Intermediate Range Wireless Power Transfer with Segmented … · 2016. 6. 30. · range wireless energy transfer can significantly reduce the transmitter voltage to a safe level (~10

0885-8993 (c) 2016 IEEE. Personal use is permitted, but republication/redistribution requires IEEE permission. See http://www.ieee.org/publications_standards/publications/rights/index.html for more information.

This article has been accepted for publication in a future issue of this journal, but has not been fully edited. Content may change prior to final publication. Citation information: DOI 10.1109/TPEL.2016.2584558, IEEETransactions on Power Electronics

TPEL-Reg-2016-02-0400.R1 9

[35] International Commission on Non-Ionizing Radiation Protection, “Guidelines for limiting exposure to time-varying electric, magnetic, and electromagnetic fields (up to 300 GHz),” Health Physics, Vol. 74, No. 4, 1998, pp. 494-522.

[36] S. Nebuya, G. H. Mills, P. Milnes, and B. H. Brown, “Indirect measurement of lung density and air volume from electrical impedance tomography (EIT) data,” Physiological Measurement, Vol. 32, No. 12, December 2011, pp.1953-1967.

[37] http://physics.nist.gov/PhysRefData/XrayMassCoef/tab2.html [38] R. Bartlett, C. Gratton, and C. G. Rolf, Encyclopedia of International

Sports Studies, Routledge, p. 164, 2009. [39] R Kramer, H. J. Khoury, J. W. Vieira, E. C. M. Loureiro, V. J. M. Lima,

F. R. A. Lima, and G. Hoff, “All about FAX a Female Adult voXel phantom for Monte Carlo calculation in radiation protection dosimetry”, Physics in Medicine and Biology, Vol. 49, No. 23, December 2004, pp. 5203-5216.

Sai Chun Tang (S’97–M’01–SM’11) was born in Hong Kong in 1972. He received the B.Eng. degree (with First Class Honours) and the Ph.D. degree in electronic engineering from the City University of Hong Kong in 1997 and 2000, respectively, where he was a Research Fellow after he graduated. He joined the National University of Ireland,

Galway, as a Visiting Academic in 2001, and then the Laboratory for Electromagnetic and Electronic Systems at the Massachusetts Institute of Technology, Cambridge, in 2002. Since 2004, he has been with the Radiology Department, Brigham and Women’s Hospital, Harvard Medical School, Boston, MA, for the developments of ultrasound diagnosis devices and noninvasive treatment systems using high-intensity focused ultrasound. In 2008, he became a Faculty in Radiology at Harvard Medical School. His current research interests include wireless power transfer, electronic medical devices, high-frequency electromagnetism, low-profile power converter design, and analog electronics.

Nathan McDannold is the Research Director of the Focused Ultrasound Laboratory at The Brigham and Women’s Hospital and an Associate Professor in Radiology at Harvard Medical School. He received his B.S. in Physics in 1995 from the University of Virginia, Charlottesville and a Ph.D. in Physics in 2001 from Tufts University in Boston, MA His work has been primarily concerned with the

development and implementation of MRI-based thermometry methods, animal experiments testing MRI and ultrasound related work, and clinical focused ultrasound treatments of breast tumors, uterine fibroids, and brain tumors. In recent years, a main focus of his work has been studying the use of ultrasound for temporary disruption of the blood-brain barrier, which may allow for targeted drug delivery in the brain.

Fig. 1. Dimensions of Coil 1.

yz

13 mm

50 mm

2 mm 0.5 mm

x

‐10

0

10

20

30

40

50

60

70

80

0 2 4 6 8 10 12 14 16 18 20

|Hz| (A

/m)

x (cm)

H‐Field of the 5‐cm coil vs. x at z=2cm

0

50

100

150

200

250

300

350

400

0 2 4 6 8 10 12 14 16 18 20

|Hz| (A

/m)

z (cm)

H‐Field of the 5‐cm coil along the z‐axis

—— Equation (1) ● FEA

Fig. 2. Hz generated by the 5-cm energy transmitting coil (a) along the z-axis,and (b) versus x at y = 0, and z = 2 cm.

(a)

(b)




TPEL-Reg-2016-02-0400.R1 10

Fig. 3. Dimensions of Coils 2 – 5 for transmitting energy.

Coil 2 Coil 3

Coil 4 Coil 5

119 mm 300 mm

219 mm 300 mm

279 mm

300 mm

299 mm

300 mm

0.5 mm 10 mm 0.5 mm 10 mm

0.5 mm 10 mm 0.5 mm

y

z x

y

z x

y

z x

y

z x

Fig. 5. A 3-D drawing of the proposed transmitting coil.

x y

z

240 mm

300 mm

70 mm

1.2 mm

2 mm

‐202468

101214161820

0 2 4 6 8 10 12 14 16 18 20

|Hz| (A

/m)

x (cm)

H‐Field of the 30‐cm coils vs. x at z=10cm

0

10

20

30

40

50

60

0 2 4 6 8 10 12 14 16 18 20

|Hz| (A

/m)

z (cm)

H‐Field of the 30‐cm coils along the z‐axis

Fig. 4. H-field generated by the 30-cm energy transmitting coils (a) alongthe z-axis, and (b) versus x at z = 10 cm when the excitation is 10 A-turn.

Coil 5

(a)

(b)

Coil 4 Coil 3

Coil 2

Coil 5

Coil 4Coil 3

Coil 2





TPEL-Reg-2016-02-0400.R1 11

-90

-60

-30

0

30

60

90

0.0

0.1

0.2

0.3

0.4

0.5

0.6

0.7

0.8

6.760 6.765 6.770 6.775 6.780 6.785 6.790 6.795 6.800

Phas

e (D

egre

e)

|Z| (

)

Frequency (MHz)

Z vs. Frequency

Fig. 9. Measured impedance magnitude and phase of the segmentedtransmitting coil tuned to 6.78 MHz.

Fig. 8. A circuit schematic for the segmented proposed coil.

Resonantcapacitors

0.0

0.2

0.4

0.6

0.8

1.0

1.2

1.4

1.6

1.8

2.0

2.0

2.2

2.4

2.6

2.8

3.0

3.2

3.4

3.6

3.8

4.0

0 1 2 3 4 5 6 7 8 9 10

Res

ista

nce

()

Indu

ctan

ce (

H)

Frequency (MHz)

Ls-Rs vs. Frequency

Fig. 7. Measured inductance and resistance of the proposed transmittingcoil.

0.0

0.5

1.0

1.5

2.0

2.5

3.0

3.5

4.0

‐7 ‐6 ‐5 ‐4 ‐3 ‐2 ‐1 0 1 2 3 4 5 6 7

|Hz| (A

/m)

y (cm)

Magnetic Field Intensity vs. y

0.0

0.5

1.0

1.5

2.0

2.5

3.0

3.5

4.0

‐7 ‐6 ‐5 ‐4 ‐3 ‐2 ‐1 0 1 2 3 4 5 6 7

|Hz| (A

/m)

x (cm)

Magnetic Field Intensity vs. x

0

1

2

3

4

5

6

7

8

0 2 4 6 8 10 12 14 16

|Hz| (A

/m)

z (cm)

Magnetic Field Intensity vs. z

Fig. 6. Simulated and measured Hz along the (a) z-axis, (b) x-axis at z =10.7 cm, and (c) y-axis at z = 10.7 cm of the proposed transmitting coil.

(a)

(b)

(c)

—— FEA ● Measurement





TPEL-Reg-2016-02-0400.R1 12

0

2

4

6

8

10

‐7 ‐6 ‐5 ‐4 ‐3 ‐2 ‐1 0 1 2 3 4 5 6 7

Lm (n

H)

y (cm)

Mutual Inductance versus y

Fig. 15. Measured mutual inductance between the transmitting andreceiving coils versus y when x = 0.

z = 10.7 cm

z = 7.7 cm

0

2

4

6

8

10

‐7 ‐6 ‐5 ‐4 ‐3 ‐2 ‐1 0 1 2 3 4 5 6 7

Lm (n

H)

x (cm)

Mutual Inductance versus x

Fig. 14. Measured mutual inductance between the transmitting andreceiving coils versus x when y = 0.

z = 10.7 cm

z = 7.7 cm

Fig. 13. Measured mutual inductance between the transmitting andreceiving coils along the z-axis.

0

2

4

6

8

10

12

14

0 2 4 6 8 10 12 14 16 18

Lm (n

H)

z (cm)

Mutual Inductance along the z‐axis

Fig. 12. Measured receiver output voltage normalized to the transmittingcoil excitation current versus frequency under no-load and 50.5 loadconditions when x = y = 0 and, z = 7.7cm.

0

10

20

30

40

50

60

6.60 6.65 6.70 6.75 6.80 6.85 6.90 6.95 7.00

V Out(V)

Frequency (MHz)

Output Voltage Normalized to the Excitation Current

No load

50.5 load

22 kHz

78 kHz

Fig. 11 . Equivalent circuit model of the coupling circuit.

Rt

Lt

Lm

Ct

C1

C2

C3

Rr

Lr RL

Receiving coil

Transmittingcoil

R1

R2

R3

It

VOut

Fig. 10. A 3-D drawing of the energy receiving coil.

x z

y

1.2 mm

1.624 mm

1.624 mm

53 mm



TPEL-Reg-2016-02-0400.R1 13

Fig. 21. Measured waveforms of the transmitting coil voltage, VTx, current ITx, and output voltage, VOut when Pout = 48.2 W when the receiving coil is located at x = y =0, and z = 7.7 cm.

0 50 100 150 200 250 300 350 400 450 500-20-10

01020

Transmitting Coil Voltage

VT

x (V

)

0 50 100 150 200 250 300 350 400 450 500-10-505

10Transmitting Coil Current

I Tx

(A)

0 50 100 150 200 250 300 350 400 450 500-50-25

02550

Output Voltage

v Out

(V

)

Time (ns)

0%

10%

20%

30%

40%

50%

60%

70%

80%

90%

100%

0

5

10

15

20

25

30

35

40

45

50

0 1 2 3 4 5 6

Efficiency

Outpu

t Pow

er (W

)

Transmitting Coil Current (A)

Output Power and Efficiency Vs. Input Current

Fig. 20. Calculated and measured output power and efficiency versustransmitting coil current when x = y = 0, z = 7.7 cm (thick lines) and 10.7cm (thin lines), and RL = 16.8 .

—— Calculation ● Measurement

0%

10%

20%

30%

40%

50%

60%

70%

80%

90%

100%

0.0

0.2

0.4

0.6

0.8

1.0

1.2

1.4

1.6

1.8

2.0

‐7 ‐6 ‐5 ‐4 ‐3 ‐2 ‐1 0 1 2 3 4 5 6 7

Efficiency

Outpu

t Pow

er (W

)

y (cm)

Output Power and Efficiency versus y

Fig. 19. Calculated and measured output power and efficiency versus ywhen x = 0, z = 7.7 cm (thick lines) and 10.7 cm (thin lines), and It =1 Armsand RL = 16.


0%

20%

40%

60%

80%

100%

0.0

0.2

0.4

0.6

0.8

1.0

1.2

1.4

1.6

1.8

2.0

‐7 ‐6 ‐5 ‐4 ‐3 ‐2 ‐1 0 1 2 3 4 5 6 7

Efficiency

Outpu

t Pow

er (W

)

x (cm)

Output Power and Efficiency versus x

Fig. 18. Calculated and measured output power and efficiency versus xwhen y = 0, z = 7.7 cm (thick lines) and 10.7 cm (thin lines), and It =1 Armsand RL = 16.


0%

10%

20%

30%

40%

50%

60%

70%

80%

90%

100%

0.0

0.5

1.0

1.5

2.0

2.5

3.0

3.5

4.0

4.5

5.0

0 1 2 3 4 5 6 7 8 9 10 11 12 13 14 15 16 17

Efficiency

Outpu

t Pow

er (W

)

z(cm)

Output Power and Efficiency versus z

Fig. 17. Calculated and measured output power and efficiency along the z-axis when It =1 Arms and RL = 16.


0%

10%

20%

30%

40%

50%

60%

70%

80%

90%

100%

0

1

2

3

4

5

6

0 20 40 60 80 100 120 140 160 180 200

Efficiency

Outpu

t Pow

er (W

)

Load resistance ()

Load Power and Efficiency Vs. Load resistance

Fig. 16. Calculated and measured output power and efficiency versus loadresistance at x = y = 0, z = 7.7 cm and It = 1 Arms.




TPEL-Reg-2016-02-0400.R1 14

Fig. 24. Measured waveforms of the transmitting coil voltage, VTx, and current ITx, when the receiver is loaded with a 24-V DC pump and a parallel 152 resistor.

0 50 100 150 200 250 300 350 400 450 500-20

-10

0

10

20Transmitting Coil Voltage

VT

x (V

)

0 50 100 150 200 250 300 350 400 450 500-10

-5

0

5

10Transmitting Coil Current

I Tx

(A)

Fig. 23. Energy coupling circuit for the circulatory model.

Lt

Lm

Ct

C1

C2

C3

Lr

D1 D2

D3 D4

CfRL

Receiving coil

Transmittingcoil DC pump

Fig. 22. Front and side views of the wirelessly powered circulatory model.

Side View Front View

DC pump

Heart-shaped water reservoir

Transmitting coil

Receiving Coil

Receiving coil

Rectifier

Additional load, RL

Segment Capacitors

10 cm



TPEL-Reg-2016-02-0400.R1 15

Fig. 26. Simulated SAR of the body model on the (a) y-z plane at x = 0 and(b) x-z plane at y = 145 mm when the transmitting coil current is 4.89 Arms.

SAR (Wkg‐1)

(b)

(a)

SAR (Wkg‐1)Z (mm)

Y (

mm

)

50100150200250300-200

-150

-100

-50

0

50

100

150

200

0

0.2

0.4

0.6

0.8

1

1.2

1.4

1.6

1.8

2

Z (mm)

X (

mm

)

50100150200250300

-150

-100

-50

0

50

100

150 0

0.2

0.4

0.6

0.8

1

1.2

1.4

1.6

1.8

2

Fig. 25. (a) A 3-D view and (b) top-view of a FEA simulation model for theevaluation of SAR in human tissues when the proposed coil is used.

(a)

Transmitting CoilBody model

y

z

x

400 mm

112 mm 120 mm 135 mm 145 mm 150 mm

20 mm 30 mm

16 mm

Rib Muscle Fat

Skin

Spine

Lung

Bloodvessels

22 mm

x

z

(b)

Coil



TPEL-Reg-2016-02-0400.R1 16

Fig. A.1 . Receiving circuit.

jLmIt

C1

C2

C3

Rr

Lr

Receiving coil

R1

R2

R3 VOut ZCr

0

1

2

3

4

0 1 2 3 4 5 6

Localized

SAR

(W/kg)

Transmitting Coil Current (A)

SAR vs. Transmitting Coil Current

Fig. 27. Simulated maximum localized SAR of 10g contiguous tissue of thebody model versus transmitting coil current with different coil-skinseparation from 10 to 30 mm.

10 mm

15 mm16 mm

20 mm 25 mm

27 mm30 mm

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Intermediate Range Wireless Power Transfer with Segmented … · 2016. 6. 30. · range wireless energy transfer can significantly reduce the transmitter voltage to a safe level (~10