CN112290689B - Optimal design method for mutual inductance coefficient in wireless energy transmission system of medical implant device - Google Patents
Optimal design method for mutual inductance coefficient in wireless energy transmission system of medical implant device Download PDFInfo
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- H—ELECTRICITY
- H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
- H02J—CIRCUIT ARRANGEMENTS OR SYSTEMS FOR SUPPLYING OR DISTRIBUTING ELECTRIC POWER; SYSTEMS FOR STORING ELECTRIC ENERGY
- H02J50/00—Circuit arrangements or systems for wireless supply or distribution of electric power
- H02J50/10—Circuit arrangements or systems for wireless supply or distribution of electric power using inductive coupling
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- G—PHYSICS
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- G06F30/20—Design optimisation, verification or simulation
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01F—MAGNETS; INDUCTANCES; TRANSFORMERS; SELECTION OF MATERIALS FOR THEIR MAGNETIC PROPERTIES
- H01F38/00—Adaptations of transformers or inductances for specific applications or functions
- H01F38/14—Inductive couplings
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- H—ELECTRICITY
- H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
- H02J—CIRCUIT ARRANGEMENTS OR SYSTEMS FOR SUPPLYING OR DISTRIBUTING ELECTRIC POWER; SYSTEMS FOR STORING ELECTRIC ENERGY
- H02J50/00—Circuit arrangements or systems for wireless supply or distribution of electric power
- H02J50/90—Circuit arrangements or systems for wireless supply or distribution of electric power involving detection or optimisation of position, e.g. alignment
Abstract
The invention belongs to the technical field of medical implant devices, and particularly relates to an optimal design method for mutual inductance in a wireless energy transmission system of a medical implant device. The invention obtains an optimized design method for improving the mutual inductance coefficient M through theoretical analysis and HFSS simulation based on three-dimensional simulation software, and the method comprises the steps of finding out the influence of various parameters of a WPT system such as coil spacing, the number of turns of a transmitting coil, the inner radius and the outer radius of the transmitting coil, the turn spacing and the like on M under the condition that the transmitting coil and the receiving coil are in positive alignment by utilizing HFSS simulation and/or theoretical calculation, and verifying a simulation result through experiments; and the receiving angle of the receiving coil is overturned or the M reduction caused by the horizontal distance offset of the centers of the receiving coil and the transmitting coil is optimized and improved, thereby providing reference for the design of the wireless energy transmission system of the medical implant device. By using the method of the invention, the key parameter values of the sending coil and the receiving coil can be conveniently and rapidly obtained, and the mutual inductance coefficient is maximized.
Description
Technical Field
The invention belongs to the technical field of medical implant devices, and particularly relates to an optimal design method for mutual inductance in an electromagnetic induction wireless energy transmission system.
Background
In recent years, wireless energy transmission (hereinafter referred to as WPT) technology has been a hot spot of research attention of domestic and foreign scholars, and research results thereof can be widely applied to household appliances, electric vehicles and human body implantation devices, especially to human body implantation device applications. At present, implantable medical devices (hereinafter referred to as IMDs) are more and more widely applied in modern medicine, such as brain pacemakers, cardiac pacemakers, cochlear implants and spinal cord stimulators, which are widely applied in clinic, and retinal implants and brain-computer interfaces are widely researched in laboratories. In IMD applications, the radio source provides the possibility for non-invasive or minimally invasive diagnostics and long-term implantation of such devices.
As the size of medical implant devices is getting smaller and smaller, wireless energy transmission is generally performed on the devices in a manner of electromagnetic induction when the devices reach millimeter level. The wireless energy transmission system consists of a transmitting coil and a receiving coil. The transmitting coil is placed outside the body to generate an electromagnetic field, a portion of which is picked up by an implanted receiving coil to effect energy transfer. In the energy transmission system, mutual inductance (hereinafter referred to as M) is used as an important parameter in an induction link, and how to increase M in the WPT system is a general concern. Because the device is millimeter-sized, an energy receiving coil (hereinafter referred to as R) is integrated in the deviceX) The size is severely limited. The small coil is the key to improve the energy transmission efficiency and optimize the mutual inductance coefficient in the electromagnetic induction. And factors that affect the magnitude of M are mainly the relative positions of the transmitting and receiving coils, the medium surrounding the coils, the number of turns of the coils, the turn-to-turn pitch, and the average coil radius, among others.
Disclosure of Invention
The invention aims to provide an optimal design method of mutual inductance in a wireless energy transmission system of a medical implant device aiming at the medical implant device.
The aerial view and the side view of the WPT system in the HFSS are shown in the figures 1 and 2. Wherein, TXBeing transmitting coils, RXIs a receive coil. RinAnd RoutAre respectively transmittingThe inner and outer diameters of the coil; r2Radius of the receiving coil, n2The number of turns of the receiving coil; ravIs the mean radius of the transmitting coil, Rav＝0.5(Rin+Rout) B is the difference between the outer diameter and the inner diameter of the transmitting coil, and b is Rout-Rin)；n1The number of turns of the transmitting coil; h is the spacing between the receiving coil and the transmitting coil; d0Is the horizontal offset of the receive coil and the transmit coil; θ is the angular deflection of the receive coil in the vertical direction.
The calculation formula of the mutual inductance coefficient (M) in the electromagnetic induction wireless energy transmission system is as follows:
wherein, mu0For permeability in vacuum, K and J are the first and second elliptical integrals, respectivelymIs an ellipse integral module:
wherein n is a quantization coefficient and can be 0,1,2,3, …, and the larger n is, the more accurate the calculation result of M is.
As medical implant devices are scaled smaller and smaller, the devices themselves are in the millimeter range, and energy-receiving coils (R) are integrated within the devicesX) The size is severely limited. Such small coils are a general concern for improving energy transfer efficiency and power draw from the load. The key to solve the problem is to improve the mutual inductance coefficient in the electromagnetic induction.
The optimal design method for improving the mutual inductance coefficient is obtained by theoretical analysis and HFSS simulation based on three-dimensional simulation software. Specifically, various parameters of the WPT system under the condition that the transmitting coil and the receiving coil are aligned are found by utilizing HFSS simulation and/or theoretical calculation; these parameters include: transmitting coil (T)X) The influence of the number of turns, the inner and outer radiuses, the turn distance and the like of the coil on M and the influence of the distance between the transmitting coil and the receiving coil on M are verified through experiments. And the misalignment condition of the transmitting coil and the receiving coil is optimized, namely the receiving angle of the receiving coil is overturned or the M reduction caused by the horizontal distance offset of the centers of the receiving coil and the transmitting coil is improved. Provides beneficial reference for the design of wireless energy transmission systems for such medical implant devices.
Considering that the central magnetic field strength of the mosquito-repellent type planar spiral coil is stronger than that of the spring type solenoid coil, the present invention configures the transmitting coil as a planar spiral structure rather than a solenoid structure.
The invention provides an optimal design method of mutual inductance coefficient in a wireless energy transmission system of a medical implant device, the flow of which is shown in figure 3, and the method comprises the following specific steps:
(1) initial values of the WPT model with positive alignment were set up: initial values including receive coil geometry: radius of coil R2N number of turns of coil2And radius r of the wire2And the spacing h between the receiving coil and the transmitting coil;
(2) optimizing transmitter coil parameters including transmitter coil inner diameter R based on mutual inductance MinOuter diameter RoutAnd the number of transmitter coil turns n1；
(2.1) optimization parameter is mean radius R of transmitting coilavThe limiting conditions are the geometric shape and size of the receiving coil and the distance h between the receiving coil and the coil; the specific optimization steps are as follows: positive alignment of the transmitter coil with the receiver coil, fixed position and geometry of the receiver coil, and changing of the single turn transmitter coil (i.e. R)in＝Rout) R of (A) to (B)avSimulation study of R of the transmitting coilavContinuously changing from 5mm to 27mM is the mutual inductance coefficient M of the WPT model with the coil distance h being 20mm, and R with the maximum system M value under the limiting conditions is obtainedav；
(2.2) optimizing the parameter to be the number of turns n of the transmitting coil1And the difference b between the inner radius and the outer radius of the transmitting coil, wherein the limiting condition is the average radius R of the transmitting coil obtained by optimizing the step (2.1)av(ii) a The specific optimization steps are as follows: r of transmitting coilavFixing the result of the optimization in the step (2.1), and researching the number of turns n of the coil of the transmitting coil1When the coil inside and outside radius difference b is continuously changed from 6mm to 12mm from 3 turns to 7 turns, the mutual inductance coefficient M of the WPT model is obtained, and therefore the inside and outside radius of the transmitting coil and the number of turns of the coil, which can maximize M, are obtained;
(3) the WPT model result obtained by optimizing the simulation software under the positive alignment condition is verified by the theoretical calculation or experimental result of M; the result of the theoretical calculation is given by formula (1); the experimental result is measured by a vector network analyzer, and the method comprises the following specific steps: the coil was connected to a Vector Network Analyzer (VNA) through a pair of threaded pin-hole connectors (SMA), and the effect of the magnetic interference generated by the SMA connectors on the experimental results was reduced by using a method of de-embedding calibration (ref: H.Cho and D.Burk, "A three-step method for the de-embedding of high-frequency S-parameter measurements," IEEE traces. Electron Devices, vol.38, No.6, pp.1371-1375, Jun.1991). The method subtracts the parasitic parameters generated by the measurement fixture from the measurements of the original Device Under Test (DUT). Let the measured raw S parameter be denoted SdutCan be converted into admittance parameter Y, and the relationship is as followsdut＝(G0-Sdut)(Z0·Sdut+Z0)-1(ii) a Wherein G is0Is an identity matrix, Z0Is a characteristic impedance matrix of each port, denoted as 50G0. Similarly, S obtained by opening and closing the coil can be usedshortAnd SopenConversion to YshortAnd Yopen. After removing parasitic capacitive coupling and self capacitance, the Y parameter of the system can be expressed as Y ═ Y [ (Y)dut-Yopen)-1-(Yshort-Yopen)-1]-1. Converting the obtained Y parameter into a Z parameter (Z ═ Y)-1) Then, the result of the mutual inductance is obtained,
(4) based on mutual inductance M, optimizing a WPT model under the condition of misalignment:
the optimization parameter is the deviation (d) of the horizontal distance between the axes of the receiving coil and the transmitting coil0) And an angular deviation (θ) of the receiving coil in the vertical direction; the limiting conditions are the coil size and the distance of the WPT model obtained through optimization. The specific optimization steps are as follows: when there is a deviation (d) of the horizontal distance between the receiving coil and the transmitting coil axis0) In the process, the mutual inductance M is reduced, and at this time, the angular deviation (θ) of the receiving coil in the vertical direction is changed from 0 ° to 90 °, so that the angular adjustment that can improve the mutual inductance M of the system to the maximum can be obtained. Similarly, when the receiving coil has an angular deviation (theta) in the vertical direction, d is set0The horizontal distance adjustment which can lead the mutual inductance M of the system to be improved most can be obtained by continuously changing from 0mm to 30 mm.
By using the method of the invention, the key parameter values of the sending coil and the receiving coil can be conveniently and rapidly obtained, and the mutual inductance coefficient is maximized.
As an application example, an energy transmission system with a distance between the transmitting coil and the receiving coil of 20mm is optimized (in most cases, the distance between the transmitting coil and the receiving coil of the medical implant device is about 20 mm), and key parameters such as the average radius of the transmitting coil, the number of turns, and the coil arrangement, which generate the maximum M value, are obtained.
Optimizing the energy transfer system under the condition that the transmitting coil and the receiving coil are not aligned correctly can reduce the drop value of M caused by the misalignment of the coils, thereby ensuring the size of M.
Drawings
Figure 1 is a bird's eye view of a WPT system in HFSS.
Figure 2 is a side view of the WPT system in HFSS.
Figure 3 shows a flow chart of WPT model optimization.
FIG. 4 is a WPTThe system is at different average radii RavAnd M at different coil spacings h.
Fig. 5 shows that at h-20 mm, the transmitter coils have different n1And b, M of WPT system.
Fig. 6 shows the magnitude of the magnetic field in the vicinity of the transmitter coil when the transmitter coil has different coil arrangement densities.
FIG. 7 shows n in the transmitting coil1Simulation and experimental results of WPT system M as a function of frequency, 7 and b 6 mm.
FIG. 8 shows the horizontal distance offset (d) when the receiving and transmitting coils have different degrees0) (ii) a The mutual inductance coefficient of the WPT system is obtained when the receiving coil has different degrees of angular deflection in the vertical direction.
Detailed Description
For the implanted WPT system, the HFSS simulation software or/and a theoretical calculation formula are used for obtaining M under different conditions.
Figure 3 shows a flow chart of WPT model optimization.
Due to the larger size of the IMD, the probability of tissue infection, damage and cell death can be increased, and without loss of generality, the invention enables the radius R of the receiving coil to be larger2Taken as R2The wire radius of the receiving coil is taken to be 0.04mm, which is 5 mm. Since the distance between the transmitting coil and the receiving coil of the medical implant device is about 20mm in most cases, the distance between the transmitting coil and the receiving coil is 20mm in the present invention.
The method comprises the following specific steps:
(1) firstly, in order to reduce the damage of the implanted receiving coil to human tissues, the radius of the receiving coil is set to be R2A single-turn small coil with the radius of the lead wire of 0.04mm is formed, wherein the diameter of the single-turn small coil is 5 mm;
(2) after setting the spacing between the transmitting coil and the receiving coil in positive alignment to a certain value (for most cases, the spacing between the transmitting coil and the receiving coil in medical implants is about 20 mm), the average radius R of the transmitting coil is optimized by HFSS simulation and theoretical calculationavIncreasing the mutual inductance coefficient M of the WPT system;
(3) then adjusting the number of turns of the transmitting coil and the difference value between the inner diameter and the outer diameter, and further optimizing the transmitting coil to maximize M;
then, the optimized WPT model is measured and analyzed through a vector network analyzer by using a de-embedding calibration method so as to carry out experimental verification;
(4) finally, the distance deviation (d) exists between the implanted receiving coil and the transmitting coil in the horizontal direction0) And the receiving coil has an angular deviation (theta) in the vertical direction, and theta and d are respectively carried out0The optimization of the WPT system improves the mutual inductance coefficient M of the optimized WPT system under the condition of coil misalignment.
Figure 4 shows a WPT system with transmit coils having different mean radii RavM when the receive and transmit coils have different coil spacings h. Wherein n in the transmitting coil 11, b is 0, and the working frequency is 50 MHz. The solid line is the simulation result, and the dotted line is the theoretical calculation result, so that the simulation and calculation results are better matched. It is clearly seen that M decreases with increasing coil spacing, and R decreases when h is smalleravAnd R2The closer the size is, the larger the mutual inductance coefficient is; when h becomes large, R is appropriately increasedavA greater mutual inductance can be obtained. As an application example, when h is 20mm, RavThe maximum mutual inductance can be obtained for a 25mm transmitting coil.
Figure 5 shows a WPT system with different n transmitting coils at h-20 mm and 50MHz operating frequency1And b mutual inductance. It can be seen that M follows n1Increase in (c) is exponentially increasing; and the more closely the coils are arranged, the larger M. At n1When b is 6mm, M reaches a maximum of 11.1.
FIG. 6 shows n at an operating frequency of 50MHz when the excitation current of the transmitting coil is 1 ampere 17 and b 6mm (left) transmitting coils and n 17 and b 12mm (right) of the magnetic field strength in the vicinity of the transmitter coil. It is evident that a transmitting coil with a denser coil arrangement has a greater magnetic field strength, and thus a greater M is obtained for the energy transfer system.
FIG. 7 shows n in the transmitter coil when h is 20mm1When b is 6mm, M is following in WPT systemOperating frequency fpSimulation and experimental results of the changes. The result shows that the simulation result is well matched with the experimental result, which shows that the simulation result of the invention has higher reliability.
Fig. 8 is an example of misalignment of the transmit and receive coils in an application. d0And the M value of the WPT system is continuously changed from 0mm to 20mm, and the theta is continuously changed from 0 degrees to 90 degrees. The results of fig. 4-7 are based on the transmit and receive coils being perfectly aligned. However, as shown in FIG. 2, the coils may be misaligned (1) by a deviation in the distance between the implanted receiver coil and the transmitter coil in the horizontal direction (d)0) And (2) an angular deviation (θ) of the receiving coil in the vertical direction. The WPT model is simulated by adopting HFSS, the working frequency of the WPT model is 50MHz, and n of the transmitting coil 17 and 6 mm. As can be seen from the figure, for a perfectly aligned WPT system, d is increased0And θ, resulting in a significant decrease in the value of M. Furthermore, when there is a deviation in the horizontal distance of the receiver coil from the center of the transmitter coil, rotating the receiver coil by an appropriate angle helps to increase the value of M, because a higher magnetic field can be obtained in the receiver coil. Also, if the receive coil has an offset in the angle of rotation, an appropriate horizontal offset can be introduced to increase the value of M.
Claims (5)
1. An optimal design method for mutual inductance coefficients in a wireless energy transmission system of a medical implant device is characterized by comprising the following specific steps:
(1) initial values of the WPT model with positive alignment were set up: initial values including receive coil geometry: radius of coil R2N number of turns of coil2And radius r of the wire2And the spacing h between the receiving coil and the transmitting coil;
(2) optimizing transmitter coil parameters including transmitter coil inner diameter R based on mutual inductance MinOuter diameter RoutAnd the number of transmitter coil turns n1；
(2.1) optimization parameter is mean radius R of transmitting coilavThe limiting conditions are the geometric shape and size of the receiving coil and the distance h between the receiving coil and the coil;
(2.2) optimizing the parameter to be the number of turns n of the transmitting coil1And the difference b between the inner radius and the outer radius of the transmitting coil, wherein the limiting condition is the average radius R of the transmitting coil obtained by optimizing the step (2.1)av；
(3) The WPT model result obtained by optimizing the simulation software under the positive alignment condition is verified by the theoretical calculation or experimental result of M;
(4) based on mutual inductance M, optimizing a WPT model under the condition of misalignment:
the optimized parameter is the deviation d of the horizontal distance between the axes of the receiving coil and the transmitting coil0And an angular deviation θ of the receiving coil in the vertical direction; the limiting conditions are the coil size and the distance of the WPT model obtained through optimization.
2. The optimization design method according to claim 1, characterized in that in step (2.1) the average radius R of the optimized parameter transmitting coilavThe method comprises the following specific steps: aligning the transmitter coil with the receiver coil, fixing the position and geometric dimensions of the receiver coil, and varying the R of a single turn transmitter coilavSimulation study RavWhen the coil pitch h is changed from 5mm to 27mm continuously, the mutual inductance M of the WPT model is 20mm, and R which maximizes the value of the system M under the above restriction conditions is obtainedav；
The number of turns n of the parameter optimizing transmitting coil in the step (2.2)1And the inner and outer radius difference b of the transmitting coil comprises the following specific steps: r of transmitting coilavFixing as a result of the optimization in step (2.1), the number of turns n of the transmitting coil is studied1And when the coil inside and outside radius difference b is continuously changed from 6mm to 12mm from 3 turns to 7 turns, the mutual inductance M of the WPT model is obtained, so that the inside and outside radius of the transmitting coil and the number of turns of the coil, which can maximize M, are obtained.
3. The optimal design method according to claim 2, wherein the WPT model result obtained by optimizing the WPT model under the above positive alignment condition by using simulation software in the step (3) is verified by using theoretical calculation or experimental result of M; experimental results by vector networksThe analyzer performs measurement, and the specific steps are as follows: connecting the coil to a vector network analyzer through a pair of threaded pinhole connectors SMA, and reducing the influence of magnetic interference generated by the SMA connectors on experimental results by using a de-embedding calibration method; the method subtracts the parasitic parameters generated by the measuring clamp from the measurement of the original tested equipment; let the measured raw S parameter be denoted SdutCan be converted into admittance parameter Y, and the relationship is as followsdut＝(G0-Sdut)(Z0·Sdut+Z0)-1(ii) a Wherein G is0Is an identity matrix, Z0Is a characteristic impedance matrix of each port, denoted as 50G0(ii) a Similarly, S obtained by opening and short-circuiting the coilshortAnd SopenConversion to YshortAnd Yopen(ii) a After removing the parasitic capacitive coupling and self-capacitance, the Y parameter of the system is expressed as:
Y＝[(Ydut-Yopen)-1-(Yshort-Yopen)-1]-1，
converting the obtained Y parameter into a Z parameter (Z ═ Y)-1) Then, the result of the mutual inductance is obtained,
4. the optimal design method according to claim 3, wherein the step (4) of optimizing the WPT model under the misalignment condition based on the mutual inductance M comprises the following specific steps: when the receiving coil and the transmitting coil have horizontal distance deviation d0When the mutual inductance M is reduced, the angle deviation theta of the receiving coil in the vertical direction is changed from 0 degree to 90 degrees, and the angle adjustment which can enable the mutual inductance M of the system to be improved most is obtained; similarly, when the receiving coil has an angle deviation theta in the vertical direction, d is adjusted0The horizontal distance adjustment which can lead the mutual inductance M of the system to be improved most is obtained by continuously changing from 0mm to 30 mm.
5. The optimal design method according to claim 3, wherein the theoretical calculation formula of the mutual inductance M is as follows:
wherein, mu0For permeability in vacuum, K and J are the first and second elliptical integrals, respectivelymIs an ellipse integral module:
wherein R isinAnd RoutRespectively the inner diameter and the outer diameter of the transmitting coil; r2Radius of the receiving coil, n2The number of turns of the receiving coil; ravIs the mean radius of the transmitting coil, Rav＝0.5(Rin+Rout) B is the difference between the outer diameter and the inner diameter of the transmitting coil, and b ═ Rout-Rin)；n1The number of turns of the transmitting coil; h is the spacing between the receiving coil and the transmitting coil; d0Is the horizontal offset of the receive coil and the transmit coil; theta is the angular deflection of the receiving coil in the vertical direction; n is a quantization coefficient, and 0,1,2,3, … is taken, wherein the larger n is, the more accurate the calculation result of M is.
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Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101572158A (en) * | 2009-03-03 | 2009-11-04 | 山东大学 | Novel electromagnetic mechanism and mathematical analysis model thereof |
| CN103559994A (en) * | 2013-11-18 | 2014-02-05 | 天津工业大学 | Receiving coil design used for wireless power supply of railway locomotive |
| CN107766669A (en) * | 2017-11-01 | 2018-03-06 | 清华大学 | A kind of Wireless charging coil self-induction and the unit for electrical property parameters computational methods of mutual inductance |
| CN110676947A (en) * | 2019-10-17 | 2020-01-10 | 南京理工大学 | Curved surface coil wireless power transmission system capable of inhibiting curvature angle splitting phenomenon |
-
2020
- 2020-09-16 CN CN202010975640.XA patent/CN112290689B/en active Active
Patent Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101572158A (en) * | 2009-03-03 | 2009-11-04 | 山东大学 | Novel electromagnetic mechanism and mathematical analysis model thereof |
| CN103559994A (en) * | 2013-11-18 | 2014-02-05 | 天津工业大学 | Receiving coil design used for wireless power supply of railway locomotive |
| CN107766669A (en) * | 2017-11-01 | 2018-03-06 | 清华大学 | A kind of Wireless charging coil self-induction and the unit for electrical property parameters computational methods of mutual inductance |
| CN110676947A (en) * | 2019-10-17 | 2020-01-10 | 南京理工大学 | Curved surface coil wireless power transmission system capable of inhibiting curvature angle splitting phenomenon |
Non-Patent Citations (4)
| Title |
|---|
| 介入式微型医疗装置连续定位系统的建模;郭旭东等;《系统仿真学报》;20070805(第15期);全文 * |
| 小功率无线电能传输系统谐振线圈设计优化;冯帆等;《电子测量技术》;20170115(第01期);全文 * |
| 植入式医疗设备磁谐振式无线输电系统线圈设计研究;曾玉凤;《中国优秀硕士学位论文全文数据库 工程科技Ⅱ辑》;20200115(第1期);全文 * |
| 电磁共振式无线电能传输系统距离特性的分析;陈文仙等;《电力系统自动化》;20150425(第08期);全文 * |
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