In vitro charging method and device for active implantable medical device

Abstract

The present application provides an in vitro charging method and apparatus for an active implantable medical device, relating to the technical field of medical devices. A first voltage value and a second voltage value are obtained respectively, and the first voltage value and the second voltage value are compared with a frequency adjustment scale value and a pulse width adjustment scale respectively to obtain a frequency compression ratio and a pulse width compression ratio. Then, a frequency compression sequence and a pulse width compression sequence are obtained through the frequency compression ratio and the pulse width compression ratio. A frequency compression ratio range and a pulse width compression ratio range are judged and selected based on the product of a real-time third voltage value and a second current value of an in vivo device. Finally, a target frequency and a target pulse width are selected within the target frequency range and the target pulse width range based on the real-time frequency compression ratio and the pulse width compression ratio at the frequency point, thereby determining a charging intensity that matches the intensities of the in vivo device with those of the in vitro device.

Description

Technical Field

[0001] The present application relates to the field of medical device technology, and in particular to an in vitro charging method and device for an active implantable medical device. Background Art

[0002] Active implantable medical devices are medical instruments implanted in the human body for a long time, including pacemakers, various types of nerve stimulators, muscle stimulators, etc. Active implantable medical devices deliver pulse stimulation signals to the target treatment area of ​​the human body through implanted electrodes to achieve the purpose of treatment.

[0003] Active implantable medical devices typically consist of an internal device and an external device. The internal device houses a battery and a receiving coil, while the external device houses a charging head. When charging the internal device's battery, the charging head must be aligned with the receiving coil for wireless charging.

[0004] However, because the internal device is located inside the human body, the exact position of the receiving coil cannot be observed. When charging the internal device's battery, the charging head may not be accurately aligned with the receiving coil, resulting in unbalanced power transfer during wireless charging. In other words, the charging intensity in the internal device does not match the charging intensity in the external device. Summary of the Invention

[0005] The embodiments of the present application provide an in vitro charging method and apparatus for an active implantable medical device, which selects a suitable target frequency and target pulse width based on the real-time frequency compression ratio and pulse width compression ratio, thereby determining the charging intensity that matches the in vivo device with the in vitro device.

[0006] The present invention provides a method for charging an active implantable medical device in vitro, the method comprising the following steps:

[0007] Obtain a first voltage value and a second voltage value, where the first voltage value is the coil voltage value corresponding to each frequency point within the frequency adjustment range when the charger is operating, and the second voltage value is the coil voltage value corresponding to each pulse width within the frequency adjustment range when the charger is operating;

[0008] The frequency compression ratio is obtained by ratioing the first voltage value to the frequency adjustment scale value corresponding to the frequency point, where the frequency adjustment scale value refers to the coil voltage value corresponding to each frequency point of the charger under no-load conditions;

[0009] The second voltage value is compared with the pulse width adjustment scale value corresponding to its pulse width to obtain the pulse width compression ratio, where the pulse width adjustment scale value refers to the coil voltage value corresponding to each pulse width of the charger at no load and center frequency;

[0010] According to the frequency compression ratio at each frequency point and the pulse width compression ratio at each pulse width, a frequency compression ratio sequence and a pulse width compression ratio sequence within the frequency adjustment range are obtained respectively;

[0011] Acquiring a third voltage value and a second current value in real time; wherein the third voltage value is a voltage value of a receiving coil of the in-vivo device, and the second current value is a current value of the receiving coil of the in-vivo device;

[0012] Determining a frequency compression ratio selection range and a pulse width compression ratio selection range according to a product of the third voltage value and the second current value, and selecting a frequency compression ratio range and a pulse width compression ratio range from the frequency compression ratio sequence and the pulse width compression ratio sequence respectively;

[0013] The corresponding target frequency range and target pulse width range are obtained according to the frequency compression ratio range and the pulse width compression ratio range.

[0014] The target frequency and target pulse width are selected within the target frequency range and target pulse width range according to the real-time frequency compression ratio and pulse width compression ratio at the frequency point to determine the charging intensity.

[0015] In a feasible implementation, selecting a target frequency and a target pulse width within a target frequency range and a target pulse width range according to a real-time frequency compression ratio and a pulse width compression ratio at a frequency point includes:

[0016] The frequency compression ratio range and the pulse width compression ratio range are divided into at least 5 intervals, and the target frequency range and the target pulse width range are divided into at least 5 intervals.

[0017] Determine a third interval corresponding to the target frequency range and a fourth interval corresponding to the target pulse width range according to the first interval of the frequency compression ratio range and the second interval of the pulse width compression ratio range of the real-time frequency compression ratio and pulse width compression ratio of the frequency point;

[0018] When the ranges of the first interval and the second interval are smaller than the preset value, the target frequency and the target pulse width are selected in the third interval and the fourth interval.

[0019] In a feasible implementation, the in vitro charging method further includes:

[0020] Acquire a first current value at intervals of a first time period, where the first current value is a coil current value of the charging head;

[0021] When the changes between two adjacent first current values ​​obtained exceed 20%, the target frequency and target pulse width are re-determined to change the charging intensity.

[0022] In a feasible implementation, when the change trend of the product value of the third voltage value and the second current value is increasing, the time interval for adjusting the target frequency and the target pulse width is increased;

[0023] When the variation trend of the product value of the third voltage value and the second current value is decreasing, the time interval for adjusting the target frequency and the target pulse width is reduced.

[0024] In a feasible implementation, the in vitro charging method further includes:

[0025] Obtaining a first temperature value and a second temperature value, where the first temperature is the temperature of the coil of the charging head; and the second temperature is the temperature of the receiving coil of the in-vivo device;

[0026] When the first temperature value exceeds the upper threshold of the first temperature range, or the second temperature value exceeds the upper threshold of the second temperature range, charging is stopped.

[0027] In a feasible implementation, the in vitro charging method further includes:

[0028] When the first temperature value is lower than a lower threshold value of the first temperature range, and the second temperature value is lower than a lower threshold value of the second temperature range, charging is resumed.

[0029] In a feasible implementation, the in vitro charging method further includes:

[0030] When the first current value has an increasing trend, lowering the upper threshold of the first temperature range and lowering the lower threshold of the first temperature range;

[0031] When the change trend of the first current value is decreasing, the upper threshold of the first temperature range is adjusted upward, and the lower threshold of the first temperature range is adjusted upward.

[0032] In a feasible implementation, the in vitro charging method further includes:

[0033] When the second current value has an increasing trend, lowering the upper threshold of the second temperature range and lowering the lower threshold of the second temperature range;

[0034] When the variation trend of the second current value is decreasing, the upper threshold of the second temperature range is adjusted upward, and the lower threshold of the second temperature range is adjusted upward.

[0035] In a second aspect, an embodiment of the present application further provides an in vitro charging device for an active implantable medical device, comprising a charging head, which uses the above-mentioned in vitro charging method to charge the in vivo device through the charging head.

[0036] In a feasible implementation, the surface of the charging head is covered with a protective layer, and the material of the protective layer is an iron-based nanocrystalline material.

[0037] The embodiment of the present application provides an in vitro charging method and device for an active implantable medical device, which respectively obtains a first voltage value and a second voltage value, and compares the first voltage value and the second voltage value with the frequency adjustment scale value and the pulse width adjustment scale to obtain a frequency compression ratio and a pulse width compression ratio, and then obtains a frequency compression sequence and a pulse width compression sequence through the frequency compression ratio and the pulse width compression ratio; judges and selects a frequency compression ratio range and a pulse width compression ratio range based on the product of a real-time third voltage value and a second current value of an in vivo device; finally, selects a target frequency and a target pulse width within a target frequency range and a target pulse width range based on the real-time frequency compression ratio and pulse width compression ratio of the frequency point, thereby determining a charging intensity that matches the intensities of the in vivo device and the in vitro device, solving the problem of unbalanced power transmission during wireless charging, and the charging method has fast convergence speed, strong anti-interference ability, and strong stability. BRIEF DESCRIPTION OF THE DRAWINGS

[0038] Figure 1 This is a topological diagram of an in vitro device and an in vivo device of an active implantable medical device provided in one embodiment of the present application;

[0039] Figure 2 This is a schematic structural diagram of a charging head in an in vitro device provided in one embodiment of the present application;

[0040] Description of reference numerals:

[0041] 100-external device; 200-in-vivo device; 300-charging head;

[0042] 110-power input module; 120-power management module; 130-inverter conversion module; 140-compensation circuit; 150-transmitting coil; 160-first current detection module; 170-first temperature detection module; 180-first voltage detection module; 190-first wireless communication module; 1100-control unit; 1110-display interface; 210-receiving coil; 220-charging parameter detection module; 230-second wireless communication module; 310-protective layer; 320-magnetic core; 330-temperature sensor. DETAILED DESCRIPTION

[0043] In order to enable those skilled in the art to better understand the technical solutions in this application, the technical solutions in the embodiments of this application will be clearly and completely described below in conjunction with the drawings in the embodiments of this application. Obviously, the described embodiments are only part of the embodiments of this application, not all of the embodiments. Based on the embodiments in this application, all other embodiments obtained by ordinary technicians in this field without making creative efforts should fall within the scope of protection of this application.

[0044] In the description of the embodiments of the present application, the terms "first" and "second" are used for descriptive purposes only and should not be understood as indicating or implying relative importance or implicitly indicating the number of the indicated technical features. Therefore, a feature defined as "first" or "second" may explicitly or implicitly include at least one of the features. In the description of the present application, the meaning of "plurality" is at least two, for example, two, three, etc., unless otherwise clearly and specifically defined.

[0045] In this application, unless otherwise specified or limited, the terms "mounted," "connected," "connect," "fixed," etc. should be understood in a broad sense. For example, they can refer to fixed connection, detachable connection, or integration; mechanical connection; direct connection or indirect connection through an intermediate medium; internal communication between two elements or interaction between two elements, unless otherwise specified. Those skilled in the art will understand the specific meanings of the above terms in this application based on specific circumstances.

[0046] In this application, unless otherwise expressly specified or limited, when a first feature is "above" or "below" a second feature, it can mean that the first and second features are in direct contact, or the first and second features are in indirect contact through an intermediate medium. Furthermore, when a first feature is "above," "above," or "above" a second feature, it can mean that the first feature is directly above or diagonally above the second feature, or simply means that the first feature is at a higher level than the second feature. When a first feature is "below," "below," or "below" a second feature, it can mean that the first feature is directly below or diagonally below the second feature, or simply means that the first feature is at a lower level than the second feature.

[0047] Active implantable medical devices are medical instruments implanted in the human body for a long time, including pacemakers, various types of nerve stimulators, muscle stimulators, etc. Active implantable medical devices deliver pulse stimulation signals to the target treatment area of ​​the human body through implanted electrodes to achieve the purpose of treatment.

[0048] Active implantable medical devices typically include an internal device 200 and an external device 100. The internal device 200 houses a battery and a receiving coil 210, while the external device 100 houses a charging head 300. To charge the battery in the internal device 200, the charging head 300 must be aligned with the receiving coil 210 for wireless charging.

[0049] However, because the in-vivo device 200 is located inside the human body, the position of the receiving coil 210 cannot be accurately observed. When charging the battery of the in-vivo device 200, the charging head 300 may not be accurately aligned with the receiving coil 210, resulting in unbalanced power transmission during wireless charging. In other words, the charging intensity in the in-vivo device 200 does not match the charging intensity in the external device 100.

[0050] The embodiment of the present application provides an in vitro charging method and device for an active implantable medical device, which respectively obtains a first voltage value and a second voltage value, and compares the first voltage value and the second voltage value with the frequency adjustment scale value and the pulse width adjustment scale to obtain a frequency compression ratio and a pulse width compression ratio, and then obtains a frequency compression sequence and a pulse width compression sequence through the frequency compression ratio and the pulse width compression ratio; judges and selects a frequency compression ratio range and a pulse width compression ratio range based on the product of a real-time third voltage value and a second current value of an in vivo device 200; finally, selects a target frequency and a target pulse width within a target frequency range and a target pulse width range based on the real-time frequency compression ratio and pulse width compression ratio of the frequency point, thereby determining a charging intensity that matches the intensity of the in vivo device 200 with that of the in vitro device 100, solving the problem of unbalanced power transmission during wireless charging, and the charging method has fast convergence speed, strong anti-interference ability, and strong stability.

[0051] Figure 1 1 is a topological diagram of an in vitro device 100 and an in vivo device 200 of an active implantable medical device provided in one embodiment of the present application.

[0052] refer to Figure 1 As shown, an active implantable medical device includes an in-vivo device 200 and an out-vivo device 100. The out-vivo device 100 includes a power input module 110, a power management module 120, an inverter module 130, a compensation circuit 140, a transmitting coil 150, a first current detection module 160, a first temperature detection module 170, a first voltage detection module 180, a first wireless communication module 190, a control unit 1100, and a display interface 1110.

[0053] The input end of power input module 110 is electrically connected to a power source, and the output end of power input module 110 is electrically connected to power management module 120. Power input module 110 is used to supply energy to extracorporeal device 100. The output end of power management module 120 is electrically connected to the input end of inverter module 130, and the output end of inverter module 130 is electrically connected to compensation circuit 140. Compensation circuit 140 is electrically connected to transmitting coil 150.

[0054] The power management module 120 controls the input and output of power. The inverter conversion module 130 controls the voltage source inverter circuit through two half-bridge drivers to generate high-frequency AC current for wireless charging. The compensation circuit 140 compensates for the power of the external charging device's transmitting circuit.

[0055] In addition, the input end of the first current detection module 160 is electrically connected to the output end of the inverter conversion module 130, and the output end of the first current detection module 160 is electrically connected to the control unit 1100. The first current detection module 160 is used to detect the first current value output by the inverter conversion module 130 and transmit the obtained first current value to the control unit 1100. The input end of the first temperature detection module 170 is connected to the transmitting coil 150, and the output end of the first temperature detection module 170 is electrically connected to the control unit 1100. The first temperature detection module 170 is used to detect the temperature of the transmitting coil 150, that is, the temperature of the coil of the charging head 300 of the external device 100. The first temperature detection module 170 transmits the obtained first temperature value to the control unit 1100. The input end of the first voltage detection module 180 is connected to the transmitting coil 150. The first voltage detection module 180 is used to detect the voltage value of the transmitting coil 150, that is, the first voltage value. The first voltage value is the voltage value of the transmitting coil 150 in the external charging device. The first voltage detection module 180 obtains the first voltage value and transmits it back to the control unit 1100 .

[0056] In addition, the in-vivo device 200 includes a receiving coil 210, a second wireless communication module 230, and a charging parameter detection module 220. The receiving coil 210 cooperates with the transmitting coil to charge the battery in the in-vivo device 200. The charging parameter detection module 220 is used to detect the third voltage value, the second current value, and the second temperature value at the receiving coil 210. The first wireless communication module 190 in the in-vivo device 100 is electrically connected to the control unit 1100 and can be used to receive data. The second wireless communication module 230 of the in-vivo device 200 communicates with the first wireless communication module 190 and transmits the third voltage value, the second current value, and the second temperature value to the control unit 1100 via the first wireless communication module 190.

[0057] The present invention provides a method for charging an active implantable medical device in vitro, the method comprising the following steps:

[0058] Obtain a first voltage value and a second voltage value, where the first voltage value is the voltage value of the transmitting coil 150 corresponding to each frequency point within the frequency adjustment range of the charging head 300 in the external charging device; and the second voltage value is the voltage value of the transmitting coil 150 corresponding to each pulse width within the frequency adjustment range of the charging head 300 in the external charging device. In some examples, the external device 100 may use the first voltage detection module 180 to detect the first and second voltage values.

[0059] Then, the obtained first voltage value is compared with the frequency adjustment scale value corresponding to each frequency point to obtain the frequency compression ratio. It should be noted that the frequency adjustment scale value refers to the voltage value of the transmitting coil 150 corresponding to each frequency point of the charging head 300 under no-load.

[0060] The second voltage value is ratioed with the pulse width adjustment scale value corresponding to its pulse width to obtain the pulse width compression ratio. It should be noted that the pulse width adjustment scale value refers to the voltage value of the transmitting coil 150 corresponding to each pulse width of the charging head 300 at no load and center frequency.

[0061] The control unit 1100 can obtain a frequency compression ratio sequence and a pulse width compression ratio sequence within the frequency adjustment range by recording the frequency compression ratio and the pulse width compression ratio at each frequency point.

[0062] The obtained frequency compression ratio sequence and pulse width compression ratio sequence have a maximum point, which means that the corresponding frequency or pulse width can be found through this maximum point. This is because the compression ratio is the largest at a certain frequency or pulse width and decreases in sequence towards both sides.

[0063] At the same time, a third voltage value and a second current value are obtained in real time; the third voltage value is the voltage value of the receiving coil 210 of the in-vivo device 200, and the second current value is the current value of the receiving coil 210 of the in-vivo device 200. In some feasible embodiments, the in-vivo device 200 is provided with a charging parameter detection module 220 for obtaining the third voltage value and the second current value at the receiving coil 210 in real time. After obtaining the third voltage value and the third current value, the charging parameter detection module 220 transmits them to the second wireless communication module 230. The second wireless communication module 230 then wirelessly transmits the third voltage value and the second current value to the first wireless communication module 190, which then transmits the data to the control unit 1100.

[0064] After obtaining the third voltage value and the second current value, control unit 1100 determines a selected frequency compression ratio range and a selected pulse width compression ratio range based on the product of the third voltage value and the second current value, and selects a frequency compression ratio range and a pulse width compression ratio range from the frequency compression ratio sequence and the pulse width compression ratio sequence, respectively. For example, the upper limit of the selected compression ratio is the maximum compression ratio in real time, and the lower limit of the selected frequency compression ratio range and the pulse width compression ratio range is determined by the product of the second current value and the third voltage value.

[0065] It should be noted that the product of the second current value and the third voltage value is divided into five levels. The control unit 1100 determines the level of the product of the second current value and the third voltage value in real time, thereby determining the distance from the lower limit of the frequency compression ratio and the pulse width compression ratio to the upper limit of the frequency compression ratio and the pulse width compression ratio to be selected, thereby determining the frequency compression ratio range and the pulse width compression ratio range. Exemplarily, the five levels related to the product of the second current value and the third voltage value are as follows: the first level has an interval range of: ≥3600; the second level has an interval range of: [2520, 2600); the third level has an interval range of: [1950, 2520); the fourth level has an interval range of: [1000, 1950); and the fifth level has an interval range of: <1000.

[0066] The corresponding target frequency range and target pulse width range are obtained according to the frequency compression ratio range and the pulse width compression ratio range.

[0067] During the charging process using the transmitting coil 150 and the receiving coil 210, the control unit 1100 selects the target frequency and target pulse width within the target frequency range and target pulse width range based on the numerical values ​​of the frequency compression ratio and the pulse width compression ratio calculated in real time at the frequency points within the frequency adjustment range, thereby determining the charging intensity of the external device 100 to the internal device 200.

[0068] It can be understood that the embodiment of the present application provides an in vitro charging method for an active implantable medical device, which obtains a first voltage value and a second voltage value respectively, and compares the first voltage value and the second voltage value with the frequency adjustment scale value and the pulse width adjustment scale respectively to obtain a frequency compression ratio and a pulse width compression ratio, and then obtains a frequency compression sequence and a pulse width compression sequence through the frequency compression ratio and the pulse width compression ratio; judges and selects the frequency compression ratio range and the pulse width compression ratio range according to the product of the real-time third voltage value and the second current value of the in-vivo device 200, and finally selects the target frequency and the target pulse width within the target frequency range and the target pulse width range according to the real-time frequency compression ratio and the pulse width compression ratio of the frequency point, thereby determining the charging intensity that matches the intensity of the in-vivo device 200 with that of the in-vivo device 100, thereby solving the problem of mismatch in charging intensity between the in-vivo device 200 and the in-vivo device 100 in the prior art.

[0069] In some feasible embodiments, in order to select a target frequency and a target pulse width within a target frequency range and a target pulse width range based on the real-time frequency compression ratio and pulse width compression ratio at a frequency point, the frequency compression ratio range and the pulse width compression ratio range are typically divided into at least five intervals, and the target frequency range and the target pulse width range are divided into at least five intervals. Then, based on the first interval of the frequency compression ratio range and the second interval of the pulse width compression ratio range in which the real-time frequency compression ratio and pulse width compression ratio of the frequency point are located, a corresponding third interval in the target frequency range and a corresponding fourth interval in the target pulse width range are determined, respectively.

[0070] The corresponding selection is repeated multiple times. When the range of the first interval and the second interval is smaller than the preset value, the target frequency and the target pulse width are selected in the third interval and the fourth interval.

[0071] In other words, in order to select the target frequency and target pulse width within the target frequency range and target pulse width range based on the real-time frequency compression ratio and pulse width compression ratio of the frequency point, the frequency compression ratio range and pulse width compression ratio range are usually divided into at least 5 intervals, and the target frequency range and target pulse width range are divided into at least 5 intervals. Then, it is determined in which interval the frequency compression ratio and pulse width compression ratio calculated in real time are respectively located. After determining the interval position, the interval corresponding to the interval position is selected within the target frequency range and target pulse width range. Reduce the step value, gradually reduce the range of the interval, and perform iterative selection until the step value is reduced to the preset value, thereby selecting the target frequency and target pulse width. Exemplarily, when the step value is less than the preset value of 3Hz, the target frequency and target pulse width are selected.

[0072] In some feasible embodiments, in order to be able to timely adjust the charging intensity of the external device 100 to the internal device 200, it is necessary to timely detect the first current value. It should be noted that the first current value is the current value of the transmitting coil 150 of the charging head 300. Exemplarily, the first current detection module 160 in the external device 100 obtains the first current value at intervals of a first time period. Exemplarily, the interval of the first time period can be set to 8s, or it can be set by technicians according to actual needs, which will not be repeated here. When the change in the first current value obtained twice in a row exceeds 20%, it indicates that the target frequency and target pulse width need to be re-determined.

[0073] In addition, when the change in the first current values ​​obtained two adjacent times exceeds 20%, the target frequency and target pulse width need to be re-determined, and the time interval for adjusting the charging intensity can be dynamically adjusted according to the changing trend of the product of the third voltage value and the second current value.

[0074] For example, when the product of the third voltage value and the second current value increases, the time interval for adjusting the target frequency and target pulse width increases; when the product of the third voltage value and the second current value decreases, the time interval for adjusting the target frequency and target pulse width decreases. It is understood that when the product of the third voltage value and the second current value is large, it indicates that the charging intensity of the in-vivo device 200 is high and the charging state is good. Therefore, the time interval for adjusting the charging intensity can be increased. Conversely, when the product of the third voltage value and the second current value is small, it indicates that the charging state of the in-vivo device 200 is poor. Therefore, the time interval for adjusting the charging intensity should be decreased. Thus, the charging frequency and pulse width are adjusted in a timely manner to adjust the charging intensity, so that the in-vivo device 200 can complete the charging process more quickly.

[0075] In some feasible embodiments, the in vitro charging method further includes:

[0076] A first temperature value and a second temperature value are obtained, where the first temperature value is the temperature of the transmitting coil 150 of the charging head 300; the second temperature value is the temperature of the receiving coil 210 of the internal device 200. For example, the first temperature detection module 170 in the external device 100 is used to detect the temperature of the transmitting coil 150; and the charging parameter detection module 220 in the internal device 200 is used to detect the temperature of the receiving coil 210. When the first and second temperature values ​​are outside the normal range, it indicates that the charging temperature of the external device 100 or the internal device 200 is abnormal, and continued charging may cause problems. Specifically, when the first temperature value exceeds the upper threshold of the first temperature range, or the second temperature value exceeds the upper threshold of the second temperature range, charging is stopped. The upper thresholds of the first and second temperature ranges can be set by technicians based on actual needs. For example, in the embodiment of the present application, the upper threshold of the first temperature range can be selected from 43°C to 47°C, and the upper threshold of the second temperature range can be selected from 38°C to 39°C.

[0077] Conversely, when the first temperature value is lower than the lower threshold of the first temperature range, and the second temperature value is lower than the lower threshold of the second temperature range, it indicates that the temperature of the external device 100 and the internal device 200 has returned to normal, and charging can be resumed at this time. The lower threshold of the first temperature range and the lower threshold of the second temperature range can be set by technicians according to actual needs. For example, in the embodiment of the present application, the lower threshold of the first temperature range can be selected in the range of 37°C-39°C, and the upper threshold of the second temperature range can be selected in the range of 37°C-38°C.

[0078] In addition, in some feasible embodiments, the in vitro charging method further includes: obtaining a first current value. As described above, the first current value is the current value of the transmitting coil 150 of the charging head 300.

[0079] When the first current value shows an increasing trend, it indicates that the charging intensity of the external device 100 and the internal device 200 is increasing. At this time, the temperature of the internal device 200 and the internal device 200 changes rapidly. In order to ensure that the abnormal charging temperature status of the two devices can be detected in time, the control unit 1100 controls to lower the upper limit threshold of the first temperature range and at the same time lower the lower limit threshold of the first temperature range.

[0080] When the first current value shows a decreasing trend, it indicates that the charging intensity of the external device 100 and the internal device 200 is decreasing. At this time, the temperature of the internal device 200 and the external device 100 changes slowly, and the internal device 200 and the external device 100 are less likely to have an abnormal charging temperature state. Therefore, the upper limit threshold of the first temperature range can be increased, and the lower limit threshold of the first temperature range can be increased.

[0081] It can be understood that when the second current value has an increasing trend, the upper threshold of the second temperature range is lowered, and the lower threshold of the second temperature range is lowered;

[0082] When the variation trend of the second current value is decreasing, the upper threshold of the second temperature range is adjusted upward, and the lower threshold of the second temperature range is adjusted upward.

[0083] Figure 2 Schematic diagram of the structure of the charging head 300 in the extracorporeal device 100 provided in one embodiment of the present application.

[0084] refer to Figure 2 As shown, on the other hand, an embodiment of the present application also provides an in vitro charging device for an active implantable medical device, wherein the in vivo charging device includes a charging head 300, and the in vivo device 200 is charged through the charging head 300 using the above-mentioned in vitro charging method.

[0085] In some feasible embodiments, the charging head 300 includes a protective layer 310, a magnetic core 320, a transmitting coil 150, and a temperature sensor 330. The transmitting coil 150 is diffracted on the magnetic core 320 and is used to cooperate with the receiving coil 210 in the in-vivo device 200 to charge the in-vivo device 200. The temperature sensor 330 is provided next to the transmitting coil 150 and is used to detect the temperature of the transmitting coil 150. Figure 2As shown, in the embodiment of the present application, the magnetic core 320 can be a heterogeneous magnetic core 320, which can improve the quality factor of the transmitting coil 150, constrain magnetic field leakage, reduce leakage in the non-charging area, reduce electromagnetic impact on the environment, and increase the magnetic flux density in the intended charging area. The designed heterogeneous magnetic core 320 has the advantages of low mass, easy processing and molding, low cost, and stable performance. In addition, the outer layer of the magnetic core 320 is coated with a protective layer 310 made of iron-based nanocrystalline material. The protective layer 310 and the magnetic core 320 form a double magnetic shield, further reducing the impact of wireless charging on the electromagnetic environment in the non-wireless charging area, and meeting the electromagnetic environment requirements of clinical applications.

[0086] It is easy to understand that those skilled in the art can combine, split, reorganize, etc. the embodiments of the present application based on the several embodiments provided in the present application to obtain other embodiments, and these embodiments do not exceed the scope of protection of the present application.

[0087] The above specific implementation methods further explain in detail the purpose, technical solutions and beneficial effects of the embodiments of the present application. It should be understood that the above are only specific implementation methods of the embodiments of the present application and are not intended to limit the scope of protection of the embodiments of the present application. Any modifications, equivalent replacements, improvements, etc. made on the basis of the technical solutions of the embodiments of the present application should be included in the scope of protection of the embodiments of the present application.

Claims

1. A method for charging an active implantable medical device in vitro, characterized in that: The method comprises the following steps: Obtain a first voltage value and a second voltage value, where the first voltage value is the voltage value of the transmitting coil corresponding to each frequency point within the frequency adjustment range when the charger is operating, and the second voltage value is the voltage value of the transmitting coil corresponding to each pulse width within the frequency adjustment range when the charger is operating; Ratioing the first voltage value to the frequency adjustment scale value corresponding to the frequency point to obtain a frequency compression ratio, wherein the frequency adjustment scale value refers to the transmitting coil voltage value corresponding to each frequency point of the charging head under no-load conditions; Ratioing the second voltage value to the pulse width adjustment scale value corresponding to its pulse width to obtain a pulse width compression ratio, wherein the pulse width adjustment scale value refers to the transmitting coil voltage value corresponding to each pulse width of the charging head at no load and center frequency; According to the frequency compression ratio at each frequency point and the pulse width compression ratio at each pulse width, a frequency compression ratio sequence and a pulse width compression ratio sequence within the frequency adjustment range are obtained respectively; Acquiring a third voltage value and a second current value in real time; wherein the third voltage value is a voltage value of a receiving coil of an in-vivo device, and the second current value is a current value of a receiving coil of the in-vivo device; determining a frequency compression ratio selection range and a pulse width compression ratio selection range according to a product of the third voltage value and the second current value, and selecting the frequency compression ratio range and the pulse width compression ratio range from the frequency compression ratio sequence and the pulse width compression ratio sequence, respectively; Obtaining a corresponding target frequency range and a target pulse width range respectively according to the frequency compression ratio range and the pulse width compression ratio range; A target frequency and a target pulse width are selected within the target frequency range and the target pulse width range according to the frequency compression ratio and the pulse width compression ratio at the frequency point in real time to determine the charging intensity.

2. The in vitro charging method for an active implantable medical device according to claim 1, characterized in that: The selecting the target frequency and the target pulse width within the target frequency range and the target pulse width range according to the frequency compression ratio and the pulse width compression ratio at the frequency point in real time comprises: The frequency compression ratio range and the pulse width compression ratio range are divided into at least 5 intervals, and the target frequency range and the target pulse width range are divided into at least 5 intervals, Determine a third interval corresponding to the target frequency range and a fourth interval corresponding to the target pulse width range according to the first interval of the frequency compression ratio range and the second interval of the pulse width compression ratio range of the frequency compression ratio and the pulse width compression ratio at the frequency point in real time; When the ranges of the first interval and the second interval are smaller than a preset value, a target frequency and a target pulse width are selected in the third interval and the fourth interval.

3. The in vitro charging method for an active implantable medical device according to claim 1, characterized in that: The in vitro charging method further comprises: Acquire a first current value at intervals of a first time period, where the first current value is a coil current value of the charging head; When the changes between two adjacent first current values ​​obtained exceed 20%, the target frequency and the target pulse width are re-determined to change the charging intensity.

4. The in vitro charging method for an active implantable medical device according to claim 3, characterized in that: When the product of the third voltage value and the second current value shows an increasing trend, increasing the time interval for adjusting the target frequency and the target pulse width; When the change trend of the product value of the third voltage value and the second current value is decreasing, the time interval for adjusting the target frequency and the target pulse width is reduced.

5. The in vitro charging method for an active implantable medical device according to claim 4, characterized in that: The in vitro charging method further comprises: Acquire a first temperature value and a second temperature value, where the first temperature is the temperature of the transmitting coil of the charging head; and the second temperature is the temperature of the receiving coil of the in-vivo device; When the first temperature value exceeds an upper threshold value of a first temperature range, or the second temperature value exceeds an upper threshold value of a second temperature range, charging is stopped.

6. The in vitro charging method for an active implantable medical device according to claim 5, characterized in that: The in vitro charging method further comprises: When the first temperature value is lower than a lower threshold value of a first temperature range, and the second temperature value is lower than a lower threshold value of a second temperature range, charging is resumed.

7. The in vitro charging method for an active implantable medical device according to claim 5, characterized in that: The in vitro charging method further comprises: When the first current value has an increasing trend, lowering the upper threshold of the first temperature range and lowering the lower threshold of the first temperature range; When the change trend of the first current value is decreasing, the upper threshold of the first temperature range is increased, and the lower threshold of the first temperature range is increased.

8. The in vitro charging method for an active implantable medical device according to claim 5, characterized in that: The in vitro charging method further comprises: When the second current value has an increasing trend, lowering the upper threshold of the second temperature range and lowering the lower threshold of the second temperature range; When the change trend of the second current value is decreasing, the upper threshold of the second temperature range is increased, and the lower threshold of the second temperature range is increased.

9. An in vitro charging device for an active implantable medical device, characterized in that: The device comprises a charging head, and uses the external charging method as described in any one of claims 1 to 8 to charge the internal device through the charging head.

10. The in vitro charging device for an active implantable medical device according to claim 9, characterized in that: The surface of the charging head is covered with a protective layer, and the material of the protective layer is iron-based nanocrystalline material.

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