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Try out PMC Labs and tell us what you think. Learn More. The optimization, manufacturing, and performance characterization of a miniaturized 3D receiver RX -based wireless power transfer WPT system fed by a multi-transmitter multi-TX array is presented in this study for applications in capsule endoscopy CE.

The 8. The multi-TX is activated using a custom-made high-efficiency dual class-E power amplifier operated in subnominal condition. The maximum variation in temperature was also measured as 1. Capsule endoscopes CEs are increasingly used for patients suffering from gastrointestinal GI disorders, as the relatively painless procedure allows early stage detection and diagnosis.

Since the introduction of the first capsule in the late s [ 1 ], increasingly complex systems have been proposed by the scientific community to achieve high-quality diagnostic yields. Subelements for these capsules range from electromechanical actuators for biopsy [ 2 , 3 ], nonwhite-light imaging sensors [ 4 , 5 ], actuators for locomotion [ 6 ], to electronic systems [ 7 ].

However, the lack of available small size batteries with sufficient capacity for continuous operation prevent their integration into todays CE [ 8 , 9 ].

Therefore, the most promising present alternative is the wireless power transfer WPT to the capsule from an external transmitter TX [ 10 , 11 ]. WPT technology has established itself as a promising candidate for complex medical implantable devices MIDs , such as neurostimulators, pacemakers, or retinal implants [ 12 , 13 , 14 ]. Unlike fixed MIDs, endoscopic capsules travel through the gastrointestinal track. Therefore, it is essential to design a method whereby power can be satisfactorily delivered to the capsule irrespective of its location and position with respect to the TX.

Moreover, the volume of a typical capsule—11 mm outer diameter by 26 mm length [ 15 ]—places severe constraints on the size of the embedded receiver RX , leading to a low power transfer efficiency PTE for the resulting system.

Different misalignment insensitive RX coils configurations have been reported in the literature for an extensive range of WPT applications. In research of Jonah et al. Furthermore, the high operation frequencies of the proposed systems could cause significant tissue heating for long durations of continuous operation as encountered in CE, requiring therefore experimental validation regarding human tissue safety.

At In addition, the proposed 3D RX is significantly 1. In research of Lenaerts et al. The specific absorption rate SAR recorded is 0. In publication of Zhiwei et al. A omnidirectional miniaturized RX coil analogous to that in research of Jonah et al. Compared to previously published studies, the proposed architecture offers a miniaturized 3D RX of 8. The SAR of 0. A 3D type RX is therefore proposed in this study to satisfy the requirements of tolerance to capsule misalignment, small size, moderate heat dissipation, and satisfactory PTE.

The 3D RX coil is fully investigated using a set of analytical expressions and optimized via a nested multidimensional optimization algorithm presented in research of Khan et al. Figure 1 shows the proposed 3D RX coils system with and without copper wires. The diameter and thickness of the holder are 8. Each coil, of wire diameter w , is assumed to have N l loops and N t layers. The second term of Equation 1 refers to the case of different loops in the same layer, whereas, in the third term, R k is the radius of a loop in different perfectly aligned layers.

In Equation 1 , the complete elliptic integrals of the first and second kind are presented as K and E , respectively. The coils are assumed to be wound as Archimedean spirals [ 25 ]. Considering the ferrite effect L self is rewritten as [ 24 ]:. D c is defined as [ 24 ]:. Furthermore, the frequency of operation, f , was selected as 1 MHz. This frequency was chosen for tissue safety, it also offers cheaper electronic circuitry compared the ISM band of 6.

The mutual inductance, M , of two current carrying loops, defined as C1 and C2 of respective radii R C 1 and R C 2 is proposed in research of Khan et al. Furthermore, d r i,j is defined as [ 25 ]:. Wire diameter and spacing between loops of a coil C i are defined as w Ci and s t,Ci , respectively.

The AC resistance, R AC , is the addition of skin and proximity effect resistors, R skin and R prox , respectively, and can be written as [ 28 ]:. R skin can be asymptotically represented as [ 29 ]:. In addition, R prox , is defined as [ 30 , 31 ]:. The simplified closed form alternative current AC resistance with the effect of ferrite on the copper wire in the 3D RX is provided in publication of Theilmann et al.

The parasitic capacitance influence analysis of the copper wire and PSC are explained in research of Yang et al. The TX coils are externally powered with the driving sources F 1 t and F 2 t. In this case, only the z -axis of the 3D RX coil is considered. The RX coil output is associated with the load resistance, R L.

The multi-TX system can be illustrated by using the coupled-mode theory as [ 34 , 35 ]:. L RX is the inductance of the coils. The distance dependent figure of merit FOMD is defined as:. A nested multi-dimensional optimization algorithm presented in research of Khan et al. This algorithm extracts coil parameters such as wire width and number of turns to achieve maximum WL-PTE.

The optimized coil parameters of TX and 3D RX are listed in Table 1 , where s and N are the spacing between two copper wires and total number of turns, respectively. The outer diameter of the coil holder without the ferrite, Figure 5 a, is 8.

The outer diameter and thickness of the proposed 3D RX and its copper wire winding were 8. Manufactured coil holders. The complete experimental setup with the multi-TX coils and 18 cm diameter spherical phantom is presented in Figure 6. The TX coils were placed 1 cm away from the outer surface of the phantom globe, resulting in a total distance of 20 cm between the RX.

The phantom with similar electrical properties as human muscle tissue was prepared using hydrophilic organic powder and degassed water [ 7 ]. A RX circuit test bench with variable capacitors to adjust resonant conditions of the RX coils and optimize load resistors was used to measure the total WL-PTE as defined in Equation The Schottky diode-based bridge rectifier for each RX coil was also embedded in the RX circuit to measure the complete system efficiency.

PTE was measured using a Keysight technologies current probe B and oscilloscope. Temperature variation inside the phantom globe was measured by a Microcontroller Arduino Nano 3. Figure 7 shows the cross-section of the phantom globe, which is made of two identical hemispheres filled with the phantom tissues described above. The 3D RX coil was mounted at the center, and five temperature sensors TSs were inserted approximately equidistantly around the RX coil.

A sixth thermistor, TS6, was placed outside the phantom to measure room temperature. Variations in frequency of the theoretical, simulated, and measured values of the Q-factors for TX and RX coils are presented in Figure 8 and Figure 9 , respectively. Excellent agreement was recorded between calculated, simulated, and measured values for both figures. The highest Q -factor was achieved at around 1 MHz. PTEs for both single and multi-TX coils are recorded in air and phantom.

In contrast, the multi-TX coils demonstrate promising PTE in the 5—15 cm distance, which is the location of the GI tract in an average human body. Increased PTE at 1. No significant difference was observed in air or in the phantom due to the low absorption of the phantom tissue at 1 MHz.

However, the SAR was recorded at 1. Temperature rise inside the tissue was also measured in the phantom using multiple TSs for a typical capsule transit time of hour inside the GI tract, shown as Figure The maximum temperature variation in the body TS5 was 1.

Temperature rise measurement in and around the capsule should also account for the additional temperature rise generated by the electronic processing inside the capsule to implement the requested sensing modalities as reported in research of Faerber et al.

Results are presented in Table 2. In research of Zhiwei et al. The WPT systems presented in research of Na et al. In this study, the proposed 3D RX coil is, however, smaller in size compared to previous works and offers therefore more space for other electronic processing circuitry or sensing modalities. However, PTE is lower compared to some previous works.

The complete WPT system with its electronic processing is presented in Figure 16 , alongside analysis of the complete system efficiency CSE. It is necessary to use same signal generator for both the TX coils to maintain the excitation with signals having the same phase.

Phase variation would otherwise reduce drastically the PTE of the proposed system. The closed-form equations of the subnominal model presented in research of Liu et al.

Three full wave bridge rectifiers built with the Schottky diode DB2SL and surface mount package of dimensions 1. For a total input power of 10 W, i. The proposed system can supply approximately 50 mW of power inside the phantom in the worst cases of angular and translational misalignment. It is possible to increase the output power of the proposed system by improving the efficiency of the class-E amplifier.

In research of Liu et al. This can lead to an output power of 75 mW for the proposed WPT system in this paper. It should be possible to improve the CSE to 0. Furthermore, the utilization of the modern 3D printing technology can lead to a more methodological manufacturing technique for the miniaturized 3D RX coil. The proposed 8. The measured results demonstrate promising PTE at larger separation distance and complete capsule rotation inside phantom.

Implementing the TX coils using flexible substrate facilitates easy mounting of the transmitter and portability.


Towards a Miniaturized 3D Receiver WPT System for Capsule Endoscopy

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3d receiver effects

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Try out PMC Labs and tell us what you think. Learn More. The optimization, manufacturing, and performance characterization of a miniaturized 3D receiver RX -based wireless power transfer WPT system fed by a multi-transmitter multi-TX array is presented in this study for applications in capsule endoscopy CE. The 8.




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