Implantable electrical stimulation device
By introducing a relay coil into the implanted electrical stimulation device, the coupling ability between the transmitting coil and the receiving coil is enhanced, the problem of low transmission efficiency is solved, and more efficient energy and signal transmission is achieved.
Patent Information
- Application Number
- CN202421739445.7
- Authority / Receiving Office
- CN · China
- Patent Type
- Utility models(China)
- Current Assignee / Owner
- Filing Date
- 2024-07-22
- Publication Date
- 2025-07-01
- Estimated Expiration
- 2034-07-22
AI Technical Summary
In traditional implantable electrical stimulation devices, the coupling ability between the transmitting coil and the receiving coil is low, resulting in lower energy and signal transmission efficiency.
In the implanted electrical stimulation device, a relay coil is added so that it is located between the transmitting coil and the receiving coil to enhance coupling capability.
By adding the relay coil, the coupling capability between the transmitting coil and the receiving coil is significantly improved, thereby improving the transmission efficiency.
Smart Images
Figure CN223042009U_ABST
Abstract
Description
Technical Field
[0001] The utility model relates to the field of medical devices, and particularly to an implantable electrical stimulation device. Background Art
[0002] In the current field of medical technology, as a cutting-edge technology, implantable electrical stimulation devices are gradually becoming the standard method for treating various neurological diseases and dysfunctions. Implantable electrical stimulation devices usually rely on efficient and reliable wireless energy transmission and data communication technologies to ensure long-term stable working performance and patient safety.
[0003] Near Field Communication (NFC) technology, as a short-range wireless communication technology, has been exploratorily applied to such implantable medical devices due to its low power consumption and simple and fast data exchange characteristics to achieve functions such as remote control, status monitoring, and wireless charging of the devices. Traditional implantable electrical stimulation devices usually use direct coupling of two coils, and the transmission efficiency of energy and signals in this way is relatively low.
[0004] Therefore, a solution is needed to solve the problem of low transmission efficiency.
[0005] The information disclosed in the background part of the utility model is only intended to increase the understanding of the overall background of the utility model, and should not be regarded as an admission or any form of suggestion that this information constitutes the prior art already known to those of ordinary skill in the art. Summary of the Utility Model
[0006] The purpose of the utility model is to provide an implantable electrical stimulation device, in which a relay coil is added between the transmitting coil and the receiving coil in the implantable electrical stimulation device, so as to enhance the coupling ability between the two coils and thus improve the transmission efficiency.
[0007] The utility model provides an implantable electrical stimulation device, comprising: a transmitter, which is arranged outside the human body and has a transmitting coil; a receiver, which can be implanted into the human body and has a receiving coil; a relay coil, which is arranged on or inside the transmitter and is located between the transmitting coil and the receiving coil when the transmitting coil approaches the receiving coil, so that the signal of the transmitting coil can be sent to the receiving coil through the relay coil.
[0008] Preferably, the distance between the transmitting coil and the relay coil ranges from 0 to 1 cm.
[0009] Preferably, when the distance between the relay coil and the receiving coil is less than or equal to 1 cm, the signal of the transmitting coil can be sent to the receiving coil through the relay coil.
[0010] Preferably, when the distance from the transmitting coil to the receiving coil is less than or equal to 2 cm, the signal of the transmitting coil can be sent to the receiving coil through the relay coil.
[0011] Preferably, the shapes of the transmitting coil, the receiving coil and the relay coil are triangular.
[0012] Preferably, the shapes of the transmitting coil, the receiving coil and the relay coil are rectangular.
[0013] Preferably, the shapes of the transmitting coil, the receiving coil and the relay coil are circular.
[0014] Preferably, the shapes of the transmitting coil, the receiving coil and the relay coil are oval.
[0015] Preferably, the relay coil can be detachably installed inside the transmitter or on the surface of the transmitter.
[0016] Preferably, the relay coil can be pasted on the surface of the transmitter.
[0017] In the implantable electrical stimulation device of the present utility model, a relay coil is added between the transmitting coil and the receiving coil in the implantable electrical stimulation device, which can enhance the coupling ability between the two coils, thereby improving the transmission efficiency.
[0018] The device of the present utility model has other characteristics and advantages, which will be obvious from the accompanying drawings and subsequent embodiments incorporated herein, or will be described in detail in the accompanying drawings and subsequent embodiments incorporated herein. These drawings and embodiments are used together to explain the specific principles of the present utility model. Description of the Drawings
[0019] Figure 1A It is the first structural schematic diagram of the implantable electrical stimulation device according to the embodiment of the present utility model;
[0020] Figure 1B It is the structural schematic of the implantable electrical stimulation device according to the embodiment of the present utility model Figure Two ;
[0021] Figure 2 It is the schematic diagram of the transmitting coil and the receiving coil modeled in HFSS;
[0022] Figure 3 It is Figure 2 the simulation result diagram of;
[0023] Figure 4 It is the schematic diagram of adding a relay coil on the basis of Figure 2 ;
[0024] Figure 5 For Figure 4 simulation result diagram of;
[0025] Explanation of reference numerals in the drawings:
[0026] 100: Transmitting coil 200: Receiving coil
[0027] 300: Relay coil 500: Transmitter
[0028] 600: Receiver.
[0029] It should be understood that the drawings are not necessarily drawn to scale, but rather present simplified representations of various features to illustrate the basic principles of the present utility model. The specific design features disclosed in the present utility model (including, for example, specific dimensions, directions, positions, and shapes) will be determined in part by the specific application and use environment.
[0030] In these drawings, throughout the various figures of the drawings, the same reference numerals represent the same or equivalent parts of the present utility model. Detailed implementation manners
[0031] The following will refer in detail to the various implementation manners of the present utility model, examples of which are presented in the drawings and described as follows. Although the present utility model will be described in conjunction with exemplary implementation manners, it should be understood that this specification is not intended to limit the present utility model to these exemplary implementation manners. On the contrary, the present utility model is intended to cover not only these exemplary implementation manners, but also various alternative forms, modified forms, equivalent forms, and other implementation manners that may be included within the spirit of the present utility model and the scope defined by the appended claims.
[0032] When a component is referred to as being "above" or "over" another component, the component may be in contact with the other component, or the component may be spaced apart from the other component, or there may be an intermediate component between the component and the other component.
[0033] Figure 1A Schematic diagram I of the structure of the implantable electrical stimulation device according to an embodiment of the present utility model; Figure 1B Schematic diagram of the structure of the implantable electrical stimulation device according to an embodiment of the present utility model Figure Two ; Figure 2 Schematic diagram of the transmitting coil and the receiving coil modeled in HFSS; Figure 3 For Figure 2 simulation result diagram of; Figure 4 For adding a relay coil on the basis of Figure 2 schematic diagram; Figure 5 For Figure 4 simulation result diagram.
[0034] The following will describe the implantable electrical stimulation device according to the embodiments of the present utility model in conjunction with Figures 1A to 5 the accompanying drawings.
[0035] As Figure 1A shown in Figure 1B FIGs.
[0036] The transmitter 500 is disposed outside the human body and has a transmitting coil 100.
[0037] The receiver 600 can be implanted into the human body and has a receiving coil 200. Specifically, the receiver 600 can be implanted into the subcutaneous fat layer of the human body.
[0038] The relay coil 300 is disposed on the transmitter 500 (see Figure 1B for cooperation) or inside the transmitter 500 (see Figure 1A for cooperation), and is located between the transmitting coil 100 and the receiving coil 200 when the transmitting coil 100 is close to the receiving coil 200, so that the signal of the transmitting coil 100 can be transmitted to the receiving coil 200 through the relay coil 300. It should be noted that the signal only passes through the relay coil 300, and the relay coil 300 itself does not have the ability to transmit, but only plays a role in enhancing the coupling ability between the transmitting coil 100 and the receiving coil 200.
[0039] By adding the relay coil 300 between the transmitting coil 100 and the receiving coil 200 in the implantable electrical stimulation device of the present utility model, the coupling ability between the two coils can be enhanced, thereby improving the transmission efficiency.
[0040] In an exemplary embodiment, the distance from the transmitting coil 100 to the relay coil 300 ranges from 0 to 1 cm.
[0041] In an exemplary embodiment, when the distance from the relay coil 300 to the receiving coil 200 is less than or equal to 1 cm and greater than the skin thickness, the signal of the transmitting coil 100 can be transmitted to the receiving coil 200 through the relay coil 300. Since the receiving coil 200 is disposed in the human body and the relay coil 300 is disposed outside the human body, the distance from the relay coil 300 to the receiving coil 200 needs to be greater than the skin thickness.
[0042] In an exemplary embodiment, when the distance from the transmitting coil 100 to the receiving coil 200 is less than or equal to 2 cm, the signal of the transmitting coil 100 can be sent to the receiving coil 200 through the relay coil 300. For example, the distance from the transmitting coil 100 to the relay coil 300 is 0.5 cm, and the distance from the relay coil 300 to the receiving coil 200 is 1.5 cm. Or, the distance from the transmitting coil 100 to the relay coil 300 is 1.2 cm, and the distance from the relay coil 300 to the receiving coil 200 is 0.8 cm.
[0043] In one embodiment, the shapes of the transmitting coil 100, the receiving coil 200, and the relay coil 300 are triangular.
[0044] In another embodiment, the shapes of the transmitting coil 100, the receiving coil 200, and the relay coil 300 are rectangular.
[0045] In yet another embodiment, the shapes of the transmitting coil 100, the receiving coil 200, and the relay coil 300 are circular.
[0046] In yet another embodiment, the shapes of the transmitting coil 100, the receiving coil 200, and the relay coil 300 are oval. Here, the shapes of the transmitting coil 100, the receiving coil 200, and the relay coil 300 are not limited thereto, and they can be any form in the prior art as long as the above functions can be achieved.
[0047] In an exemplary embodiment, the relay coil 300 can be detachably installed inside or on the surface of the transmitter 500. For example, the relay coil 300 can be pasted on the surface of the transmitter 500.
[0048] When the relay coil 300 is damaged, the relay coil 300 can be detached and a new relay coil 300 can be replaced.
[0049] Simulation analysis
[0050] As Figure 2 shown, a pair of ordinary coils are modeled in HFSS. The size of this pair of coils is 30*22 mm, and the two coils are 10 mm apart. Running the simulation, the S parameters are as Figure 3 shown. Referring to Figure 3 , the S21 simulation result of this pair of coils is -10.16 dB.
[0051] A relay coil of the same size is added between this pair of coils. The model is as Figure 4 shown. Running the simulation, the S parameters are as Figure 5As shown, S21 is -4.5 dB, which is about 5.5 dB higher than that without the relay coil, indicating that the relay coil has improved the coupling ability. The simulation results of the scheme without the relay coil and the scheme with the relay coil are compared in Table 1 below.
[0052] Table 1
[0053] S11 / dB S21 / dB S22 / dB Without relay coil -21.0 -10.1 -21.0 With relay coil -15.8 -4.5 -15.8
[0054] As can be seen from Table 1, for the S11, S21, and S22 of the scheme with the relay coil, they are all better than those of the scheme without the relay coil.
[0055] Through the above simulations and analyses, the following conclusion can be drawn: Using the relay coil can effectively improve the coupling ability of the coil.
[0056] Test verification
[0057] At the transmitting end, a mobile phone is used to transmit a 13.56 MHz signal. At the receiving end, the output voltage of the rectifying circuit is measured to be 5.94 V with a load of 500 Ω. The power obtained at the receiving end is calculated to be approximately 70 mW.
[0058] A relay coil is added between the mobile phone and the receiving coil. The output voltage of the rectifying circuit is measured to be 6.495 V with a load of 500 Ω. The power obtained at the receiving end is calculated to be 84 mW.
[0059] Comparing the two sets of test data shows that at the same distance, the relay coil strengthens the coupling between the mobile phone and the receiving end and improves the transmission efficiency.
[0060] For those skilled in the art, the other components and functions of the implantable electrical stimulation device according to the embodiments of the present invention are known, and in order to reduce redundancy, they will not be elaborated here.
[0061] The operation of the implantable electrical stimulation device according to the embodiments of the present invention will be described below with reference to the accompanying drawings.
[0062] The receiver 600 of the implantable electrical stimulation device is implanted into the human body. For example, the receiver 600 is implanted in the back.
[0063] The relay coil 300 is installed inside or on the surface of the transmitter 500, and it is necessary to ensure that the relay coil 300 is close to the transmitting coil 100 of the transmitter 500.
[0064] The side of the transmitter 500 where the relay coil 300 is installed is brought close to or attached to the position on the back corresponding to the receiver 600.
[0065] Turn on the switch of the transmitter 500 so that the signal of the transmitter 500 is transmitted through the transmitting coil 100 and the relay coil 300 to the receiving coil 200 of the receiver 600 in the human body, so as to realize the transmission of signals and energy to the receiver 600 in the human body. By using the relay coil 300, the coupling ability between the transmitting coil 100 and the receiving coil 200 can be effectively improved, thereby improving the transmission efficiency.
[0066] If the relay coil 300 is damaged, the damaged relay coil 300 can be disassembled and a new relay coil 300 can be replaced.
[0067] For the sake of convenient explanation and precise definition of the appended claims, the terms "upper", "lower", "inner", "outer", "above", "below", "upper", "lower", "upward", "downward", "front", "rear", "back", "inner side", "outer side", "inward", "outward", "inside", "outside", "internal", "external", "forward", "backward" are used to describe the features of the exemplary specific embodiments with reference to the positions of these features shown in the accompanying drawings.
[0068] The foregoing description of the specific exemplary embodiments of the present invention has been presented for purposes of illustration and description. The foregoing description is not intended to be exhaustive nor to limit the present invention to the precise form disclosed, and obviously many changes and variations are possible in light of the above teaching. The exemplary embodiments were chosen and described in order to explain the particular principles of the present invention and its practical application so that others skilled in the art may realize and utilize the various exemplary embodiments of the present invention and their various alternative forms and modifications. The scope of the present invention is defined by the appended claims and their equivalents.
Claims
1. An implantable electrical stimulation device, characterized in that: include: A transmitter, which is arranged outside the human body and has a transmitting coil; A receiver, which can be implanted in a human body and has a receiving coil; The relay coil is arranged on or inside the transmitter and is located between the transmitter coil and the receiving coil when the transmitter coil is close to the receiving coil, so that the signal of the transmitter coil can be sent to the receiving coil through the relay coil.
2. The implantable electrical stimulation device according to claim 1, characterized in that: The distance between the transmitting coil and the relay coil ranges from 0 to 1 cm.
3. The implantable electrical stimulation device according to claim 1, characterized in that: When the distance between the relay coil and the receiving coil is less than or equal to 1 cm, the signal of the transmitting coil can be sent to the receiving coil through the relay coil.
4. The implantable electrical stimulation device according to claim 1, characterized in that: When the distance between the transmitting coil and the receiving coil is less than or equal to 2 cm, the signal of the transmitting coil can be sent to the receiving coil through the relay coil.
5. The implantable electrical stimulation device according to claim 1, characterized in that: The transmitting coil, the receiving coil and the relay coil are in a triangular shape.
6. The implantable electrical stimulation device according to claim 1, characterized in that: The transmitting coil, the receiving coil and the relay coil are in a rectangular shape.
7. The implantable electrical stimulation device according to claim 1, characterized in that: The transmitting coil, the receiving coil and the relay coil are circular in shape.
8. The implantable electrical stimulation device according to claim 1, characterized in that: The transmitting coil, the receiving coil and the relay coil are in an elliptical shape.
9. The implantable electrical stimulation device according to claim 1, characterized in that: The relay coil can be detachably mounted inside the transmitter or on the surface of the transmitter.
10. The implantable electrical stimulation device according to claim 9, characterized in that: The relay coil can be attached to the surface of the transmitter.