transmitter to power the electric pulse stimulation device. The electric pulse stimulation device is implanted in the patient's body (such as the chest cavity, skull, etc.), and the electrode wire is connected to the electric pulse stimulation device through one end under the skin, and the other end is equipped with a stimulation electrode. Among them, the schematic diagram of the stimulation electrode can be seen in FIG. Figure 2 ,like Figure 2 As shown, the stimulation electrode includes at least one metal contact that outputs a stimulation source. These metal contacts can be circular or directional electrodes composed of multiple segmented electrode contacts. The stimulation electrode is implanted in a designated location in the patient's brain (such as a nucleus or neural tissue associated with the condition). The doctor sends programming parameters to the electrical pulse stimulation device through a programmable device. The electrical pulse stimulation device delivers electrical stimulation to at least one metal contact in the stimulation electrode via the electrode wire, causing the at least one metal contact to generate an electric field to treat the corresponding condition.

[0032] Among them, the wireless charging receiving end can be a receiving coil, which converts the energy of the external electric field into current based on the principle of magnetic induction. The electric pulse stimulation device can be a stimulator. The receiving coil is arranged inside the stimulator and connected to the battery inside the stimulator to transmit the converted current to the battery, thereby completing the charging of the battery.

[0033] During the treatment of patients through implantable medical devices, the power receiving end is required to provide energy. In practical applications, implantable medical devices have metal shells. Due to the presence of the metal shell, the implantable medical devices are prone to electromagnetic shielding effects when charging, resulting in low charging efficiency. In addition, the power receiving end needs to continuously send modulated signals to maintain communication, which requires the control unit of the power receiving end to be in a continuous working state, consuming a large amount of electricity, and affecting the battery life of the implantable medical device. The embodiment of the present invention aims to propose an implantable medical instrument that reduces the power consumption of the implantable medical instrument itself, thereby improving the battery life of the implantable medical instrument.

[0034] Example 1

[0035] Figure 3 This is a structural diagram of an implantable medical device provided by an embodiment of the present invention. This embodiment is applicable to the situation where the implantable medical device is charged and powered by a wireless charger.

[0036] like Figure 3 As shown, the implantable medical instrument 100 includes: a first control unit 101 , a wireless communication unit 102 and an energy receiving unit 103 .

[0037] The implantable medical device provided in this embodiment is charged in a wireless charging manner, and is charged via a wireless charger 200 .

[0038] Among them, the first control unit 101 is used to switch from the first working mode to the second working mode based on the current signal sending cycle, and update the current signal sending cycle based on the current charging status information of the energy receiving unit 103 in the second working mode, and send a trigger control signal to the wireless communication unit 102; wherein, the first control unit switches from the second working mode to the first working mode after sending the trigger control signal, and the resource consumption corresponding to the first working mode is less than the resource consumption corresponding to the second working mode; the wireless communication unit 102 is used to send the current charging status information to the wireless charger through a wireless communication message when receiving the trigger control signal, so that the wireless charger adjusts the energy transmission parameters transmitted to the implantable medical instrument based on the current charging status information; the energy receiving unit 103 is used to receive and store the charging energy transmitted by the wireless charger 200.

[0039] The energy receiving unit 103 may include an energy receiving coil, a rectifier circuit, and an energy storage device. The energy receiving coil is responsible for capturing energy from the external wireless charger 200 and converting it into alternating current. The rectifier circuit is responsible for converting the alternating current (AC) output by the receiving coil into direct current (DC) for use by subsequent circuits or the energy storage device. The energy storage device is responsible for storing the rectified energy and supplying power to the load when needed. Current charging status information refers to the charging status information of the energy receiving unit 103 during the current cycle. Charging status information refers to real-time or periodic monitoring data related to the energy reception, storage, and supply processes in the energy receiving unit 103, which is used to reflect the current operating status, energy storage level, and potential fault conditions of the energy receiving unit 103. Specifically, the current charging status information may include energy reception status information, rectification and conversion status information, energy storage status information, and protection and fault information. For example, the energy reception status information may specifically include: input power, which refers to the instantaneous power captured by the receiving coil and reflects the energy transmission efficiency. Input voltage / current refers to the AC parameters before the rectifier circuit, which is used to monitor whether energy reception is normal (such as whether the resonant frequency is reached). Coupling efficiency refers to the degree of energy transmission matching between the implantable medical device 100 and the wireless charger 200 (such as efficiency drop due to distance or offset). Rectification and conversion status information may specifically include: voltage / current after rectification, which refers to the real-time parameters of the DC output, which determines whether the rectifier circuit is operating normally. Conversion efficiency refers to the AC-DC conversion loss of the rectifier circuit (such as efficiency loss caused by diode voltage drop). Energy storage status information may specifically include: charging capacity, which refers to the current percentage of power in the energy storage device (such as a battery or supercapacitor) (such as a battery charged to 80%). Charging current / voltage refers to the parameters actually stored in the energy storage device, which is used for overcharge / over-discharge protection. Health status value refers to the aging degree of the energy storage device (such as the battery capacity decaying to 90% of the nominal value). System protection and fault information may specifically include: temperature information, which refers to the temperature of the coil, rectifier or energy storage device to prevent overheating damage. Error flag refers to the abnormal signal generated when abnormal conditions such as overvoltage, undervoltage, overcurrent, short circuit, etc. occur.

[0040] Among them, the current signal sending cycle refers to the signal sending cycle corresponding to the current loop execution process. The signal sending cycle refers to the time interval for the wireless communication unit 102 to periodically send data, that is, the length of time between two consecutive signal transmissions. The first working mode is different from the second working mode. For the implantable medical device 100, the resource consumption of the implantable medical device 100 working in the first working mode is lower than the resource consumption corresponding to the second working mode. The resource consumption refers to the computing, storage and power consumption resources occupied and consumed by the implantable medical device 100 when performing wireless charging related tasks. These resources mainly include: computing resources, storage resources, power consumption resources (operating current / energy consumption) and peripheral resources.

[0041] In this embodiment, in the first operating mode, at least one of the following components within the implantable medical device is in a low-power operating state: the central processing unit, the high-speed clock, with the high-speed clock source disabled, the radio frequency module, the peripheral interface, with non-essential peripheral interfaces disabled, the analog module, the low-speed clock, the timer, the general-purpose input / output interface, the power management module, and the static random access memory. This reduces the energy consumption of the components within the implantable medical device in the first operating mode.

[0042] Specifically, when the implantable medical device 100 is in the first working mode, the execution states of the various components within the implantable medical device 100 include:

[0043] (1) Central Processing Unit (CPU): stops running and enters sleep mode;

[0044] (2) High-speed clock (HF Clock): Turn off the high-speed clock source;

[0045] (3) RF Core: turns off the RF transceiver function and stops wireless communication;

[0046] (4) Peripheral interface: turn off unnecessary peripheral interfaces (such as SPI, I2C, UART, etc.);

[0047] (5) Analog module: turn off analog modules such as ADC and DAC;

[0048] (6) Low-speed clock (LF Clock): Keeps running and is used to drive the timer.

[0049] (7) Timer (RTC or GPT): keeps running, used to count the time interval of the current signal sending cycle, and wake up the first control unit 101, where the first control unit 101 can be a central processing unit.

[0050] (8) General Purpose Input / Output (GPIO) wake-up function: maintains the working state and is used to detect external events (such as abnormal signals).

[0051] (9) Power management module: maintains working status and is used to monitor the power status.

[0052] (10) Static Random-Access Memory (SRAM): retains the working status of part of the SRAM and is used to store the current charging status information of the energy receiving unit 103.

[0053] When the implantable medical device 100 is in the second working mode, the execution states of the various components within the implantable medical device 100 include:

[0054] (1) Central Processing Unit (CPU): Start running;

[0055] (2) High-speed clock (HF Clock): Enable the high-speed clock source;

[0056] (3) RF Core: Enables RF transceiver function and wireless communication.

[0057] (4) Peripheral interface: Enable non-essential peripheral interfaces (such as SPI, I2C, UART, etc.);

[0058] (5) Analog module: Enable analog modules such as ADC and DAC;

[0059] (6) Low-speed clock (LF Clock): Keeps running and is used to drive the timer.

[0060] (7) Timer (RTC or GPT): keeps running, is used to count the time interval of the current signal sending cycle, and wakes up the first control unit 101.

[0061] (8) General Purpose Input / Output (GPIO) wake-up function: maintains the working state and is used to detect external events (such as abnormal signals).

[0062] (9) Power management module: maintains working status and is used to monitor the power status.

[0063] (10) Static Random-Access Memory (SRAM): retains the working status of all SRAMs and is used to store the current charging status information of the energy receiving unit 103.

[0064] It can be seen from this that for the implantable medical device 100, compared with the second working mode, in the first working mode, the working states of the central processing unit (CPU), high-speed clock (HF Clock), radio frequency module (RF Core), peripheral interface, analog module and static random access memory are different. In the first working mode, these components are set to a working state of temporarily stopping operation or partially operating, which can effectively reduce the power consumption of the implantable medical device 100.

[0065] That is to say, in the first working mode, the implantable medical device 100 is in a low-power working state. In this mode, except for the charging-related modules inside the implantable medical device, the other modules are in a dormant state. This can greatly reduce the power consumption inside the implantable medical device 100 during the charging process, thereby improving the charging efficiency and utilization rate.

[0066] It should be noted that during the wireless charging process, when the implantable medical device 100 is not in a working state, it can enter the first working mode; when the implantable medical device 100 is in a working state (i.e., delivering pulse stimulation to the electrode), it does not need to enter the first working mode. This ensures that during the charging process, the implantable medical device 100 can achieve stimulation while charging, thereby improving the user experience and treatment effect.

[0067] Among them, the trigger control signal is a digital or analog signal sent by the first control unit 101, which is used to activate or control the data transmission function of the wireless module. The wireless communication message refers to the standardized data packet sent by the wireless communication unit 102 to the wireless charger 200, and the standardized data packet contains the current charging status information of the energy receiving unit 103. The energy transmission parameter refers to the key parameter for controlling the energy transmission characteristics that is dynamically adjusted by the wireless charger 200 based on the current charging status information fed back by the implanted device. For example, the energy transmission parameter can be the energy transmission power, measured in watts (W). Charging energy refers to the total amount of electrical energy that is transmitted from the wireless charger 200 to the wireless charging receiving end through an electromagnetic field (such as magnetic field coupling, electromagnetic induction), and is ultimately stored or utilized by the receiving end circuit.

[0068] Optionally, when the implantable medical device enters the charging state, the first control unit controls the implantable medical device to enter the first operating mode.

[0069] In a specific application process, when the implantable medical device 100 is charged for the first time, the implantable medical device 100 can operate in the first operating mode. At this time, the current signal transmission period can be a preset default period (for example, the preset default period is 2 seconds). Based on this, after a time interval of the preset default period, it switches to the second operating mode. In the second operating mode, the first control unit 101 can obtain the current charging status information of the energy receiving unit 103 and update the preset default period based on the current charging status information to obtain an updated current signal transmission period (for example, the preset default period is 3 seconds). At the same time, the first control unit 101 sends a trigger control signal to the wireless communication unit 102 in the second working mode, so that the wireless communication unit 102 can communicate with the wireless charger 200 when receiving the trigger control signal, thereby realizing intermittent communication between the implantable medical device 100 and the wireless charger based on the wireless communication unit, ensuring the stability and reliability of communication information transmission during the entire charging process, and thus ensuring high-quality charging output. In this way, in the first working mode, the wireless communication unit 102 can be in a dormant state, avoiding the wireless communication unit 102 being in a working state for a long time, and reducing energy consumption in the intermittent communication mode.

[0070] After the first control unit 101 completes the updating of the current signal transmission cycle and completes the task of sending a trigger control signal to the wireless communication unit 102, it immediately switches from the second working mode to the first working mode. Alternatively, when the first control unit detects that the implantable medical device has entered the charging state, in this case, the implantable medical device can be controlled to operate in the first working mode. After the first control unit completes the working mode switching operation, the low-speed clock starts timing. When the timing reaches the current signal transmission cycle, that is, 3 seconds, it repeats the execution steps of switching from the first working mode to the second working mode, updating the current signal transmission cycle based on the current charging status information of the energy receiving unit 103 in the second working mode, and sending a trigger control signal to the wireless communication unit 102, and then immediately switching to the second working mode.

[0071] For the wireless communication unit 102, whenever the wireless communication unit 102 receives the trigger control signal sent by the first control unit 101, it can simultaneously obtain the current charging status information of the energy receiving unit 103, and encapsulate the current charging status information into a wireless communication message, and then send the wireless communication message to the wireless charger 200.

[0072] In this embodiment, the purpose of sending the wireless communication message containing the current charging status information to the wireless charger 200 is to enable the wireless charger 200 to adjust the energy transmission parameters transmitted to the energy receiving unit 103 according to the current charging status information carried in the wireless communication message when receiving the wireless communication message, so that charging energy can be transmitted to the implantable medical device 100 according to the adjusted energy transmission parameters.

[0073] In this embodiment, the energy receiving unit 103 can receive and store the charging energy transmitted by the wireless charger 200 .

[0074] In this embodiment, the wireless communication unit 102 may optionally use a wireless communication unit in the 300MHz to 3GHz frequency band, and further, a 403MHz wireless communication unit may be selected. The 403MHz wireless communication unit 102 is a wireless data transmission device operating in the 403MHz frequency band. This frequency band belongs to the Sub-1GHz frequency band and has the characteristics of strong penetration and good anti-interference ability. Due to the low data rate, the 403MHz module usually adopts a sleep and wake-up mechanism, and the average current can be as low as microamperes, which can effectively reduce the power consumption of the implantable medical device 100.

[0075] The technical solution of an embodiment of the present invention provides an implantable medical instrument, a transmitter and a wireless charging method, wherein the implantable medical instrument is charged by a wireless charger, mainly including: a first control unit, used to switch from a first working mode to a second working mode based on a current signal sending cycle, and update the current signal sending cycle based on current charging status information in the second working mode, and send a trigger control signal to a wireless communication unit; wherein the first control unit switches from the second working mode to the first working mode after sending the trigger control signal, and the resource consumption corresponding to the first working mode is less than the resource consumption corresponding to the second working mode; the wireless communication unit is used to send the current charging status information to the wireless charger through a wireless communication message when receiving the trigger control signal, so that the wireless charger adjusts the energy transmission parameters transmitted to the implantable medical instrument based on the current charging status information; an energy receiving unit is used to receive and store the charging energy transmitted by the wireless charger.

[0076] The implantable medical device proposed in the technical solution of this embodiment, on the one hand, uses a control unit within the implantable medical device to intermittently communicate data with a wireless charger by controlling a wireless communication unit. Because wireless signals have strong penetrating power, they can effectively overcome the shielding effect of the metal casing on electromagnetic waves, improving the device's energy reception efficiency and, consequently, charging efficiency. Furthermore, the control unit within the implantable medical device can periodically switch operating modes, allowing it to operate in a low-power mode most of the time, reducing the device's own power consumption and thereby improving its battery life.

[0077] Example 2

[0078] Based on the above embodiment, this embodiment further refines the functions of the first control unit 101 in the implantable medical device. The specific implementation methods can be found in the technical solution of this embodiment. The technical terms that are the same as or corresponding to the above embodiment are not repeated here.

[0079] In this embodiment, the implantable medical device 100 includes a first control unit 101 , a wireless communication unit 102 , and an energy receiving unit 103 .

[0080] Among them, the first control unit 101 is used to switch from the first working mode to the second working mode based on the current signal sending cycle, and update the current signal sending cycle based on the current charging status information of the energy receiving unit 103 in the second working mode, and send a trigger control signal to the wireless communication unit 102; wherein, the control unit switches from the second working mode to the first working mode after sending the trigger control signal, and the resource consumption corresponding to the first working mode is less than the resource consumption corresponding to the second working mode; the wireless communication unit 102 is used to send the current charging status information to the wireless charger 200 through a wireless communication message when receiving the trigger control signal, so that the wireless charger 200 adjusts the energy transmission parameters transmitted to the energy receiving unit 103 based on the current charging status information; the energy receiving unit 103 is used to receive and store the charging energy transmitted by the wireless charger 200.

[0081] Optionally, the current charging status information may include charging current, coil temperature, and charging capacity, where charging current refers to the average input current of the energy receiving coil, coil temperature refers to the average temperature of the energy receiving coil, and charging capacity refers to the current percentage of power in the energy storage device. On this basis, the specific implementation method for the first control unit 101 to update the current signal transmission cycle based on the current charging status information of the energy receiving unit 103 may include:

[0082] The charging current to be processed is determined based on the charging current corresponding to at least one sampling time point of the energy receiving unit 103 within the preset time period, and the coil temperature change rate is determined based on the coil temperature corresponding to at least one sampling time point within the preset time period.

[0083] The preset duration is a pre-set time period, the pending charging current is a current value determined based on at least one charging current, and the coil temperature change rate is a rate at which the temperature of the receiving coil in the energy receiving unit 103 increases within a preset duration.

[0084] In this embodiment, when the first control unit 101 switches from the first operating mode to the second operating mode, it can obtain charging current values ​​corresponding to one or more sampling time points within a preset time period before the current moment, thereby determining the charging current to be processed based on these charging current values. For example, the average value of these charging current values ​​can be determined as the charging current to be processed, the maximum value of these charging current values ​​can be determined as the charging current to be processed, or the minimum value of these charging current values ​​can be determined as the charging current to be processed. When the first control unit 101 switches from the first operating mode to the second operating mode, it can also obtain the first coil temperature value at the current moment and the second coil temperature value at a preset time period before the current moment, thereby determining the coil temperature change rate based on the first coil temperature value and the second coil temperature value.

[0085] Based on the charging current to be processed and the coil temperature change rate, charging attribute information corresponding to the energy receiving unit 103 is determined.

[0086] The charging attribute information is used to represent the charging efficiency of the energy receiving unit 103 .

[0087] In this embodiment, the charging attribute information includes a normal charging attribute, a high-efficiency charging attribute, or a low-efficiency charging attribute.

[0088] In this embodiment, the charging attribute information corresponding to the energy receiving unit 103 can be determined based on the charging current to be processed, the coil temperature change rate, and preset judgment conditions.

[0089] Specifically, if the charging current to be processed meets the preset charging current threshold and the coil temperature change rate is less than or equal to the first preset temperature change rate, the charging attribute information corresponding to the energy receiving unit 103 is determined to be a high-efficiency charging attribute; if the charging current to be processed meets the preset charging current threshold and the coil temperature change rate is between the first preset temperature change rate and the second preset temperature change rate, the charging attribute information corresponding to the energy receiving unit 103 is determined to be a normal charging attribute; if the charging current to be processed does not meet the preset charging current threshold, and / or the coil temperature change rate is greater than or equal to the second preset temperature change rate, the charging attribute information corresponding to the energy receiving unit 103 is determined to be a high-efficiency charging attribute.

[0090] The preset charging current threshold is a preset current threshold. The first preset temperature change rate and the second preset temperature change rate are both preset temperature change rates, and the first preset temperature change rate is less than the second preset temperature change rate. In specific applications, the preset charging current threshold, the first preset temperature change rate, and the second preset temperature change rate can all be adjusted based on actual conditions.

[0091] In this embodiment, a preset judgment condition can be constructed by presetting the charging current threshold, the first preset temperature change rate, and the second preset temperature change rate. Thus, on the basis of obtaining the charging current to be processed and the coil temperature change rate, the charging current to be processed and the coil temperature change rate are judged and processed by the preset judgment condition to determine which charging attribute information the energy receiving unit 103 corresponds to.

[0092] Furthermore, based on the charging attribute information and / or the charging power, the current signal sending period is updated.

[0093] In this embodiment, the signal transmission period can be related to the charging attribute information. For example, when the charging attribute information is normal charging, the first control unit 101 can execute the control task at a preset default period (e.g., 2 seconds). When the charging attribute information is high-efficiency charging, the charging situation is relatively stable, and the first control unit 101 can execute the control task at a period longer than the preset default period (e.g., 4 seconds). When the charging attribute information is low-efficiency charging, the charging situation is relatively unstable, and the first control unit 101 can execute the control task at a period shorter than the preset default period (e.g., 0.5 seconds). In addition, the signal transmission period can be related to the charging level. For example, when the charging level is low, such as below 50%, the first control unit 101 can operate at a lower signal transmission period. At this time, the battery level is low and frequent monitoring of the charging level is not required. When the battery level exceeds 50% or higher, in order to avoid heating problems caused by overcharging, feedback notifications can be sent at a higher frequency, so that the wireless charger 200 can adjust the charging strategy in a timely manner, such as reducing the charging power or stopping charging.

[0094] Optionally, a specific implementation method of updating the current signal sending period based on the charging attribute information and / or the charging power may include: updating the current signal sending period based on the charging attribute information and / or the charging power, and the signal sending period mapping relationship.

[0095] The signal transmission period mapping relationship includes a correspondence between charging attribute information and / or charging power information and a preset signal transmission period. It is understood that the signal transmission period mapping relationship is a preset rule table or function relationship that defines how to dynamically adjust the signal transmission period for status feedback sent by the implanted device to the wireless charger based on at least one of the charging attribute information and / or charging power.

[0096] In this embodiment, the first control unit dynamically adjusts the current signal transmission period based on the current charging attribute information and / or charging power, combined with a preset signal transmission period mapping relationship, such as a table or function of optimal communication intervals corresponding to different charging states. For example, when the battery power is low, the mapping relationship may specify a shorter transmission period, such as communicating once every 10 seconds, to ensure a quick response and power increase for the charger. When the battery power is nearly full or the temperature is too high, the signal transmission period is switched to a longer period, such as communicating once every 60 seconds, to reduce communication energy consumption and prioritize the execution of safety policies. This adaptive adjustment based on real-time status optimizes charging efficiency while taking into account system security and energy consumption management.

[0097] Optionally, the signal sending cycle mapping relationship may include: if the charging power is less than a preset charging threshold and the charging attribute information is a normal charging attribute, then the preset default cycle is determined as the current signal sending cycle; if the charging power is less than the preset charging threshold and the charging attribute information is a high-efficiency charging attribute, then the first preset cycle is determined as the current signal sending cycle; if the charging power is greater than or equal to the preset charging threshold, or the charging attribute information is an inefficient charging attribute, then the second preset cycle is determined as the current signal sending cycle.

[0098] The first preset period is longer than the default period, and the second preset period is shorter than the default period. In specific applications, the lengths of the first and second preset periods can be adjusted based on actual conditions.

[0099] In this embodiment, the current signal transmission period may be updated only according to the charging attribute information, or only according to the charging power, or according to both the charging attribute information and the charging power.

[0100] In a specific application process, the first control unit is further used to: when it is determined according to the current charging state that the current charging efficiency does not meet the preset charging efficiency condition, generate a prompt information for adjusting the charging position, and send the prompt information for adjusting the charging position to the wireless charger.

[0101] The preset charging efficiency condition refers to a pre-set threshold or standard used to determine whether the wireless charging process is in a relatively optimal state. The charging position adjustment prompt information refers to guiding feedback information sent to the user when the first control unit detects that the current wireless charging efficiency does not meet the preset standard, prompting the user to optimize the physical location or placement of the wireless charger.

[0102] In this embodiment, during the charging process of the implantable medical device 100, the first control unit 101 monitors the current charging status in real time, such as parameters such as energy receiving power, charging rate or temperature, and converts the current charging efficiency based on these charging status information. Subsequently, the current charging efficiency is compared with the preset charging efficiency conditions; if it is detected that the actual efficiency does not meet the standard, a specific prompt information for adjusting the charging position is automatically generated, such as "Please move the charger 3 cm to the left" or "The charging distance is too far, please keep it close to the body surface", etc. Subsequently, the prompt information for adjusting the charging position can be fed back to the wireless charger to prompt the user to adjust the spatial position of the wireless charger through the wireless charger.

[0103] According to a technical solution of an embodiment of the present invention, a first control unit in an implantable medical device is further configured to determine a pending charging current based on the charging current of the energy receiving unit corresponding to at least one sampling time point within a preset time period, and to determine a coil temperature change rate based on the coil temperature corresponding to at least one sampling time point within the preset time period; determine charging attribute information corresponding to the energy receiving unit based on the pending charging current and the coil temperature change rate; and update a current signal transmission period based on the charging attribute information and / or the charging power; wherein the charging attribute information includes a normal charging attribute, a high-efficiency charging attribute, or an inefficient charging attribute. According to the technical solution of this embodiment, the first control unit in the implantable medical device can dynamically adjust the signal transmission period of the first control unit based on the charging current, coil temperature, and charging power in the current charging status information. Thus, data communication between the receiving end and the transmitting end is intermittently achieved based on the dynamically adjusted signal transmission period, and the charging status between the receiving end and the transmitting end can be adjusted in a timely manner, thereby ensuring the stability and reliability of the wireless charging system.

[0104] Example 3

[0105] Figure 4 This is a structural diagram of a wireless charger provided by an embodiment of the present invention. This embodiment is applicable to the situation where an implantable medical device is charged and powered by a wireless charging system including an implantable medical device 100 and a wireless charging device.

[0106] like Figure 4 As shown, the wireless charger 200 includes: a second control unit 201 and an energy transmitting unit 202 .

[0107] Among them, the second control unit 201 is used to receive the wireless communication message sent by the wireless communication unit 102 of the implantable medical device 100, and adjust the energy transmission parameters based on the current charging status information carried in the wireless communication message; the energy transmission unit 202 is used to transmit charging energy to the implantable medical device 100 based on the adjusted energy transmission parameters.

[0108] In this embodiment, the second control unit 201 in the wireless charger 200 can receive wireless communication messages sent by the wireless communication unit 102 of the implantable medical device 100 and adjust energy transmission parameters based on the current charging status information carried in the wireless communication messages. Thus, the energy transmission unit 202 can transmit charging energy to the implantable medical device 100 based on the adjusted energy transmission parameters.

[0109] Optionally, the current charging status information includes at least one of: charging current, charging voltage, and coil temperature. The charging current refers to the average input current of the energy receiving coil, the coil temperature refers to the average temperature of the energy receiving coil, and the charging capacity refers to the current capacity percentage of the energy storage device. Based on this, the specific implementation method for the second control unit 201 to adjust the energy transmission parameters according to the current charging status information carried in the wireless communication message may include:

[0110] Based on at least one of the charging current, the charging voltage, and the coil temperature, PID control is performed on the actual energy transmission parameters of the wireless charger 200 to obtain adjusted energy transmission parameters.

[0111] The actual energy transmission parameter refers to the power value currently actually output by the energy transmission unit 202 .

[0112] In this embodiment, the current actual energy transmission parameters (i.e., the actual power being output by the transmitter) are calculated using one or more parameters including the charging current, charging voltage, or coil temperature in the current charging status information. The PID control algorithm (proportional-integral-differential control) is then used to compare the actual power with the target power, dynamically adjust the transmitter's drive signal (such as voltage, frequency, or duty cycle), and ultimately output the adjusted energy transmission parameters to ensure that the wireless charger 200 can transmit energy stably and efficiently while avoiding the risk of overheating or overload.

[0113] Optionally, the wireless charger 200 provided in this embodiment of the present invention further includes a display and a voice prompt unit. In specific applications, the second control unit is further configured to, upon receiving a prompt message for adjusting the charging position from an implantable medical device, control the display to display the prompt message and / or control the voice prompt unit to play the prompt message.

[0114] In this embodiment, when the wireless charger 200 receives the prompt information for adjusting the charging position sent by the implantable medical device 100, the prompt content can be intuitively displayed in the form of graphics and text on the display, and / or clear position adjustment instructions can be played through a voice prompt, thereby guiding the user to restore an efficient charging state through physical position optimization, ensuring the stability and safety of energy transmission.

[0115] A wireless charger provided in an embodiment of the present invention includes: a second control unit and an energy transmission unit; the second control unit is configured to receive wireless communication messages sent by the wireless communication unit 102 of an implantable medical device and adjust energy transmission parameters based on the current charging status information carried in the wireless communication messages; and the energy transmission unit is configured to transmit charging energy to the implantable medical device based on the adjusted energy transmission parameters. The technical solution of this embodiment proposes a wireless charger that can receive wireless communication messages sent by an implantable medical device and dynamically adjust the output of the transmitter based on the current charging status information in the wireless communication messages. This allows for timely adjustment of the energy transmission power between the receiving and transmitting ends, ensuring efficient and safe energy transmission.

[0116] Example 4

[0117] Figure 5 This is a schematic diagram of an implantable charging system according to a fourth embodiment of the present invention. This embodiment is applicable to charging and powering implantable medical devices via a wireless charger. The implantable charging system 10 includes: an implantable medical device 100 according to any of the aforementioned embodiments; and a wireless charger 200 according to any of the aforementioned embodiments.

[0118] During specific applications of the implantable charging system 10, for the implantable medical device 100, the first control unit is configured to switch from the first operating mode to the second operating mode based on the current signal transmission cycle, and to update the current signal transmission cycle based on the current charging status information in the second operating mode, and to send a trigger control signal to the wireless communication unit. After the first control unit completes sending the trigger control signal, it switches from the second operating mode to the first operating mode, and the resource consumption corresponding to the first operating mode is less than the resource consumption corresponding to the second operating mode. Upon receiving the trigger control signal, the wireless communication unit is configured to send the current charging status information to the wireless charger 200 via a wireless communication message, so that the wireless charger 200 adjusts the energy transmission parameters transmitted to the implantable medical device 100 based on the current charging status information.

[0119] The energy receiving unit is configured to receive and store the charging energy transmitted by the wireless charger 200 .

[0120] For the wireless charger 200, the second control unit is used to receive the wireless communication message sent by the wireless communication unit of the implantable medical device 100, and adjust the energy transmission parameters based on the current charging status information carried in the wireless communication message; the energy transmission unit is used to transmit charging energy to the implantable medical device 100 based on the adjusted energy transmission parameters.

[0121] The technical solution of the embodiments of the present invention provides an implantable medical device, a transmitter, and a wireless charging method, wherein the implantable medical device is charged via a wireless charger. The method mainly includes: a first control unit, configured to switch from a first operating mode to a second operating mode based on a current signal transmission cycle, and in the second operating mode, update the current signal transmission cycle based on current charging status information, and send a trigger control signal to a wireless communication unit. After the first control unit sends the trigger control signal, the first operating mode switches to the first operating mode, and the resource consumption corresponding to the first operating mode is less than the resource consumption corresponding to the second operating mode. The wireless communication unit, upon receiving the trigger control signal, transmits the current charging status information to the wireless charger via a wireless communication message, so that the wireless charger adjusts the energy transmission parameters transmitted to the implantable medical device based on the current charging status information. The energy receiving unit, configured to receive and store the charging energy transmitted by the wireless charger, is used to receive and store the charging energy transmitted by the wireless charger. The implantable medical device provided by the technical solution of this embodiment, on the one hand, controls the wireless communication unit to achieve intermittent data communication with the wireless charger. Because the wireless signal has strong penetrating power, it can effectively overcome the shielding effect of the metal shell on electromagnetic waves, thereby improving the energy reception efficiency of the device and thus improving the charging efficiency. On the other hand, the control unit in the implantable medical instrument can periodically switch the working mode, which makes the control unit in the implantable medical instrument in a low-power working mode most of the time, reducing the power consumption of the implantable medical instrument itself, thereby improving the battery life of the implantable medical instrument.

[0122] Note that the above are only preferred embodiments of the present invention and the technical principles employed. Those skilled in the art will appreciate that the present invention is not limited to the specific embodiments herein, and that various obvious changes, readjustments, and substitutions are possible for those skilled in the art without departing from the scope of protection of the present invention. Therefore, although the present invention has been described in detail through the above embodiments, the present invention is not limited to the above embodiments and may include many other equivalent embodiments without departing from the scope of the present invention. The scope of the present invention is determined by the scope of the appended claims.

Claims

1. An implantable medical device, characterized in that: The implantable medical instrument is charged by a wireless charger, and the implantable medical instrument includes: a first control unit, a wireless communication unit and an energy receiving unit; wherein, The first control unit is configured to switch from the first operating mode to the second operating mode based on the current signal transmission cycle, update the current signal transmission cycle based on the current charging state information in the second operating mode, and send a trigger control signal to the wireless communication unit; wherein the first control unit switches from the second operating mode to the first operating mode after completing the sending of the trigger control signal, and the resource consumption corresponding to the first operating mode is less than the resource consumption corresponding to the second operating mode; The wireless communication unit is configured to transmit the current charging status information to the wireless charger via a wireless communication message upon receiving the trigger control signal, so that the wireless charger adjusts energy transmission parameters transmitted to the implantable medical device based on the current charging status information; The energy receiving unit is used to receive and store the charging energy transmitted by the wireless charger.

2. The implantable medical device according to claim 1, wherein: When the implantable medical device enters a charging state, the first control unit controls the implantable medical device to enter a first operating mode.

3. The implantable medical device according to claim 1, wherein: The current charging state information includes charging current, coil temperature, and charging power. The first control unit is further configured to: Determining a charging current to be processed based on a charging current of the energy receiving unit corresponding to at least one sampling time point within a preset time period, and determining a coil temperature change rate based on a coil temperature corresponding to at least one sampling time point within the preset time period; determining charging attribute information corresponding to the energy receiving unit based on the to-be-processed charging current and the coil temperature change rate; Based on the charging attribute information and / or the charging power, a current signal sending period is updated.

4. The implantable medical device according to claim 3, wherein: The first control unit is further configured to: Based on the charging attribute information and / or the charging power, and the signal transmission cycle mapping relationship, the current signal transmission cycle is updated; wherein the signal transmission cycle mapping relationship includes the correspondence between the charging attribute information and / or the charging power information and the preset signal transmission cycle.

5. The implantable medical device according to claim 3, wherein: The charging attribute information includes a normal charging attribute, a high-efficiency charging attribute, or a low-efficiency charging attribute. The first control unit is further configured to: If the to-be-processed charging current satisfies a preset charging current threshold, and the coil temperature change rate is less than or equal to a first preset temperature change rate, the charging attribute information corresponding to the energy receiving unit is determined to be a high-efficiency charging attribute; If the to-be-processed charging current satisfies a preset charging current threshold, and the coil temperature change rate is between a first preset temperature change rate and a second preset temperature change rate, then the charging attribute information corresponding to the energy receiving unit is determined to be a normal charging attribute; wherein the first preset temperature change rate is less than the second preset temperature change rate; If the to-be-processed charging current does not meet the preset charging current threshold, and / or the coil temperature change rate is greater than or equal to the second preset temperature change rate, the charging attribute information corresponding to the energy receiving unit is determined to be an inefficient charging attribute.

6. The implantable medical device according to claim 4, wherein: The signal transmission period mapping relationship includes: If the charging amount is less than the preset charging threshold and the charging attribute information indicates a normal charging attribute, the preset default period is determined as the current signal sending period; If the charging power is less than the preset charging threshold and the charging attribute information is a high-efficiency charging attribute, a first preset period is determined as the current signal sending period; wherein the length of the first preset period is greater than the preset default period; If the charging power is greater than or equal to the preset charging threshold, or the charging attribute information is an inefficient charging attribute, the second preset period is determined as the current signal sending period; wherein the time length of the second preset period is less than the preset default period.

7. The implantable medical device according to claim 1, wherein: In the first working mode, at least one of the following components inside the implantable medical instrument is in a low-power working state: central processing unit, high-speed clock, high-speed clock source turned off, radio frequency module, peripheral interface: non-essential peripheral interface turned off, analog module, low-speed clock, timer, general input / output interface, power management module and static random access memory.

8. The implantable medical device according to claim 1, wherein: The wireless communication unit uses a wireless communication unit in the 300MHz to 3GHz frequency band.

9. The implantable medical device according to claim 1, wherein: The implantable medical instrument further includes: the first control unit, further configured to: When it is determined according to the current charging state that the current charging efficiency does not meet the preset charging efficiency condition, a charging position adjustment prompt message is generated and sent to the wireless charger.

10. A wireless charger, characterized in that: include: The second control unit and the energy emission unit; wherein, The second control unit is configured to receive a wireless communication message sent by a wireless communication unit of the implantable medical instrument, and adjust the energy transmission parameters based on the current charging state information carried in the wireless communication message; The energy transmission unit is used to transmit charging energy to the implantable medical device based on the adjusted energy transmission parameters.

11. The wireless charger according to claim 10, wherein: The current charging status information includes: at least one of a charging current, a charging voltage, and a coil temperature. The second control unit is further used to perform PID control on the actual energy emission parameters based on at least one of the charging current, the charging voltage, and the coil temperature to obtain adjusted energy emission parameters.

12. The wireless charger according to claim 10, wherein: The implantable medical instrument further includes: a display and a voice prompt unit, and the second control unit is further used to: When receiving the charging position adjustment prompt information sent by the implantable medical device, the display is controlled to display the charging position adjustment prompt information, and / or the voice prompt unit is controlled to play the charging position adjustment prompt information.

13. An implantable charging system, characterized in that: include: An implantable medical device according to any one of claims 1 to 9 implanted into a user's body; And, the wireless charger according to any one of claims 10 to 12.

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