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High-efficiency power transfer at a long distance can be efficiently established using resonance-based wireless techniques. In contrast to the conventional two-coil-based inductive links, this paper presents a magnetically coupled fully planar four-coil printed spiral resonator-based wireless power-transfer system that compensates the adverse effec...
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Context 1
... a nominal coupling distance of d = 10 mm, Rload = 100 Ω, and f = 13.56 MHz, Table 4 lists the electrical specifications of the designed coils achieved from simulation. Figure 14 shows the experimental setup [35] to verify the fabricated coils. Resonant circuit similar to Figure 6 is built for both the square and circular coils. ...
Context 2
... a nominal coupling distance of d = 10 mm, R load = 100 Ω, and f = 13.56 MHz, Table 4 lists the electrical specifications of the designed coils achieved from simulation. Figure 13a,b shows the fabricated square and circular coils, respectively. For a nominal coupling distance of d = 10 mm, Rload = 100 Ω, and f = 13.56 ...
Context 3
... a nominal coupling distance of d = 10 mm, Rload = 100 Ω, and f = 13.56 MHz, Table 4 lists the electrical specifications of the designed coils achieved from simulation. Figure 14 shows the experimental setup [35] ...
Context 4
... 10 mm of coupling distance between the TX and RX coils and 13.56-MHz frequency, the maximum simulated and measured PDLs for the square coil resonator are 481.76 and 396 mW, respectively. Table 4 lists the comparison of the coupling coefficients between the square and circular coils. Thus, Equation (37) justifies the higher PDLs of the circular coil, which are 570.35 and 443.5 mW, respectively, under the simulation and measurement conditions. ...
Context 5
... 10 mm of coupling distance between the TX and RX coils and 13.56-MHz frequency, the maximum simulated and measured PDLs for the square coil resonator are 481.76 and 396 mW, respectively. Table 4 lists the comparison of the coupling coefficients between the square and circular coils. Thus, Equation (37) justifies the higher PDLs of the circular coil, which are 570.35 and 443.5 mW, respectively, under the simulation and measurement conditions. ...
Context 6
... 10 mm of coupling distance between the TX and RX coils and 13.56-MHz frequency, the maximum simulated and measured PDLs for the square coil resonator are 481.76 and 396 mW, respectively. Table 4 lists the comparison of the coupling coefficients between the square and circular coils. Thus, Equation (37) justifies the higher PDLs of the circular coil, which are 570.35 and 443.5 mW, respectively, under the simulation and measurement conditions. ...
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Citations
... The benefits of using a resonant 3-antenna system, with passive resonator co-located on the implanted device, over the conventional 2-antenna system are coupling enhancement, better misalignment insensitivity and better bandwidth 53,54 . Figure 2b and Supplementary Fig. 5a, b illustrate the simulated B-field of the 3-antenna system, in which the receiver antenna and the resonator are co-located on the top and bottom sides of the implant. ...
... The geometric parameters of the implant antenna (i.e., the width, the gap between adjacent turns, the dimension and shape of the antennas) are chosen to optimize transmission efficiency at 13.56 MHz ( Supplementary Fig. 6a, b) while minimizing the size of the implant. Adding a resonator improves the coupling between the transmitter and receiver as shown in simulations ( Supplementary Fig. 7a) [54][55][56][57] . A comparison between the transmission efficiency of the 3-antenna WPT and the conventional 2-antenna WPT shows that adding the resonator antenna increases the transmission efficiency from 12% to 37% ( Supplementary Fig. 7b). ...
Electrical stimulation of the neuromuscular system holds promise for both scientific and therapeutic biomedical applications. Supplying and maintaining the power necessary to drive stimulation chronically is a fundamental challenge in these applications, especially when high voltages or currents are required. Wireless systems, in which energy is supplied through near field power transfer, could eliminate complications caused by battery packs or external connections, but currently do not provide the harvested power and voltages required for applications such as muscle stimulation. Here, we introduce a passive resonator optimized power transfer design that overcomes these limitations, enabling voltage compliances of ± 20 V and power over 300 mW at device volumes of 0.2 cm², thereby improving power transfer 500% over previous systems. We show that this improved performance enables multichannel, biphasic, current-controlled operation at clinically relevant voltage and current ranges with digital control and telemetry in freely behaving animals. Preliminary chronic results indicate that implanted devices remain operational over 6 weeks in both intact and spinal cord injured rats and are capable of producing fine control of spinal and muscle stimulation.
... Based on the near-field coupling, the quality factor (Q-factor) of self-resonating structures and coupling coefficient between the structures play important roles in the WPT performance. For increasing the Q-factor, various novel resonators have been designed, such as metallic-coil based resonators [13][14][15], dielectric resonators [16,17], and cavity mode resonators [18,19]. For enhancing the coupling efficiency and controlling the power transfer route, the metamaterials and metasurfaces also been introduced to tailor the near-field and manipulate the coupling between the transmitter and the receiver ends [20][21][22][23]. ...
In this paper, we use a pair of self-resonating subwavelength spoof plasmonic structures to achieve remote non-radiative terahertz wireless power transfer, while nearly without affecting the electromagnetic environment of free space around the structure. The resonating frequency and quality factor of the magnetic dipole mode supported by the spoof plasmonic structures can be freely tuned by tailoring the geometric structure. By putting the weak source and detector into the self-resonating structures, we can find that the effective non-radiative terahertz power transferring distance can reach several hundred times the radius of the structures. Finally, we also demonstrate the efficient wireless power transfer capability for the multi-target receiving system. These results may provide a novel approach to the design of non-radiative terahertz wireless power transfer and communications.
... To comply with ICNIRP guidelines, the IEEE C95.1-2005 standard limits the average SAR over any 10 g of tissue in the shape of a cube to less than 2 W/kg (SAR 10g, max ≤ 2 W/kg), which is followed by the European Union [58]. Figure 4 shows the generalized steps for designing, manufacturing and testing inbody antennas. In the first step, the researchers benchmark the antenna parameters based on the specifications provided in Section 2. These parameters are then used to generate an analytical model, which leads to analysis and simulation in programming and numeric computing platforms, such as MATLAB [44,[59][60][61][62][63][64]. This is an important step of optimizing the antenna to accomplish the best performance [65]. ...
... To comply with IC-NIRP guidelines, the IEEE C95.1-2005 standard limits the average SAR over any 10 g of tissue in the shape of a cube to less than 2 W/kg (SAR10g, max ≤ 2 W/kg), which is followed by the European Union [58]. Figure 4 shows the generalized steps for designing, manufacturing and testing inbody antennas. In the first step, the researchers benchmark the antenna parameters based on the specifications provided in Section 2. These parameters are then used to generate an analytical model, which leads to analysis and simulation in programming and numeric computing platforms, such as MATLAB [44,[59][60][61][62][63][64]. This is an important step of optimizing the antenna to accomplish the best performance [65]. ...
In-body biomedical devices (IBBDs) are receiving significant attention in the discovery of solutions to complex medical conditions. Biomedical devices, which can be ingested, injected or implanted in the human body, have made it viable to screen the physiological signs of a patient wirelessly, without regular hospital appointments and routine check-ups , where the antenna is a mandatory element for transferring bio-data from the IBBDs to the external world. However, the design of an in-body antenna is challenging due to the dispersion of the dielectric constant of the tissues and unpredictability of the organ structures of the human body, which can absorb most of the antenna radiation. Therefore, various factors must be considered for an in-body antenna, such as miniaturization, link budget, patient safety, biocompatibility, low power consumption and the ability to work effectively within acceptable medical frequency bands. This paper presents a comprehensive overview of the major facets associated with the design and challenges of in-body antennas. The review comprises surveying the design specifications and implementation methodology, simulation software and testing of in-body biomedical antennas. This work aims to summarize the recent in-body antenna innovations for biomedical applications and indicates the key research challenges.
... In [20], the heating performance of coil type implanted devices was evaluated for uncompensated coils and for coils with reactive power compensation. Moreover, different inductive links and coil type implants were investigated with respect to a four-coil system by the authors in [21] and [22] considering reactive power compensation with respect to the Q-factor. Additionally, a performance optimization has been done. ...
Millimeter-sized devices, which are implanted within tumors by a minimally invasive operation technique, are very promising for tumor treatment with a contactless thermal ablation procedure. These implanted devices are heated from outside of the patients’ body by an alternating magnetic field. For minimizing unwanted influencing and heating of healthy tissue and other devices inside the patients’ body, the ratio of generated heating power within the implanted devices to required magnetic field strength has to be maximized. In this paper, the heating power generated by eddy currents within solid and electrically conductive implanted devices, whose dimensions are restricted by the minimally invasive operation technique, is analyzed and optimized based on a combination of numerical and analytic calculations for different parameter sets of material and magnetic field properties. The parameters for achieving maximum heating power are presented along with the dependency of the heating power on these parameters. The results are validated by experimental prototype measurements. Furthermore, the specific absorption rate is evaluated based on specific coil configurations for generating the alternating magnetic field. This paper shows the feasibility of significantly increasing the heating power of solid and electrically conductive implanted devices by choosing the appropriate properties of the implant material. This enhances the safety and the well-being of the patients and represents a great benefit for the outcome of the tumor treatment.
... The applicable depth of IBMDs inside the human tissue was specified according to the size of the implants [42]. However, the IBMD is generally located at a depth of less than 10 mm in human tissue [56]. ...
Implantable biomedical devices (IBMD) and biomedical sensors (BMS) enhance patients' quality of life by monitoring vital signs, detecting diseases, and replacing malfunctioning organs. However, IBMDs and BMSs require battery power to operate, and they have limited battery life. Wireless power transfer (WPT) is one practical way to address this limitation. In this paper, the authors designed and implemented WPT-based magnetic resonant coupling (MRC) using a spider-web coil (SWC) (WPT-MRC-SWC) that supplies the proposed IBMD, including accelerometer sensors, the single-chip microcontroller ATmega 328, and the nRF24L01 wireless protocol, with power. The WPT-MRC-SWC examines acceleration measurements on three knee-joint axes (X, Y, and Z) in five different positions: sitting, standing, walking, lying down, and jogging. The SWC of transmitters and receivers (implanted) exhibits an operating frequency of 1.78 MHz with a series/parallel (S/P) configuration. The implanted system's data, transmitted outside the human body using nRF24L01, operates at 2.4 GHz. The results reveal that WPT provides 5 V at an air gap of 60 mm between the receiver and transmitter coils, indicating that it can run or charge IBMD batteries without failure. This study validates the effectiveness of the WPT-MRC-SWC by applying it to an actual application.
... The difference in the inductances required for each topology impacts the potential WPT applications. In biomedical applications such as implantable medical devices, wearable electronics, and sensors, the transmitting and receiving coils should be small [41], which consequently results in short transmission distances, and the shunt-shunt resonator topology may be a preferred choice. Conversely, for applications where large inductors are required for power transmission over mid-range distances, such as EV charging systems, smart home devices, and portable devices, the series-series topology may be the preferred choice. ...
... The researchers designed four coils, two on the transmitter side characterized as the source and transmitter coils and two on the receiver side characterized as the receiver and load coils, for enabling high transmission efficiency. 24 This method offers achieving high efficiency along with extension of the transmission distance. Since the human body has limited available space inside, placing multiple coils inside the human body, such as coronary artery sensors, is challenging. ...
Wireless power transfer technology features shorter power transmission distances in biomedical applications. This is a result of the small size of the implanted coils, biocompatible material conductivity, and the large distances between the receiving and transmitting coils. There have been numerous attempts to improve the power transfer efficiency across longer distances. Multiple coils, including 2-, 3-, 4-, and multi-layered coils, were previously considered. This study proposes a novel approach to achieve higher power transmission efficiency by integrating a single coil on the receiving side and three asymmetric coils on the transmitter side. As such, it delivers power to the sensor implanted within the coronary artery that monitors the blood pressure while introducing a uniquely shaped stent. The efficiency of power transmitted to the stent in its dual implanted forms, helical and zigzag helical, was examined as well, with the wireless power transmission system thereby analyzed at the 27 MHz Industrial Scientific Medical band operating frequency. For the four-coil technique, the power transmission efficiency at a distance of 25 mm between the receiver and transmitter sides by using biological human tissue as a medium between the transmission coils and the receiver stent can reach 56.42%, whereas other approaches show lower efficiencies: the three-coil method's efficiency is 32.88%, the double-layer parallel method's efficiency is 27.75%, the two-coil method's efficiency is 24.76%, the triple-layer parallel method's efficiency is 17.31%, the double-layer series method's efficiency is 0.501%, and the triple-layer series method's transmission efficiency is 0.092%. In addition, the suggested approach is demonstrated to be more efficient than prior designs with regard to the size of the implanted coils, which represent stents.
... However, there is an optimal distance to transmit the maximum efficiency between the transmitter and the receiver for the MRC WPT system [10]. The transmission efficiency will drop quickly when the receiving coil is shifted away from its optimal distance [11,12]. MRC WPT acquires advantages compared to the Inductive Coupling (IC) WPT due to its reliability for medium-distance applications and high efficiency [13][14][15]. ...
Wireless Power Transfer in the 5G frequency band is the most promising technology to power up ubiquitous small electronic devices as well as IoT devices. A strongly coupled magnetic resonance WPT technique that focuses on near-field electromagnetic energy has been proposed in this paper. However, most Magnetic Resonance Coupling Wireless Power Transfer (MRC WPT) applications have been designed in kHz and MHz frequency spectrum. This paper demonstrates Planar Spiral Coil Magnetic Resonance Coupling (PSC MRC) WPT designs at 5G (GHz) frequencies. Also, the transformation technique of the low frequency (kHz and MHz) magnetic resonance circuit model equations to high frequency (GHz) circuit model equations to achieve a high-efficiency power transfer. PSC MRC WPT designs structure antennas are designed at 3.4 - 3.5 GHz in the form of circular and square shapes with 1 turn coil. The proposed antenna structures are firstly being optimized in a full-wave electromagnetic simulator, CST Microwave Studio to resonate at the 3.4 - 3.5 GHz band. Then, the close-loop equations to determine the efficiency of 5G Magnetic Resonance Coupling Planar Spiral Coil Wireless Power Transfer is designed. Lastly, the results are compared with the simulation and calculated parts. The highest efficiency of the PSC MRC circular antenna is 31.58 % when the distance is at 2 mm, and 31.26 and 31.02 % when the distance is at 3 and 4 mm, respectively. The efficiency of circular PSC MRC is found to be 25 % better than the efficiency of square shape design. HIGHLIGHTS IoT devices need to be charged and maintained as the network system has massive numbers of sensors. Wireless power transfer is a promising technology to power up IoT devices This paper proposed, a WPT technique based on strongly coupled magnetic resonance which focuses on the near-field electromagnetic energy. This technique can extend the distance of the power transfer between the transmitter and the receiver The transformation technique of the low frequency (kHz and MHz) magnetic resonance circuit model equations to high frequency (GHz) circuit model equations to achieve a high-efficiency PSC MRC WPT design structure is introduced in this paper This novel technique can be applied to effectively design PSC MRC Antenna WPT for 5G applications. Most reported Magnetic Resonance Coupling Wireless Power Transfer (MRC WPT) applications have been designed in kHz and MHz frequency spectrum GRAPHICAL ABSTRACT
... The bene ts of using a resonant 3-antenna system, with passive resonator co-located on the implanted device, over the conventional 2-antenna system are coupling enhancement, better misalignment insensitivity and better bandwidth 32,33 . Figure 2b and Supplementary Fig. 4a and 4b illustrate the simulated B-eld of the 3-antenna system, in which the receiver antenna and the resonator are co-located on the top and bottom side of the implant. ...
... The geometric parameters of the implant antenna (i.e., the width, the gap between adjacent turns, the dimension and shape of the antennas) are chosen to optimize transmission e ciency at 13.56 MHz ( Supplementary Fig. 5a,b) while minimizing the size of the implant. Adding a resonator improves the coupling between the transmitter and receiver as shown in simulations (Supplementary Fig. 6a) [33][34][35][36] . A comparison between the transmission e ciency of the 3-antenna WPT and the conventional 2-antenna WPT shows that adding the resonator antenna increases the transmission e ciency from 12-37% ( Supplementary Fig. 6b). ...
Electrical stimulation of the neuromuscular system holds promise for both scientific and therapeutic biomedical applications. Supplying and maintaining the power necessary to drive stimulation chronically is a fundamental challenge in these applications, especially when high voltages or currents are required. Wireless systems, in which energy is supplied through near field power transfer, could eliminate complications caused by battery packs or external connections, but currently do not provide the harvested power and the voltages for applications such as muscle stimulation. Here, we introduce a passive resonator optimized power transfer design that overcomes these limitations, enabling voltage compliances of ± 20 V and power over 300 mW at device volumes of 0.2 cm ² , thereby improving power transfer 500% over previous systems. This improved performance enables multichannel, biphasic, current-controlled operation at clinically relevant voltage and current ranges with digital control and telemetry. Implanted devices remain operational over 6 weeks in both intact and spinal cord injured rats and are capable of producing fine control of spinal and muscle stimulation.
... Thus, the maximal achievable power transfer efficiency (PTE) was very low in these systems [7]- [10]. The PTE of the WPT system was dependent on the structure and dimension of the coils, physical spacing between both the coils, environment and relative location of the different coils [11]. In [12] the researchers designed the 2 coils using the inductive coupling system, wherein the receiver coil was designed as a 38 mm-long helical stent when the PTE was ≥0.03. ...
In this study, the researchers have proposed an alternative technique for designing an asymmetric 4 coil-resonance coupling module based on the series-to-parallel topology at 27 MHz industrial scientific medical (ISM) band to avoid the tissue damage, for the constant monitoring of the in-stent restenosis coronary artery. This design consisted of 2 components, i.e., the external part that included 3 planar coils that were placed outside the body and an internal helical coil (stent) that was implanted into the coronary artery in the human tissue. This technique considered the output power and the transfer efficiency of the overall system, coil geometry like the number of coils per turn, and coil size. The results indicated that this design showed an 82% efficiency in the air if the transmission distance was maintained as 20 mm, which allowed the wireless power supply system to monitor the pressure within the coronary artery when the implanted load resistance was 400 Ω.
