CN117180619A - Implantable medical device and percutaneous energy delivery system - Google Patents

Abstract

The present application relates to an implantable medical device and a percutaneous energy delivery system. The implantable medical device includes a housing having oppositely disposed fat and muscle sides, a power assembly, and a thermally conductive element; the power supply assembly comprises a battery, an electric generating element and a control module, wherein the electric generating element is arranged in the shell and is in communication connection with the control module, and is used for charging the battery; the heat conducting element is arranged in the shell and connected with the fat side and the muscle side, and is used for conducting heat emitted by the electricity generating element from the fat side to the muscle side. Therefore, on one hand, the time that the temperature in the shell reaches the preset temperature can be prolonged, the situation that the temperature in the shell rapidly exceeds the preset temperature to stop charging is avoided, the charging efficiency is further improved, on the other hand, the highest temperature on the surface of the implantable medical device can be controlled in a safe range in the charging process, and the patient is prevented from being damaged by charging heat.

Description

Implantable medical device and percutaneous energy delivery system

Technical Field

The application relates to the technical field of medical instruments, in particular to an implantable medical device and a percutaneous energy transmission system.

Background

Implantable medical devices may be used for implantation in a patient to monitor the condition of the patient and provide corresponding therapy, wherein rechargeable implantable medical devices include rechargeable batteries therein, and the useful life thereof may be extended to weeks, months, or even years, as compared to non-rechargeable implantable medical devices. When the energy stored in the battery of the implantable medical device is depleted, the patient uses the extracorporeal charging device to charge the battery of the implantable medical device. Because the battery of the implantable medical device is implanted in the patient and the charging device is located outside the patient, this charging process may be referred to as transcutaneous energy transfer.

Because implantable medical devices are chronically implanted in a patient, contact with patient tissue and increased temperatures of the device may cause thermal injury to the patient. In the prior art, when the temperature control of the implantable medical device is performed in a discontinuous charging mode, namely when the equipment temperature exceeds the fat heat bearing limit corresponding to the fat heat metering threshold value in the standard ISO14708-3, the external charging device immediately stops charging and resumes charging after the temperature is reduced, so that the highest temperature of the surface of the implantable medical device can be controlled within a safe range in the wireless charging process, and the patient is prevented from being hurt by charging heat. However, when the conventional implantable medical device is charged in the above-mentioned intermittent charging manner, there are problems in that the actual chargeable time is short and the charging efficiency is very low, so that the charging time is too long, which makes it very inconvenient for a user to use the implantable medical device.

Disclosure of Invention

Accordingly, it is necessary to provide an implantable medical device and a percutaneous energy transmission system including the same, which can improve the charging efficiency, in order to solve the technical problems that the conventional implantable medical device has a short actual chargeable time and has low charging efficiency when being charged.

According to one aspect of the present application, there is provided an implantable medical device comprising:

a housing having oppositely disposed fat and muscle sides;

the power supply assembly comprises a battery, an electric generating element and a control module, wherein the battery is electrically connected with the electric generating element, the electric generating element is arranged in the shell, close to the fat side, and is in communication connection with the control module, and is used for charging the battery, and the control module is used for sending a control signal when the temperature in the shell reaches a preset temperature so as to control the electric generating element to stop charging the battery;

the heat conducting element is arranged in the shell and is connected with the fat side and the muscle side, and the heat conducting element is used for conducting at least heat generated when the electricity generating element is charged to the muscle side from the fat side so as to prolong the time when the temperature in the shell reaches the preset temperature.

In one embodiment, the power supply assembly further comprises a circuit board, the control module is arranged on the circuit board, and a waveform generation module is further arranged on the circuit board and used for generating a stimulation waveform under the control of the control module.

In one embodiment, a magnetic shielding sheet is provided between the circuit board and the electricity generating element.

In one embodiment, the heat conducting element is filled in a gap formed by the power supply assembly and the inner wall of the shell, and/or the heat conducting element is filled in a gap formed by the circuit board and the shell and wraps the circuit board and the electronic element thereon.

In one embodiment, the power supply assembly further comprises a temperature sensor, wherein the temperature sensor is arranged on the inner wall of the shell, which is positioned on one side of the fat side, and is in communication connection with the control module.

In one embodiment, a support is arranged in the shell, the support divides the inner cavity of the shell into a first cavity and a second cavity which are isolated from each other, the first cavity is close to the fat side, the second cavity is close to the muscle side, the electric generating element is arranged in the first cavity, the battery is arranged in the second cavity, and the heat conducting element penetrates through the support, so that part of the heat conducting element is positioned in the first cavity, and the other part of the heat conducting element is positioned in the second cavity.

In one embodiment, the central position of the electric generating element is provided with a central hole penetrating through two opposite sides of the electric generating element, and the heat conducting element penetrates through the central hole of the electric generating element.

In one embodiment, the battery is attached to one side of the heat conducting element to support the heat conducting element.

In one embodiment, the heat conducting element is made of an elastic soft material which is insulating and has heat conducting properties.

According to another aspect of the present application, there is provided a percutaneous energy transmission system including:

an implantable medical device as described above for implantation within a human body, the electrical generating element of the implantable medical device being an energy receiving coil;

the external charging device is used for being arranged outside a human body, an energy transmitting coil is arranged in the external charging device, the energy transmitting coil can generate an alternating magnetic field, and the energy receiving coil can generate current under the action of the alternating magnetic field.

In one embodiment, the control module of the implantable medical device is in wireless communication with the external charging device, and the control module is capable of sending a control signal to the external charging device when the temperature in the housing reaches the preset temperature, so as to control the external charging device to stop generating the alternating magnetic field.

The implantable medical device and the percutaneous energy transmission system comprising the implantable medical device enable heat emitted by the electric generating element when generating electric current to be rapidly conducted from a fat side with higher temperature to a muscle side with lower temperature by arranging the heat conducting element connected to the fat side and the muscle side of the shell in the shell. On the one hand, the temperature in the shell can be uniform, and the temperature of the fat side of the shell is prevented from exceeding the preset temperature rapidly due to slow heat dissipation, so that the control module is prevented from stopping the charging of the battery by the electric generating element in a short time, the time that the temperature in the shell reaches the preset temperature can be prolonged, the electric generating element can have longer effective charging time, and the aim of greatly improving the charging efficiency of the implanted medical device is fulfilled; on the other hand, the highest temperature of the surface of the implantable medical device can be controlled within a safe range in the charging process, and the patient is prevented from being damaged by charging heat.

Drawings

Fig. 1 is a schematic diagram of an application scenario of a percutaneous energy transmission system according to an embodiment of the application.

Fig. 2 is a schematic diagram illustrating an external structure of an implantable medical device according to an embodiment of the present application.

Fig. 3 is a schematic diagram illustrating an internal structure of an implantable medical device according to an embodiment of the present application.

Fig. 4 is a schematic diagram of control logic for charging an implantable medical device according to an embodiment of the present application.

Fig. 5 is a schematic diagram showing a predicted trend of temperature-time variation when an implantable medical device according to an embodiment of the present application is charged in a continuous charging manner.

Fig. 6 is a schematic diagram showing a predicted trend of temperature-time change when charging by intermittent charging before installing a heat conducting element in an implantable medical device according to an embodiment of the present application.

Fig. 7 is a schematic view illustrating heat transfer after the implantable medical device according to an embodiment of the present application is mounted with a heat conducting element.

Fig. 8 is a schematic diagram showing a predicted trend of temperature-time change when charging by intermittent charging after installing a heat conducting element in an implantable medical device according to an embodiment of the present application.

Fig. 9 is a graph showing temperature versus time for bench experiments performed before and after installing a heat conducting element in an implantable medical device according to an embodiment of the present application.

Reference numerals illustrate:

10. a percutaneous energy delivery system; 100. an implantable medical device; 101. a fat side; 102. a muscle side; 110. a housing; 111. a front shell; 112. a rear case; 113. a first cavity; 114. a second cavity; 120. a connector; 130. a power supply assembly; 131. a battery, 132, an electricity generating element; 132a, a central bore; 133. a circuit board; 134. a control module; 135. a temperature sensor; 140. a heat conductive element; 150. magnetic isolating sheets; 160. a bracket; 200. an in vitro charging device; 210. a host; 220. an energy transmitting coil; 300. a wire; 400. an electrode.

Detailed Description

In order that the above objects, features and advantages of the application will be readily understood, a more particular description of the application will be rendered by reference to the appended drawings. In the following description, numerous specific details are set forth in order to provide a thorough understanding of the present application. The present application may be embodied in many other forms than described herein and similarly modified by those skilled in the art without departing from the spirit of the application, whereby the application is not limited to the specific embodiments disclosed below.

In the description of the present application, it should be understood that, if any, these terms "center", "longitudinal", "transverse", "length", "width", "thickness", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", "clockwise", "counterclockwise", "axial", "radial", "circumferential", etc., are used herein with respect to the orientation or positional relationship shown in the drawings, and are merely for convenience of description and to simplify the description, and do not indicate or imply that the apparatus or article referred to must have a particular orientation, be constructed and operated in a particular orientation, and therefore should not be construed as limiting the application.

Furthermore, the terms "first," "second," and the like, if any, are used for descriptive purposes only and are not to be construed as indicating or implying a relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defining "a first" or "a second" may explicitly or implicitly include at least one such feature. In the description of the present application, the terms "plurality" and "a plurality" if any, mean at least two, such as two, three, etc., unless specifically defined otherwise.

In the present application, unless explicitly stated and limited otherwise, the terms "mounted," "connected," "secured," and the like are to be construed broadly. For example, the two parts can be fixedly connected, detachably connected or integrated; can be mechanically or electrically connected; either directly or indirectly, through an intervening medium, may be in communication between two members or in an interactive relationship therebetween, unless otherwise specifically indicated. The specific meaning of the above terms in the present application can be understood by those of ordinary skill in the art according to the specific circumstances.

In the present application, unless expressly stated or limited otherwise, the meaning of a first feature being "on" or "off" a second feature, and the like, is that the first and second features are either in direct contact or in indirect contact through an intervening medium. Moreover, a first feature being "above," "over" and "on" a second feature may be a first feature being directly above or obliquely above the second feature, or simply indicating that the first feature is level higher than the second feature. The first feature being "under", "below" and "beneath" the second feature may be the first feature being directly under or obliquely below the second feature, or simply indicating that the first feature is less level than the second feature.

It will be understood that if an element is referred to as being "fixed" or "disposed" on another element, it can be directly on the other element or intervening elements may also be present. If an element is referred to as being "connected" to another element, it can be directly connected to the other element or intervening elements may also be present. The terms "vertical," "horizontal," "upper," "lower," "left," "right," and the like as used herein, if any, are for descriptive purposes only and do not represent a unique embodiment.

The present application provides an implantable medical device and a percutaneous energy delivery system including the same, and the structure of the implantable medical device and the percutaneous energy delivery system of the present application will be described below by taking the implantable medical device as an example of a stimulator for nerve stimulation treatment of a patient. It will be appreciated that in other embodiments, the implantable medical device of the present application is not limited to a stimulator for neurostimulation therapy of a patient, but rather may be a medical device for treating a patient in other therapeutic manners, and is not limited herein.

Referring to fig. 1, fig. 1 shows a schematic view of a usage scenario of a percutaneous energy transmission system 10 according to an embodiment of the application, wherein the percutaneous energy transmission system 10 includes an implantable medical device 100 and an extracorporeal charging device 200, the implantable medical device 100 is configured to be implanted in a patient to monitor a condition of the patient and provide corresponding treatment, and the extracorporeal charging device 200 is located outside the patient and is spaced apart from the implantable medical device 100, so as to charge the implantable medical device 100 in a wireless connection manner when an electric quantity inside the implantable medical device 100 is exhausted, thereby achieving a purpose of enabling the implantable medical device 100 to be recycled.

In one embodiment, as shown in connection with fig. 1 and 2, the implantable medical device 100 includes a housing 110 and a connector 120, the connector 120 is connected to the outside of the housing 110 and connected to an electrode 400 through an extension lead 300, the electrode 400 is mounted on a patient's patient site, and during treatment, the implantable medical device 100 is capable of delivering a stimulation waveform, and the connector 120 transmits stimulation energy to the electrode 400 through the extension lead 300, so as to perform a neurostimulation treatment on the patient's patient site, such as alleviating symptoms of parkinson's disease or chronic pain, and the electrode 400 can enter electrically stimulated target tissue of the brain, spinal cord, dorsal root, etc. through any suitable site, thereby achieving an effective treatment effect.

Further, as shown in fig. 3, which is a schematic illustration of the internal structure of the implantable medical device 100 in one embodiment, the housing 110 has a fat side 101 and a muscle side 102 that are disposed opposite to each other, and after the implantable medical device 100 is implanted in a patient, the fat side 101 is disposed toward fat in the patient, and the muscle side 102 is disposed toward muscle in the patient. In an alternative embodiment, the housing 110 is a removable structure comprising a front shell 111 and a rear shell 112 removably connected to each other, the fat side 101 being located on the outer wall of the front shell 111 and the muscle side 102 being located on the outer wall of the rear shell 112.

As shown in fig. 3 and 4, the power supply assembly 130 is disposed in the housing 110, the power supply assembly 130 includes a battery 131, an electric generating element 132, a circuit board 133 and a control module 134, the battery 131 is electrically connected to the electric generating element 132, the electric generating element 132 is disposed in the housing 110 near the fat side 101 and is communicatively connected to the control module 134, for generating a current to charge the battery 131, the control module 134 is disposed on the circuit board 133 and is electrically connected to the circuit board 133, the control module 134 is wirelessly connected (e.g. by bluetooth) to the external charging device 200, for sending a control signal to the external charging device 200 when the temperature in the housing 110 reaches a preset temperature, so that the external charging device 200 controls the electric generating element 132 to stop generating a current, thereby stopping charging the battery 131, and after the temperature drops, controlling the external charging device 200 to restart the electric generating element to generate a current and restart charging. Referring to fig. 5 and 6, fig. 5 and 6 are schematic diagrams showing predicted trend of temperature-time change in the housing 110 in the continuous charging mode and the intermittent charging mode, respectively, it can be seen from fig. 5 that the temperature in the housing 110 is always increased with time in the continuous charging mode, so that the thermal tolerance limit (i.e. the preset temperature, for example, 41 ℃) corresponding to the thermal measurement threshold of fat in the standard ISO14708-3 is easily exceeded, and further, thermal injury is caused to the patient, and it can be seen from fig. 6 that the temperature change with time is always kept below the preset temperature in the intermittent charging mode, so that the thermal injury to the patient caused by the excessive temperature in the housing 110 can be avoided by the intermittent charging mode.

Optionally, in one embodiment, a waveform generation module (not shown) is further disposed on the circuit board 133, and is configured to perform algorithm control under the control of the control module 134, so as to generate a stimulus waveform.

With continued reference to fig. 4, the power supply assembly 130 further includes a temperature sensor 135 (not shown), where the temperature sensor 135 is disposed in the housing 110 near the electric generating element 132, that is, on an inner wall of the housing 110 on the fat side 101 side, and the temperature sensor 135 is communicatively connected to the control module 134, and is configured to detect a temperature in the housing 110 in real time, so as to send a temperature signal to the control module 134 when the heat generated by the electric current generated by the electric generating element 132 reaches a preset temperature, so that the control module 134 can stop the external charging device 200 from charging the battery 131 of the implantable medical device 100.

It should be understood that in other embodiments, the control module 134 may also have the functions of detecting the temperature in the housing 110, controlling the electric generating element 132 to stop generating the electric current and generating the stimulation waveform, without providing a separate temperature sensor 135 or a separate circuit board 133 in the power supply assembly 130, which is not limited herein.

Still further, to enable wireless charging, the implantable medical device 100 is made to be easily implanted in a patient, and to enable a reduction in the volume and weight of the implantable medical device 100 and the extracorporeal charging device 200. In a preferred embodiment, the electric generating element 132 is an energy receiving coil, and correspondingly, the external charging device 200 includes a main unit 210 and an energy transmitting coil 220 connected to the main unit 210, which are capable of achieving electromagnetic energy transmission through electromagnetic coupling, so that the electric generating element 132 can generate the current required for charging.

Specifically, the energy receiving coil and the energy transmitting coil 220 are both metal coils, which achieve energy transmission between the extracorporeal charging apparatus 200 and the implantable medical apparatus 100 by means of electromagnetic coupling. Preferably, the two are placed in a mode that the central axes are parallel, and an alternating magnetic field is generated by energizing the energy transmitting coil 220 by utilizing the electromagnetic induction principle, and the alternating magnetic field strength is changed, which is equivalent to the movement of the energy receiving coil for cutting the magnetic induction line in the magnetic field, so that alternating current can be generated, and then the alternating current is rectified and filtered by a circuit in the circuit board 133 to obtain a direct current signal, so that the battery 131 can be charged. When the energy transmitting coil 220 of the extracorporeal charging apparatus 200 does not generate an alternating magnetic field, the energy receiving coil (i.e. the electrical generating element 132) in the implantable medical device 100 is also accordingly unable to charge the battery 131.

With continued reference to fig. 3, in order to shield the electrical generating element 132 (i.e., the energy receiving coil) from the electrical circuit on the circuit board 133, and reduce crosstalk, and in order to focus the magnetic field generated by the energy transmitting coil 220, a magnetic shielding sheet 150 is disposed between the circuit board 133 and the electrical generating element 132. In some embodiments, the magnetic separator sheet 150 is made primarily of ferrite, amorphous, nanocrystalline, etc. materials.

In addition, in order to facilitate the installation of the electric generating element 132, the circuit board 133, the battery 131, the magnetism isolating sheet 150, and other elements, a bracket 160 is further provided in the housing 110, the bracket 160 divides the inner cavity of the housing 110 into a first cavity 113 and a second cavity 114 that are isolated from each other, the first cavity 113 is close to the fat side 101, the second cavity 114 is close to the muscle side 102, the electric generating element 132 is located in the first cavity 113, the battery 131 is located in the second cavity 114, and the magnetism isolating sheet 150 is provided on the inner wall of the first cavity 113 and between the electric generating element 132 and the circuit board 133 in the embodiment in the drawing. In other embodiments, the magnetic shielding sheet 150 may be disposed on the inner wall of the second cavity 114, so long as it is located between the electricity generating element 132 and the circuit board 133 and can function to shield the electricity generating element 132 and the circuit on the circuit board 133 from each other.

As described above, to avoid having the equipment temperature exceed the fat caloric burden limit corresponding to the fat caloric metering threshold in standard ISO14708-3, it is conventional practice to employ intermittent charging to ensure that the maximum temperature of the surface of the implantable medical device 100 is controlled within a safe range during wireless charging. However, the present inventors have found in the study that although the above-mentioned intermittent charging method of the conventional implantable medical device 100 can ensure the safety of charging, the heat generated from both sides of the housing 110 is not uniform, and the housing 110 is filled with a gas insulation layer, so that it is difficult to dissipate heat from the side of the housing 110 facing the fat (i.e. the fat side 101), and the temperature thereof can reach the limit temperature of the fat heat tolerance too quickly, resulting in too short effective charging time and reduced charging efficiency. This is because the implantable medical device 100 is typically implanted 10mm to 20mm below the skin surface of the human body, in the fat and muscle or muscle layer (as shown in fig. 7). Because there is perfusion of blood flow in the muscle, the heat conduction speed of the muscle is faster than that of fat, and because the electricity generating element 132 is arranged in the shell 110 near the fat side 101, the side of the shell 110 facing the muscle (i.e. the muscle side 102) generates heat slowly and dissipates heat quickly, while the side of the shell 110 facing the fat (i.e. the fat side 101) generates heat quickly and dissipates heat slowly, and the sealed shell 110 is internally filled with gas heat insulation layers which obstruct heat transfer, and the gas heat insulation layers obstruct heat transfer generated by the electricity generating element 132. This will result in the temperature of the fat side 101 of the housing 110 easily reaching the fat heat tolerance limit (i.e. the preset temperature) corresponding to the fat heat metering threshold in the standard ISO14708-3 in a very short time, and when the above limit is reached, the control module 134 will control the external charging device 200 to stop generating the alternating magnetic field, so that the electric generating element 132 will stop generating the electric current only after a short time of charging, and the charging efficiency of the implantable medical device 100 will be too low.

In order to solve this problem, the present inventors have conducted intensive studies to think that the time for which the temperature of the inside of the case 110, particularly the fat side 101, reaches the preset temperature can be prolonged by changing the heat transfer path, thereby delaying the control module 134 from controlling the external charging device 200 to stop generating the magnetic field, increasing the effective charging time for the battery 131.

Therefore, as a further improvement of the above embodiment, referring to fig. 3, the heat conducting element 140 is disposed in the housing 110, and the heat conducting element 140 connects the fat side 101 and the muscle side 102 of the housing 110, and may be made of an elastic soft material with high heat conductivity and insulation, and the higher the insulation coefficient and the heat conductivity coefficient, the better, for example, may be a medium with good heat conductivity and insulation such as heat conducting silica gel, heat conducting silicone grease or heat conducting pad.

Referring to fig. 8, fig. 8 shows a predicted trend of temperature-time change in the housing 110 after the heat conducting element 140 is disposed in the housing 110, and compared with the predicted trend of temperature-time in the housing 110 when the heat conducting element 140 is not disposed in the housing 110 shown in fig. 6, it can be seen that the slope of the line shown in fig. 8 is smaller when the temperature is raised, which indicates that the temperature of the housing 110 is raised slowly within the same time after the heat conducting element 140 is added, and the effective charging time is prolonged.

It should be noted that the implantable medical device 100 is required to be as small and light as possible to avoid adding additional burden to the patient as an implant implanted in the human body, so that in order to achieve the object, the present inventors also noted that when the electric generating element 132 is a coil, the center position of the electric generating element 132 has a center hole 132a penetrating through opposite sides thereof, and the center position of the bracket 160 is also provided with a through hole penetrating through opposite sides thereof, the center hole 132a and the through hole are mutually communicated and coaxially arranged, just because of the existence of the center hole 132a of the electric generating element 132 and the through hole of the bracket 160, the position where the fat side 101 of the housing 110 heats up most is the position corresponding to the center hole 132a of the electric generating element 132 and the through hole of the bracket 160. With the above opening positions of the central hole 132a and the through hole, in a preferred embodiment, as shown in fig. 3, the heat conducting element 140 sequentially penetrates through the through hole of the bracket 160 and the central hole 132a of the electricity generating element 132, and one end of the heat conducting element 140 is connected to the inner wall of the muscle side 102 side of the housing 110, and the other end is connected to the inner wall of the fat side 101 side of the housing 110, so that the heat conducting element 140 is just installed in the middle position in the housing 110, the existing space in the housing 110 is fully utilized, and the installation space for the heat conducting element 140 is not required to be additionally increased, thereby reducing the occupied volume of the implantable medical device 100, and the arrangement of the heat conducting element 140 can stabilize the overall structure of the housing 110. It should be noted that, when the bracket 160 is not disposed in the housing 110, the heat conducting element 140 directly penetrates the electricity generating element 132, which can also save installation space.

In addition, when the heat conducting element 140 is made of an elastic soft material, for example, a heat conducting silica gel, in order to better support the heat conducting element 140 and prevent the heat conducting element 140 from falling off the inner wall of the housing 110, in a more preferred embodiment, the battery 131 is attached to one side of the heat conducting element 140, and the battery 131 is attached to the lower side of the heat conducting element 140, so that the battery 131 can better support the heat conducting element 140, and the battery 131 can be used as a solid and also can be used as a good conductor of heat, thereby being more helpful for rapidly conducting heat from the fat side 101 to the muscle side 102. Further, since the heat conductive member 140 itself is soft and elastic, when other members are installed in the case 110, the other members can be installed using the most effective space by using the deformation of the heat conductive member 140, for example, forming various spaces around the heat conductive member 140 to match the outer shape of the other members.

It is understood that the heat conducting element 140 may not be attached to the battery 131, but obviously has a better effect when attached to the battery 131.

In a preferred embodiment, the heat conducting element 140 is filled in the gap between the power supply assembly 130 and the inner wall of the housing 110, and preferably fills the gap, so that the circuit board 133 can be encapsulated. Still further, the heat conductive element 140 may also be used to connect the fat side 101 and the muscle side 102 of the housing 110 while encapsulating the circuit board 133. In this way, while protecting the circuit board 133, the circuit on the circuit board 133 can be prevented from being affected by the surrounding static electricity, thereby improving the product safety through the dual scheme of circuit protection and heat dissipation efficiency improvement.

As can be seen from this, the present inventors have provided the heat conductive member 140 by utilizing the characteristic that the heat conductive properties of different tissues of the human body are different, so that the heat emitted from the electricity generating member 132 when generating electric current can be rapidly conducted from the fat side 101 to the muscle side 102. On the one hand, the heat dissipation can be accelerated to make the temperature in the housing 110 more uniform, and the time for the fat side 101 of the housing 110 to reach the preset temperature can be prolonged, so that the implantable medical device 100 can have a longer effective charging time, and the purpose of greatly improving the charging efficiency of the implantable medical device 100 is achieved.

On the other hand, the heat generated from the fat side 101 of the housing 110 is transferred from the heat conductive member 140 to the muscle side 102 of the housing 110, so that the heat is quickly transferred from the muscle side 102 of the housing 110 to other parts of the human tissue, thereby controlling the temperature of the human tissue and avoiding thermal damage.

In yet another aspect, when the heat conducting element 140 is made of a highly heat conducting, elastic, soft, heat conducting material, as compared to other metal heat conducting materials, not only can the elastic, soft, heat conducting material perform the functions of insulation and heat conduction, but also can reduce the overall weight of the implantable medical device 100, and because the material of the heat conducting element 140 has a high degree of plasticity, the heat conducting element 140 can be adhered to a larger area on the inner wall of the housing, and before the front shell 111 and the rear shell 112 of the housing 110 are joined together, the size of the heat conducting element 140 is larger than the distance from the fat side 101 to the muscle side 102 after the front shell 111 and the rear shell 112 are joined together, so that the inner wall of the housing 110 on the fat side 101 and the inner wall of the housing 110 on the muscle side 102 can be ensured to be in close contact with the heat conducting element 140. Further, since the material of the heat conducting element 140 has high plasticity, and there is no need to separately provide an installation space for the heat conducting element 140, so that the heat conducting element 140 can be inserted between each component in the housing 110 and freely adapt to the narrow structure inside the implantable medical device 100, and the positions of other components are not limited, so that the effects of guiding the heat dissipation direction, saving the design space and optimizing the space utilization efficiency are achieved, and particularly, the heat conducting device has a very good effect when applied to the implantable medical device 100 with very high volume requirements. Furthermore, in the process of installing the heat conducting element 140, the heat conducting element 140 can be subjected to repeated plasticity for a plurality of times according to the installation space reserved for the heat conducting element 140 until the installation requirement of the heat conducting element 140 can be met, the heat conducting element 140 does not need to be replaced, and the production cost of the implantable medical device 100 is effectively saved.

Finally, in order to verify that the implantable medical device 100 provided by the present application can actually have the effect of improving the charging efficiency after adding the heat conducting element 140 in the housing 110, the present inventors also specially performed a bench experiment on the temperature-time change in the housing 110 for the case where the heat conducting element 140 is present in the housing 110 and the case where the heat conducting element 140 is absent, the experimental result is shown in fig. 9, the abscissa in fig. 9 shows the charging time, the ordinate shows the temperature of the fat side 101 of the housing 110, and the experimental result shown in the drawing shows that the slope of the curve representing the temperature rise after adding the heat conducting element 140 is significantly smaller, the time required to reach the preset temperature is longer, and the predicted trend is consistent with that shown in fig. 8, which proves that the effective charging time can be significantly increased after disposing the heat conducting element 140 in the housing 110 of the implantable medical device 100, and the charging efficiency is improved.

The technical features of the above-described embodiments may be arbitrarily combined, and all possible combinations of the technical features in the above-described embodiments are not described for brevity of description, however, as long as there is no contradiction between the combinations of the technical features, they should be considered as the scope of the description.

The above examples illustrate only a few embodiments of the application, which are described in detail and are not to be construed as limiting the scope of the claims. It should be noted that it will be apparent to those skilled in the art that several variations and modifications can be made without departing from the spirit of the application, which are all within the scope of the application. Accordingly, the scope of protection of the present application is to be determined by the appended claims.

Claims (11)

1. An implantable medical device, comprising:

a housing having oppositely disposed fat and muscle sides;

the power supply assembly comprises a battery, an electric generating element and a control module, wherein the battery is electrically connected with the electric generating element, the electric generating element is arranged in the shell, close to the fat side, and is in communication connection with the control module, and is used for charging the battery, and the control module is used for sending a control signal when the temperature in the shell reaches a preset temperature so as to control the electric generating element to stop charging the battery;

the heat conducting element is arranged in the shell and is connected with the fat side and the muscle side, and the heat conducting element is used for conducting at least heat generated by the electric generating element during charging from the fat side to the muscle side so as to prolong the time when the temperature in the shell reaches the preset temperature.

2. The implantable medical device according to claim 1, wherein the power supply assembly further comprises a circuit board, the control module being disposed on the circuit board, a waveform generation module being further disposed on the circuit board, the waveform generation module being configured to generate a stimulation waveform under control of the control module.

3. The implantable medical device according to claim 2, wherein a magnetic barrier sheet is provided between the circuit board and the electrical generating element.

4. The implantable medical device according to claim 2, wherein the heat conducting element fills in a gap formed by the power supply assembly and an inner wall of the housing, and/or wherein the heat conducting element fills in a gap formed by the circuit board and the housing and encapsulates the circuit board and electronic components thereon.

5. The implantable medical device of claim 1, the power supply assembly further comprising a temperature sensor disposed on an inner wall of the housing on the fat side and in communication with the control module.

6. The implantable medical device according to claim 1, wherein a bracket is provided in the housing, the bracket dividing an inner cavity of the housing into a first cavity and a second cavity isolated from each other, the first cavity being adjacent to the fat side, the second cavity being adjacent to the muscle side, the electrical generating element being provided in the first cavity, the battery being provided in the second cavity, the heat conducting element being provided through the bracket such that a portion of the heat conducting element is located in the first cavity and another portion is located in the second cavity.

7. The implantable medical device according to claim 1, wherein the electrical generating element has a central hole extending through opposite sides thereof at a central position thereof, and the heat conducting element is disposed through the central hole of the electrical generating element.

8. The implantable medical device according to claim 1, wherein the battery is attached to one side of the thermally conductive element to support the thermally conductive element.

9. The implantable medical device according to claim 1, wherein the thermally conductive element is made of an elastic soft material that is insulating and has thermal conductivity.

10. A percutaneous energy delivery system, comprising:

the implantable medical device of any one of claims 1-9, for implantation within a human body, the electrical generating element of the implantable medical device being an energy receiving coil;

the external charging device is used for being arranged outside a human body, an energy transmitting coil is arranged in the external charging device, the energy transmitting coil can generate an alternating magnetic field, and the energy receiving coil can generate current under the action of the alternating magnetic field.

11. The percutaneous energy delivery system according to claim 10, wherein the control module of the implantable medical device is in wireless communication with the external charging device, the control module being capable of sending a control signal to the external charging device to control the external charging device to cease generating the alternating magnetic field when the temperature within the housing reaches the preset temperature.