Implantable electrical stimulation device
By introducing a relay coil design into the implanted electrical stimulation device, the problem of large volume and weight of the transmitter is solved, and the separation between the transmitter and the receiver is achieved, reducing the burden of use and improving the patient experience.
Patent Information
- Application Number
- CN202421736354.8
- 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
The emitters of existing implantable electrical stimulation devices are large in size and weight, which leads to inconvenience in use by medical staff and patients, and has poor experience when applied to patients' skin.
Using the design of a transmitter, a receiver, a first relay coil and a second relay coil, through a predetermined spacing and wire connection between the first relay coil and the transmitting coil, the signal is transmitted to the receiving coil through the relay coil, reducing direct contact between the transmitter and the receiver.
With extremely small transmission losses or basically unchanged transmission efficiency, the transmitter and receiver are separated, reducing the burden on medical staff and patients, and improving the patient's user experience.
Smart Images
Figure CN223042008U_ABST
Abstract
Description
Technical Field
[0001] The utility model relates to the field of medical devices, in particular 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] An implantable electrical stimulation device generally includes a transmitter and a receiver. During use, the receiver is implanted into the human body, and the transmitter is attached to the skin corresponding to the receiver on the outside of the human body, and the signal and energy of the transmitter are sent to the receiver in the human body through NFC technology. However, the volume and weight of the transmitter are relatively large, which will be a relatively large burden for both medical staff and the patient himself when holding the transmitter. In addition, directly attaching the transmitter with a relatively large volume and weight to the patient's skin will also result in a very poor user experience for the patient.
[0004] Therefore, there is a need for further improvement in the existing implantable electrical stimulation devices.
[0005] The information disclosed in the background section of the present utility model is only intended to increase the understanding of the overall background of the present 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 present utility model is to provide an implantable electrical stimulation device, which can reduce the burden on medical staff and patients and improve the user experience of patients.
[0007] The present utility model provides an implantable electrical stimulation device, including: 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 first relay coil, which is arranged on or inside the transmitter; and a second relay coil, which is electrically connected to the first relay coil, and the first relay coil has a first predetermined distance from the transmitting coil; wherein, when the distance between the second relay coil and the receiving coil is less than a second predetermined distance, the signal of the transmitting coil can be sent to the receiving coil through the first relay coil and the second relay coil.
[0008] Preferably, the second relay coil is electrically connected to the first relay coil through a wire.
[0009] Preferably, the range of the first predetermined distance is 0-1 cm.
[0010] Preferably, the second predetermined distance is less than or equal to 1 cm.
[0011] Preferably, the shapes of the transmitting coil, the receiving coil, the first relay coil, and the second relay coil are triangular.
[0012] Preferably, the shapes of the transmitting coil, the receiving coil, the first relay coil, and the second relay coil are rectangular.
[0013] Preferably, the shapes of the transmitting coil, the receiving coil, the first relay coil, and the second relay coil are circular.
[0014] Preferably, the shapes of the transmitting coil, the receiving coil, the first relay coil, and the second relay coil are oval.
[0015] Preferably, the first relay coil is detachably mounted inside the transmitter or on the surface of the transmitter.
[0016] Preferably, the first relay coil can be pasted on the surface of the transmitter.
[0017] The implementation scheme of the present utility model can separate the transmitter and the receiver at the cost of extremely low transmission loss or while ensuring that the basic transmission efficiency remains basically unchanged. During use, the transmitter can be placed in an easily accessible position to reduce the burden on medical staff and patients, and the smaller second relay coil can be attached to the patient's skin to improve the patient's usage experience.
[0018] The device of the present utility model has other characteristics and advantages, which will be obvious from the accompanying drawings incorporated herein and the subsequent implementation schemes, or will be described in detail in the accompanying drawings incorporated herein and the subsequent implementation schemes. These accompanying drawings and implementation schemes are jointly used to explain the specific principles of the present utility model. Description of the Drawings
[0019] Figure 1A Schematic diagram 1 of the structure of the implantable electrical stimulation device according to the implementation scheme of the present utility model;
[0020] Figure 1B Schematic diagram of the structure of the implantable electrical stimulation device according to the implementation scheme of the present utility model Figure 2 ;
[0021] Figure 2 Schematic diagram of the transmitting coil, receiving coil, first relay coil, and second relay coil modeled in HFSS;
[0022] Figure 3 For Figure 2 Simulation result diagram.
[0023] Description of the reference numerals in the drawings:
[0024] 100: Transmitting coil 200: Receiving coil
[0025] 500: Transmitter 600: Receiver
[0026] 700: First relay coil 701: Wire
[0027] 800: Second relay coil.
[0028] It should be understood that the drawings are not necessarily drawn to scale and instead present simplified representations of various features for the purpose of illustrating 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.
[0029] In these drawings, throughout the multiple drawings, the same reference numerals represent the same or equivalent parts of the present utility model. Detailed implementation manners
[0030] The following will refer in detail to the various implementation manners of the present utility model, and examples of these implementation manners are presented in the drawings and described as follows. Although the present utility model will be described in combination with the 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 can be included within the spirit of the present utility model and the scope defined by the appended claims.
[0031] 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.
[0032] The following will be described in combination with Figures 1A to 3 the implantable electrical stimulation device of the implementation manner of the present utility model.
[0033] Figure 1A is a first schematic structural diagram of the implantable electrical stimulation device of the implementation manner of the present utility model; Figure 1B is the schematic structure of the implantable electrical stimulation device of the implementation manner of the present utility model Figure 2 ; Figure 2 is a schematic diagram of the transmitting coil, receiving coil, first relay coil, and second relay coil modeled in HFSS; Figure 3 is Figure 2 the simulation result diagram of.
[0034] As Figure 1A and Figure 1B shown, the implantable electrical stimulation device of the embodiment of the present utility model includes: a transmitter 500, a receiver 600, a first relay coil 700, and a second relay coil 800.
[0035] The transmitter 500 is disposed outside the human body and has a transmitting coil 100.
[0036] 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.
[0037] The first relay coil 700 is disposed on the transmitter 500 (for reference, see Figure 1B ) or inside the transmitter 500 (for reference, see Figure 1A ).
[0038] The second relay coil 800 is electrically connected to the first relay coil 700, and the first relay coil 700 has a first predetermined distance from the transmitting coil 100.
[0039] Wherein, when the distance between the second relay coil 800 and the receiving coil 200 is less than a second predetermined distance, the signal of the transmitting coil 100 can be sent to the receiving coil 200 through the first relay coil 700 and the second relay coil 800. It should be noted that the signal only passes through the first relay coil 700 and the second relay coil 800, and the first relay coil 700 and the second relay coil 800 themselves do not have the transmitting ability.
[0040] The embodiment of the present utility model can separate the transmitter 500 and the receiver 600 at the cost of extremely small transmission loss or while ensuring that the basic transmission efficiency remains basically unchanged. During use, the transmitter 500 can be placed in an easily accessible position to reduce the burden on medical staff and patients, and the smaller second relay coil 800 can be attached to the patient's skin to improve the patient's experience.
[0041] In an exemplary embodiment, the second relay coil 800 is electrically connected to the first relay coil 700 through a wire 701, and the length of the wire 701 is less than or equal to 1 m.
[0042] In an exemplary embodiment, the range of the first predetermined distance between the first relay coil 700 and the transmitting coil 100 is 0 to 1 cm.
[0043] In an exemplary embodiment, the second predetermined spacing between the second relay coil 800 and the receiving coil 200 is less than or equal to 1 cm and greater than the thickness of the skin. Since the receiving coil 200 is disposed inside the human body and the second relay coil 800 is disposed outside the human body, the distance from the second relay coil 800 to the receiving coil 200 needs to be greater than the thickness of the skin.
[0044] In one embodiment, the shapes of the transmitting coil 100, the receiving coil 200, the first relay coil 700, and the second relay coil 800 are triangular.
[0045] In another embodiment, the shapes of the transmitting coil 100, the receiving coil 200, the first relay coil 700, and the second relay coil 800 are rectangular.
[0046] In yet another embodiment, the shapes of the transmitting coil 100, the receiving coil 200, the first relay coil 700, and the second relay coil 800 are circular.
[0047] In yet another embodiment, the shapes of the transmitting coil 100, the receiving coil 200, the first relay coil 700, and the second relay coil 800 are oval.
[0048] In an exemplary embodiment, the first relay coil 700 is detachably mounted inside the transmitter 500 or on the surface of the transmitter 500. For example, the first relay coil 700 can be pasted on the surface of the transmitter 500.
[0049] When the first relay coil 700 is damaged, the first relay coil 700 can be detached and replaced with a new first relay coil 700. Similarly, the second relay coil 800 can also be replaced.
[0050] As Figure 2 shown, in HFSS, the original transmitting coil 100 and receiving coil 200 are placed 30 cm apart. Then, the first relay coil 700 is disposed at the transmitting coil 100, the second relay coil 800 is disposed at the receiving coil 200, and the first relay coil 700 and the second relay coil 800 are connected. Specifically, the first relay coil 700 is electrically connected to the second relay coil 800 through a wire 701.
[0051] The simulation results of the dual relay coils are as Figure 3 shown. S21 is -9.33 dB, and the standing wave performance at both ends is good. Using the relay coils can achieve the level without relay coils and with the transmitting coil 100 and receiving coil 200 1 cm apart.
[0052] Through the above simulations and analyses, the following conclusions can be obtained:
[0053] The dual-relay coil can separate the transmitting end and the receiving end, and can achieve the effect of having no relay coil and a relatively close distance between the transmitting coil and the receiving coil.
[0054] Test verification
[0055] (1) The transmitting end is a demo board
[0056] Make a dual-relay coil with square coils of 2*2 cm at both ends and an intermediate connecting wire length of about 50 cm.
[0057] The transmitting end (i.e., the transmitter 500 including the transmitting coil 100) and the receiving end (i.e., the receiver 600 including the receiving coil 200) use a demo board. Align the first relay coil 700 with the transmitting end and the second relay coil 800 with the receiving end. The distance between the transmitting end and the first relay coil 700 is 2.5 mm, and the distance between the receiving end and the second relay coil 800 is 2.5 mm. The output voltage of the receiving end is 7.02 V, and the power under a 500Ω load is calculated to be 98.5 mW.
[0058] When the distance between the transmitting coil 100 and the receiving coil 200 is 5 mm, the transmitting coil 100 and the receiving coil 200 are directly coupled. The measured voltage at the receiving end is 7.1 V, and the power under a 500Ω load is calculated to be 150 mW.
[0059] The experiment shows that the energy transfer performance of the relay dual-coil is basically equivalent to the case of direct coupling between the transmitting coil and the receiving coil.
[0060] (2) The transmitting end is a mobile phone
[0061] Make an extended dual-relay coil for the mobile phone. One end of the dual-relay coil is a square coil of 2*2 cm, and the other end is a rectangular coil of 3*2 cm. The length of the intermediate connecting wire is about 50 cm. Among them, the end with the rectangular coil shape is the end close to the mobile phone.
[0062] Using the extended relay coil for communication, it can be seen that the mobile phone can read the UID in the tag chip. Later, different brands of mobile phones will be used for testing, and the energy transfer efficiency will be optimized by changing the matching. The test results are shown in Table 1.
[0063] Table 1
[0064] Mobile phone brand Received voltage V Load of the receiving end Ω Received power mW Xiaomi 10 8.28 500 137 Meizu 17 pro 6.96 500 96.7 Huawei Mate 60 5.05 500 50.9
[0065] By comparison, it can be seen that different brands of mobile phones have different transmitting powers and coil sizes, resulting in differences in the performance of the receiving end.
[0066] In the experiment of the dual-relay coil, the results show that the dual-relay coil can achieve communication and energy transfer normally. However, under different brands and different sizes of transmitting antennas, there are certain differences in the received energy. This indicates that for different devices or usage scenarios, the relay dual-coil needs to be of different sizes and matches to achieve the best performance.
[0067] Other components and functions of the implantable electrical stimulation device according to the embodiments of the present invention are known to those skilled in the art. To reduce redundancy, they will not be described in detail.
[0068] 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.
[0069] 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.
[0070] The first relay coil 700 is installed inside or on the surface of the transmitter 500, and it is necessary to ensure that the first relay coil 700 is close to the transmitting coil 100 of the transmitter 500.
[0071] The transmitter 500 is placed in an easily accessible position, such as in the pocket of the patient's clothes.
[0072] The second relay coil 800 is placed close to or attached to the skin of the back where the receiver 600 is implanted.
[0073] The switch of the transmitter 500 is turned on, so that the signal of the transmitter 500 is transmitted through the transmitting coil 100, the first relay coil 700, and the second relay coil 800 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. This solution separates the transmitter 500 and the receiver 600 at the cost of extremely low transmission loss or while ensuring that the basic transmission efficiency remains basically unchanged. When in use, the transmitter 500 can be placed in an easily accessible position, reducing the burden on medical staff and patients, and attaching the smaller second relay coil 800 to the patient's skin, improving the patient's usage experience.
[0074] If the first relay coil 700 and the second relay coil 800 are damaged, the damaged first relay coil 700 and second relay coil 800 can be disassembled and replaced with new first relay coil 700 and second relay coil 800.
[0075] For the sake of convenience in explanation and for the purpose of precisely defining the appended claims, the terms "upper", "lower", "inner", "outer", "above", "below", "upper surface", "lower surface", "upper side", "lower side", "upward", "downward", "front", "rear", "back", "inner side", "outer side", "inward", "outward", "interior", "exterior", "inner part", "outer part", "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.
[0076] 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 forms disclosed, and obviously many modifications and variations are possible in light of the above teachings. 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 its 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; A first relay coil, which is arranged on the transmitter or inside the transmitter; as well as a second relay coil electrically connected to the first relay coil, the first relay coil being spaced a first predetermined distance from the transmitting coil; When the distance between the second relay coil and the receiving coil is less than the second predetermined distance, the signal of the transmitting coil can be sent to the receiving coil through the first relay coil and the second relay coil.
2. The implantable electrical stimulation device according to claim 1, characterized in that: The second relay coil is electrically connected to the first relay coil through a conductive wire.
3. The implantable electrical stimulation device according to claim 1, characterized in that: The first predetermined distance ranges from 0 to 1 cm.
4. The implantable electrical stimulation device according to claim 1, characterized in that: The second predetermined distance is less than or equal to 1 cm.
5. The implantable electrical stimulation device according to claim 1, characterized in that: The transmitting coil, the receiving coil, the first relay coil and the second 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, the first relay coil and the second 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, the first relay coil and the second 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, the first relay coil and the second relay coil are elliptical in shape.
9. The implantable electrical stimulation device according to claim 1, characterized in that: The first 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 1, characterized in that: The first relay coil can be attached to the surface of the transmitter.