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完整後設資料紀錄
DC 欄位 | 值 | 語言 |
---|---|---|
dc.contributor.advisor | 陳志宏(Jyh-Honrg Chen) | |
dc.contributor.author | In-Tsang Lin | en |
dc.contributor.author | 林胤藏 | zh_TW |
dc.date.accessioned | 2021-06-15T01:32:09Z | - |
dc.date.available | 2016-08-20 | |
dc.date.copyright | 2011-08-20 | |
dc.date.issued | 2011 | |
dc.date.submitted | 2011-08-16 | |
dc.identifier.citation | [1] P. Haldar and P. Abetti, 'Absolute zero, as the name suggests, is as cold as it gets,' Spectrum, IEEE, vol. 48, pp. 50-60, 2011.
[2] P. C. Lauterbur, 'Image formation by induced local interactions: examples employing nuclear magnetic resonance,' Nature, vol. 242, pp. 190-191, 1973. [3] P. Mansfield and P. Grannell, 'NMR'diffraction'in solids?,' Journal of Physics C: solid state physics, vol. 6, p. L422, 1973. [4] B. Beck, D. Plant, S. Grant, P. Thelwall, X. Silver, T. Mareci, H. Benveniste, M. Smith, C. Collins, and S. Crozier, 'Progress in high field MRI at the University of Florida,' Magnetic Resonance Materials in Physics, Biology and Medicine, vol. 13, pp. 152-157, 2001. [5] D. Hoult and R. Richards, 'The signal-to-noise ratio of the nuclear magnetic resonance experiment,' J Magn Reson, vol. 24, pp. 71-85, 1976. [6] A. Wright, H. Song, and F. Wehrli, 'In vivo MR micro imaging with conventional radiofrequency coils cooled to 77 K,' Magnetic Resonance in Medicine, vol. 43, pp. 163-169, 2000. [7] M. Cheng, B. Yan, K. Lee, Q. Ma, and E. Yang, 'A high temperature superconductor tape RF receiver coil for a low field magnetic resonance imaging system,' Superconductor Science and Technology, vol. 18, pp. 1100-1105, 2005. [8] D. Gadian and F. Robinson, 'Radiofrequency losses in NMR experiments on electrically conducting samples,' J Magn Reson, vol. 34, pp. 449-455, 1979. [9] J. C. Ginefri, L. Darrasse, and P. Crozat, 'High temperature superconducting surface coil for in vivo microimaging of the human skin,' Magnetic Resonance in Medicine, vol. 45, pp. 376-382, 2001. [10] J. Wosik, L. Xie, K. Nesteruk, L. Xue, J. Bankson, and J. Hazle, 'Superconducting single and phased-array probes for clinical and research MRI,' IEEE Transactions on Applied Superconductivity, vol. 13, pp. 1050-1055, 2003. [11] R. Black, T. Early, P. Roemer, O. Mueller, A. Mogro-Campero, L. Turner, and G. Johnson, 'A high-temperature superconducting receiver for nuclear magnetic resonance microscopy,' Science, vol. 259, pp. 793-795, 1993. [12] R. Ludwig and P. Bretchko, RF circuit design vol. 57: Prentice Hall, 2000. [13] Z. Y. Shen, High-temperature superconducting microwave circuits: Artech House, 1994. [14] J. Yuan and G. Shen, 'Quality factor of Bi (2223) high-temperature superconductor tape coils at radio frequency,' Superconductor Science and Technology, vol. 17, pp. 333-336, 2004. [15] G. Grasso, A. Malagoli, N. Scati, P. Guasconi, S. Roncallo, and A. Siri, 'Radio frequency response of Ag-sheathed (Bi, Pb) 2Sr2Ca2Cu3O10+ x superconducting tapes,' Superconductor Science and Technology, vol. 13, pp. L15-L18, 2000. [16] S. J. Penn, M. N. Alford, D. Bracanovic, A. A. Esmail, V. Scott, and T. W. Button, 'Thick film YBCO receive coils for very low field MRI,' Applied Superconductivity, IEEE Transactions on, vol. 9, pp. 3070-3073, 1999. [17] J. Ginefri, E. Durand, and L. Darrasse, 'Quick measurement of nuclear magnetic resonance coil sensitivity with a single-loop probe,' Review of Scientific Instruments, vol. 70, p. 4730, 1999. [18] H. Zhang, Q. Li, J. Zong, and N. Dong, 'Development of low thermal conductivity Ag-Au alloy sheath Bi-2223 tape and design of a 20 kA HTS current lead,' Physica C: Superconductivity, vol. 412, pp. 1217-1220, 2004. [19] H. Yi, Z. Han, J. Zhang, T. Liu, L. Liu, M. Li, J. Fang, Q. Liu, and Y. Zheng, 'Research status of the manufacturing technology and application properties of Bi-2223/Ag tapes at Innost,' Physica C: Superconductivity, vol. 412, pp. 1073-1078, 2004. [20] T. Van Duzer and C. W. Turner, Principles of superconductive devices and circuits: Prentice Hall PTR Upper Saddle River, NJ, USA, 1998. [21] H. Xu, Thin film high temperature superconducting radio frequency resonators and filters, and their applications: Columbia University, 2001. [22] W. Hayt Jr, 'JA Buck, Engineering Electromagnetics,' ed: McGraw-Hill Higher Education, New York, 2001. [23] H. Lee, I. Lin, J. Chen, H. Horng, and H. Yang, 'High-Tc superconducting receiving coils for nuclear magnetic resonance imaging,' IEEE Trans Appl Superconductivity, vol. 15, pp. 1326-1329, 2005. [24] P. L. Kuhns, M. J. Lizak, S. H. Lee, and M. S. Conradi, 'Inductive coupling and tuning in NMR probes; applications,' Journal of Magnetic Resonance (1969), vol. 78, pp. 69-76, 1988. [25] D. Hoult and B. Tomanek, 'Use of mutually inductive coupling in probe design,' Concepts in Magnetic Resonance, vol. 15, pp. 262-285, 2002. [26] W. R. Smyte, Static and dynamic electricity: McGraw-Hill, 1968. [27] H. Okada, T. Hasegawa, J. Vanheteren, and L. Kaufman, 'RF coil for low-field MRI coated with high-temperature superconductor,' Journal of Magnetic Resonance, Series B, vol. 107, pp. 158-164, 1995. [28] C. Chen and D. I. Hoult, Biomedical magnetic resonance technology: A. Hilger, 1989. [29] Q. Y. Ma, K. C. Chan, D. F. Kacher, E. Gao, M. S. Chow, K. K. Wong, H. Xu, E. S. Yang, G. S. Young, J. R. Miller, and F. A. Jolesz, 'Superconducting RF coils for clinical MR imaging at low field,' Acad Radiol, vol. 10, pp. 978-87, Sep 2003. [30] W. Chunli, B. Zhiming, X. Jingkui, and W. Jinxing, 'Simulation analysis on quality factor of RF receiving coil for an MRI system,' 2009, pp. 4652-4655. [31] S. Yamazaki, H. Nakane, and A. Tanaka, 'Basic analysis of a metal detector,' Instrumentation and Measurement, IEEE Transactions on, vol. 51, pp. 810-814, 2002. [32] W. Edelstein, G. Glover, C. Hardy, and R. Redington, 'The intrinsic signal to noise ratio in NMR imaging,' Magnetic resonance in medicine, vol. 3, pp. 604-618, 1986. [33] R. Black, T. Early, and G. Johnson, 'Performance of a high-temperature superconducting resonator for high-field imaging,' Journal of Magnetic Resonance, Series A, vol. 113, pp. 74-80, 1995. [34] Y. Kobayashi and M. Katoh, 'Microwave measurement of dielectric properties of low-loss materials by the dielectric rod resonator method,' Microwave Theory and Techniques, IEEE Transactions on, vol. 33, pp. 586-592, 1985. [35] P. Kaleeba, A. Tennant, and J. Ide, 'Modelling a planar phase switched structure (PSS) in Ansoft HFSS (high frequency structure simulator),' 2003, pp. 257-261 vol. 1. [36] D. Kajfez and E. Hwan, 'Q-factor measurement with network analyzer,' IEEE Transactions on microwave theory and techniques, vol. 32, pp. 666-670, 1984. [37] W. E. Kwok and Z. You, 'In vivo MRI using liquid nitrogen cooled phased array coil at 3.0 T,' Magnetic resonance imaging, vol. 24, pp. 819-823, 2006. [38] I. T. Lin, H. C. Yang, C. W. Hsieh, T. Jao, and J. H. Chen, 'Human hand imaging using a 20 cm high-temperature superconducting coil in a 3T magnetic resonance imaging system,' Journal of Applied Physics, vol. 107, pp. 124701-124701-6, 2010. [39] H. Yang, K. Tsai, J. Chen, C. Wu, H. Horng, J. Chen, and L. Kuo, 'High-Tc superconducting surface coils for improving the image quality on a 3 T imager,' Superconductor Science and Technology, vol. 20, pp. 777-780, 2007. [40] J. Wosik, L. Xue, L. M. Xie, M. Kamel, K. Nesteruk, and J. A. Bankson, 'Superconducting array for high-field magnetic resonance imaging,' Applied Physics Letters, vol. 91, pp. 183503-183503-3, 2007. [41] D. Jones, M. Catani, C. Pierpaoli, S. Reeves, S. Shergill, M. O'Sullivan, P. Golesworthy, P. McGuire, M. Horsfield, and A. Simmons, 'Age effects on diffusion tensor magnetic resonance imaging tractography measures of frontal cortex connections in schizophrenia,' Human brain mapping, vol. 27, pp. 230-238, 2006. [42] M. Kubicki, R. McCarley, C. Westin, H. Park, S. Maier, R. Kikinis, F. Jolesz, and M. Shenton, 'A review of diffusion tensor imaging studies in schizophrenia,' Journal of psychiatric research, vol. 41, pp. 15-30, 2007. [43] B. Chen and E. Hsu, 'Noise removal in magnetic resonance diffusion tensor imaging,' Magnetic Resonance in Medicine, vol. 54, pp. 393-401, 2005. [44] C. Lin, W. Tseng, H. Cheng, and J. Chen, 'Validation of diffusion tensor magnetic resonance axonal fiber imaging with registered manganese-enhanced optic tracts,' Neuroimage, vol. 14, pp. 1035-1047, 2001. [45] P. Basser, J. Mattiello, and D. LeBihan, 'MR diffusion tensor spectroscopy and imaging,' Biophysical Journal, vol. 66, pp. 259-267, 1994. [46] P. Basser, 'Inferring microstructural features and the physiological state of tissues from diffusion-weighted images,' NMR in Biomedicine, vol. 8, pp. 333-344, 1995. [47] L. Kuo, V. Wedeen, J. Weng, T. Reese, J. Chen, and W. Tseng, 'Reconstruction and visualization of white matter tracts based on clinical diffusion spectrum imaging,' 2005. [48] J. Miller, S. Hurlston, Q. Ma, D. Face, D. Kountz, J. MacFall, L. Hedlund, and G. Johnson, 'Performance of a high-temperature superconducting probe for in vivo microscopy at 2.0 T,' Magnetic Resonance in Medicine, vol. 41, 1999. [49] S. Hurlston, W. Brey, S. Suddarth, and G. Johnson, 'A high-temperature superconducting Helmholtz probe for microscopy at 9.4 T,' Magnetic Resonance in Medicine, vol. 41, pp. 1032-1038, 1999. [50] M. Cheng, B. Yan, K. Lee, Q. Ma, and E. Yang, 'A high temperature superconductor tape RF receiver coil for a low field magnetic resonance imaging system,' Superconductor Science and Technology, vol. 18, p. 1100, 2005. [51] F. E. Terman, Radio engineers' handbook vol. 2: McGraw-Hill, 1943. [52] K. Lee, M. Cheng, K. Chan, K. Wong, S. Yeung, K. Lee, Q. Ma, and E. Yang, 'Performance of large-size superconducting coil in 0.21 T MRI system,' Biomedical Engineering, IEEE Transactions on, vol. 51, pp. 2024-2030, 2004. [53] A. Hall, N. Alford, T. Button, D. Gilderdale, K. Gehring, and I. Young, 'Use of high temperature superconductor in a receiver coil for magnetic resonance imaging,' Magnetic Resonance in Medicine, vol. 20, pp. 340-343, 1991. [54] L. Darrasse and J. Ginefri, 'Perspectives with cryogenic RF probes in biomedical MRI,' Biochimie, vol. 85, pp. 915-937, 2003. [55] J. Nouls, M. Izenson, H. Greeley, and G. Johnson, 'Design of a superconducting volume coil for magnetic resonance microscopy of the mouse brain,' Journal of magnetic resonance, vol. 191, pp. 231-238, 2008. [56] I. J. Bahl, 'High-Q and low-loss matching network elements for RF and microwave circuits,' Microwave Magazine, IEEE, vol. 1, pp. 64-73, 2000. [57] J. Mispelter, M. Lupu, and A. Briguet, NMR probeheads for biophysical and biomedical experiments: theoretical principles & practical guidelines: Imperial College Pr, 2006. [58] M. K. Choy, K. K. Cheung, D. L. Thomas, D. G. Gadian, M. F. Lythgoe, and R. C. Scott, 'Quantitative MRI predicts status epilepticus-induced hippocampal injury in the lithium-pilocarpine rat model,' Epilepsy research, vol. 88, pp. 221-230, 2010. [59] I. T. Lin, H. C. Yang, and J. H. Chen, 'Using high-Tc superconducting resonator for enhancement of diffusion tensor imaging,' Journal of Applied Physics, vol. 109, p. 116103, 2011. [60] J. Folkman, K. Watson, D. Ingber, and D. Hanahan, 'Induction of angiogenesis during the transition from hyperplasia to neoplasia,' Nature, vol. 339, pp. 58-61, 1989. [61] J. Folkman, 'Tumor angiogenesis,' Advances in cancer research, vol. 43, pp. 175-203, 1985. [62] I. J. Fidler and L. M. Ellis, 'The implications of angiogenesis for the biology and therapy of cancer metastasis,' Cell, vol. 79, p. 185, 1994. [63] N. Weidner, 'Intratumor microvessel density as a prognostic factor in cancer,' The American journal of pathology, vol. 147, p. 9, 1995. [64] Y. Takahashi, Y. Kitadai, C. D. Bucana, K. R. Cleary, and L. M. 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Abetti, 'Absolute zero, as the name suggests, is as cold as it gets,' Spectrum, IEEE, vol. 48, pp. 50-60, 2011. [2] P. C. Lauterbur, 'Image formation by induced local interactions: examples employing nuclear magnetic resonance,' Nature, vol. 242, pp. 190-191, 1973. [3] P. Mansfield and P. Grannell, 'NMR'diffraction'in solids?,' Journal of Physics C: solid state physics, vol. 6, p. L422, 1973. [4] B. Beck, D. Plant, S. Grant, P. Thelwall, X. Silver, T. Mareci, H. Benveniste, M. Smith, C. Collins, and S. Crozier, 'Progress in high field MRI at the University of Florida,' Magnetic Resonance Materials in Physics, Biology and Medicine, vol. 13, pp. 152-157, 2001. [5] D. Hoult and R. Richards, 'The signal-to-noise ratio of the nuclear magnetic resonance experiment,' J Magn Reson, vol. 24, pp. 71-85, 1976. [6] A. Wright, H. Song, and F. Wehrli, 'In vivo MR micro imaging with conventional radiofrequency coils cooled to 77 K,' Magnetic Resonance in Medicine, vol. 43, pp. 163-169, 2000. [7] M. Cheng, B. Yan, K. Lee, Q. Ma, and E. Yang, 'A high temperature superconductor tape RF receiver coil for a low field magnetic resonance imaging system,' Superconductor Science and Technology, vol. 18, pp. 1100-1105, 2005. [8] D. Gadian and F. Robinson, 'Radiofrequency losses in NMR experiments on electrically conducting samples,' J Magn Reson, vol. 34, pp. 449-455, 1979. [9] J. C. Ginefri, L. Darrasse, and P. Crozat, 'High temperature superconducting surface coil for in vivo microimaging of the human skin,' Magnetic Resonance in Medicine, vol. 45, pp. 376-382, 2001. [10] J. Wosik, L. Xie, K. Nesteruk, L. Xue, J. Bankson, and J. Hazle, 'Superconducting single and phased-array probes for clinical and research MRI,' IEEE Transactions on Applied Superconductivity, vol. 13, pp. 1050-1055, 2003. [11] R. Black, T. Early, P. Roemer, O. Mueller, A. Mogro-Campero, L. Turner, and G. Johnson, 'A high-temperature superconducting receiver for nuclear magnetic resonance microscopy,' Science, vol. 259, pp. 793-795, 1993. [12] R. Ludwig and P. Bretchko, RF circuit design vol. 57: Prentice Hall, 2000. [13] Z. Y. Shen, High-temperature superconducting microwave circuits: Artech House, 1994. [14] J. Yuan and G. Shen, 'Quality factor of Bi (2223) high-temperature superconductor tape coils at radio frequency,' Superconductor Science and Technology, vol. 17, pp. 333-336, 2004. [15] G. Grasso, A. Malagoli, N. Scati, P. Guasconi, S. Roncallo, and A. Siri, 'Radio frequency response of Ag-sheathed (Bi, Pb) 2Sr2Ca2Cu3O10+ x superconducting tapes,' Superconductor Science and Technology, vol. 13, pp. L15-L18, 2000. [16] S. J. Penn, M. N. Alford, D. Bracanovic, A. A. Esmail, V. Scott, and T. W. Button, 'Thick film YBCO receive coils for very low field MRI,' Applied Superconductivity, IEEE Transactions on, vol. 9, pp. 3070-3073, 1999. [17] J. Ginefri, E. Durand, and L. Darrasse, 'Quick measurement of nuclear magnetic resonance coil sensitivity with a single-loop probe,' Review of Scientific Instruments, vol. 70, p. 4730, 1999. [18] H. Zhang, Q. Li, J. Zong, and N. Dong, 'Development of low thermal conductivity Ag-Au alloy sheath Bi-2223 tape and design of a 20 kA HTS current lead,' Physica C: Superconductivity, vol. 412, pp. 1217-1220, 2004. [19] H. Yi, Z. Han, J. Zhang, T. Liu, L. Liu, M. Li, J. Fang, Q. Liu, and Y. Zheng, 'Research status of the manufacturing technology and application properties of Bi-2223/Ag tapes at Innost,' Physica C: Superconductivity, vol. 412, pp. 1073-1078, 2004. [20] T. Van Duzer and C. W. Turner, Principles of superconductive devices and circuits: Prentice Hall PTR Upper Saddle River, NJ, USA, 1998. [21] H. Xu, Thin film high temperature superconducting radio frequency resonators and filters, and their applications: Columbia University, 2001. [22] W. Hayt Jr, 'JA Buck, Engineering Electromagnetics,' ed: McGraw-Hill Higher Education, New York, 2001. [23] H. Lee, I. Lin, J. Chen, H. Horng, and H. Yang, 'High-Tc superconducting receiving coils for nuclear magnetic resonance imaging,' IEEE Trans Appl Superconductivity, vol. 15, pp. 1326-1329, 2005. [24] P. L. Kuhns, M. J. Lizak, S. H. Lee, and M. S. Conradi, 'Inductive coupling and tuning in NMR probes; applications,' Journal of Magnetic Resonance (1969), vol. 78, pp. 69-76, 1988. [25] D. Hoult and B. Tomanek, 'Use of mutually inductive coupling in probe design,' Concepts in Magnetic Resonance, vol. 15, pp. 262-285, 2002. [26] W. R. Smyte, Static and dynamic electricity: McGraw-Hill, 1968. [27] H. Okada, T. Hasegawa, J. Vanheteren, and L. Kaufman, 'RF coil for low-field MRI coated with high-temperature superconductor,' Journal of Magnetic Resonance, Series B, vol. 107, pp. 158-164, 1995. [28] C. Chen and D. I. Hoult, Biomedical magnetic resonance technology: A. Hilger, 1989. [29] Q. Y. Ma, K. C. Chan, D. F. Kacher, E. Gao, M. S. Chow, K. K. Wong, H. Xu, E. S. Yang, G. S. Young, J. R. Miller, and F. A. Jolesz, 'Superconducting RF coils for clinical MR imaging at low field,' Acad Radiol, vol. 10, pp. 978-87, Sep 2003. [30] W. Chunli, B. Zhiming, X. Jingkui, and W. Jinxing, 'Simulation analysis on quality factor of RF receiving coil for an MRI system,' 2009, pp. 4652-4655. [31] S. Yamazaki, H. Nakane, and A. Tanaka, 'Basic analysis of a metal detector,' Instrumentation and Measurement, IEEE Transactions on, vol. 51, pp. 810-814, 2002. [32] W. Edelstein, G. Glover, C. Hardy, and R. Redington, 'The intrinsic signal to noise ratio in NMR imaging,' Magnetic resonance in medicine, vol. 3, pp. 604-618, 1986. [33] R. Black, T. Early, and G. Johnson, 'Performance of a high-temperature superconducting resonator for high-field imaging,' Journal of Magnetic Resonance, Series A, vol. 113, pp. 74-80, 1995. [34] Y. Kobayashi and M. Katoh, 'Microwave measurement of dielectric properties of low-loss materials by the dielectric rod resonator method,' Microwave Theory and Techniques, IEEE Transactions on, vol. 33, pp. 586-592, 1985. [35] P. Kaleeba, A. Tennant, and J. Ide, 'Modelling a planar phase switched structure (PSS) in Ansoft HFSS (high frequency structure simulator),' 2003, pp. 257-261 vol. 1. [36] D. Kajfez and E. Hwan, 'Q-factor measurement with network analyzer,' IEEE Transactions on microwave theory and techniques, vol. 32, pp. 666-670, 1984. [37] W. E. Kwok and Z. You, 'In vivo MRI using liquid nitrogen cooled phased array coil at 3.0 T,' Magnetic resonance imaging, vol. 24, pp. 819-823, 2006. [38] I. T. Lin, H. C. Yang, C. W. Hsieh, T. Jao, and J. H. Chen, 'Human hand imaging using a 20 cm high-temperature superconducting coil in a 3T magnetic resonance imaging system,' Journal of Applied Physics, vol. 107, pp. 124701-124701-6, 2010. [39] H. Yang, K. Tsai, J. Chen, C. Wu, H. Horng, J. Chen, and L. Kuo, 'High-Tc superconducting surface coils for improving the image quality on a 3 T imager,' Superconductor Science and Technology, vol. 20, pp. 777-780, 2007. [40] J. Wosik, L. Xue, L. M. Xie, M. Kamel, K. Nesteruk, and J. A. Bankson, 'Superconducting array for high-field magnetic resonance imaging,' Applied Physics Letters, vol. 91, pp. 183503-183503-3, 2007. [41] D. Jones, M. Catani, C. Pierpaoli, S. Reeves, S. Shergill, M. O'Sullivan, P. Golesworthy, P. McGuire, M. Horsfield, and A. Simmons, 'Age effects on diffusion tensor magnetic resonance imaging tractography measures of frontal cortex connections in schizophrenia,' Human brain mapping, vol. 27, pp. 230-238, 2006. [42] M. Kubicki, R. McCarley, C. Westin, H. Park, S. Maier, R. Kikinis, F. Jolesz, and M. Shenton, 'A review of diffusion tensor imaging studies in schizophrenia,' Journal of psychiatric research, vol. 41, pp. 15-30, 2007. [43] B. Chen and E. Hsu, 'Noise removal in magnetic resonance diffusion tensor imaging,' Magnetic Resonance in Medicine, vol. 54, pp. 393-401, 2005. [44] C. Lin, W. Tseng, H. Cheng, and J. Chen, 'Validation of diffusion tensor magnetic resonance axonal fiber imaging with registered manganese-enhanced optic tracts,' Neuroimage, vol. 14, pp. 1035-1047, 2001. [45] P. Basser, J. Mattiello, and D. LeBihan, 'MR diffusion tensor spectroscopy and imaging,' Biophysical Journal, vol. 66, pp. 259-267, 1994. [46] P. Basser, 'Inferring microstructural features and the physiological state of tissues from diffusion-weighted images,' NMR in Biomedicine, vol. 8, pp. 333-344, 1995. [47] L. Kuo, V. Wedeen, J. Weng, T. Reese, J. Chen, and W. Tseng, 'Reconstruction and visualization of white matter tracts based on clinical diffusion spectrum imaging,' 2005. [48] J. Miller, S. Hurlston, Q. Ma, D. Face, D. Kountz, J. MacFall, L. Hedlund, and G. Johnson, 'Performance of a high-temperature superconducting probe for in vivo microscopy at 2.0 T,' Magnetic Resonance in Medicine, vol. 41, 1999. [49] S. Hurlston, W. Brey, S. Suddarth, and G. Johnson, 'A high-temperature superconducting Helmholtz probe for microscopy at 9.4 T,' Magnetic Resonance in Medicine, vol. 41, pp. 1032-1038, 1999. [50] M. Cheng, B. Yan, K. Lee, Q. Ma, and E. Yang, 'A high temperature superconductor tape RF receiver coil for a low field magnetic resonance imaging system,' Superconductor Science and Technology, vol. 18, p. 1100, 2005. [51] F. E. Terman, Radio engineers' handbook vol. 2: McGraw-Hill, 1943. [52] K. Lee, M. Cheng, K. Chan, K. Wong, S. Yeung, K. Lee, Q. Ma, and E. Yang, 'Performance of large-size superconducting coil in 0.21 T MRI system,' Biomedical Engineering, IEEE Transactions on, vol. 51, pp. 2024-2030, 2004. [53] A. Hall, N. Alford, T. Button, D. Gilderdale, K. Gehring, and I. Young, 'Use of high temperature superconductor in a receiver coil for magnetic resonance imaging,' Magnetic Resonance in Medicine, vol. 20, pp. 340-343, 1991. [54] L. Darrasse and J. Ginefri, 'Perspectives with cryogenic RF probes in biomedical MRI,' Biochimie, vol. 85, pp. 915-937, 2003. [55] J. Nouls, M. Izenson, H. Greeley, and G. Johnson, 'Design of a superconducting volume coil for magnetic resonance microscopy of the mouse brain,' Journal of magnetic resonance, vol. 191, pp. 231-238, 2008. [56] I. J. Bahl, 'High-Q and low-loss matching network elements for RF and microwave circuits,' Microwave Magazine, IEEE, vol. 1, pp. 64-73, 2000. [57] J. Mispelter, M. Lupu, and A. Briguet, NMR probeheads for biophysical and biomedical experiments: theoretical principles & practical guidelines: Imperial College Pr, 2006. [58] M. K. Choy, K. K. Cheung, D. L. Thomas, D. G. Gadian, M. F. Lythgoe, and R. C. 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dc.identifier.uri | http://tdr.lib.ntu.edu.tw/jspui/handle/123456789/42998 | - |
dc.description.abstract | 由於生醫科技蓬勃發展,磁振造影是基礎研究及臨床診斷中相當重要的一個方法,不論是基礎研究或臨床診斷都期盼更高的空間和時間解析度來觀察更細微的組織結構。然而,影像解析度的提升將會降低訊雜比。相較於傳統的磁振造影線圈,使用低電阻的高溫超導材料已是公認可以大幅提升線圈品質的方式。然而,此方法應用於臨床上的可行性仍需要作進一步之驗證。
因此,本論文的主要目的為實現高溫超導線圈於核磁共振造影上應用的可行性,並且可分為下列三部份。第一為建立高溫超導表面線圈及其應用。第二為發展高溫超導體線圈及其應用。最後,運用高溫超導表面線圈來作病理上的觀測。 第一部份中,首先專注研究高溫超導表面線圈於3T MRI的模擬和量測,我們驗證了在現有的系統中,運用直徑 40毫米的高溫超導表面線圈的訊雜比為300 K下自製銅表面線圈的3.8倍。接著,運用高溫超導線圈於擴散張量磁振造影上,更可將差異角度之標準差由44.38度縮小為18.66度,也同時增進了神經追蹤之準確度,並將此技術應用在自發性腫瘤鼠腦上。最後,探討直徑20厘米的高溫超導射頻共振器系統應用於人手的研究證實為可行,並得到1.95倍訊雜比增益。第二部份中,著重討論高溫超導體線圈用以獲取小鼠的全身影像,77 K下的高溫超導體線圈的訊雜比為300K下的自製銅體線圈的兩倍。 第三部份中,首先是散曈劑誘發海馬迴損傷所產生的匹羅卡品大鼠模型,數據顯示,增強影像的對比度可能有助於早期針對性的預測,因而減少腦損傷及其相關疾病發病率。接著,連續觀察三週血管內皮生長因子(VEGF)189的變化,結果顯示,在誘導腫瘤血管生成上,有助於觀測其不同作用的VEGF異構體。 總結而言,我們驗證了高溫超導表面線圈於磁振造影上應用的可行性,也建立此技術於臨床上進一步應用之潛力。此外,我們建立起高溫超導體線圈,利用高溫超導體線圈不僅改善了訊雜比,也使小鼠的全身掃描更便利。最後,在臨床研究上,我們率先將其應用於自發性鼠腦腫瘤、癲癇及肺線癌研究上,並且驗證了此方法有助於臨床研究上。本論文成功地建立了高溫超導線圈於核磁共振造影上,透過提升訊雜比,相信對未來神經科學的基礎研究或是臨床診斷都有極大的助益。 | zh_TW |
dc.description.abstract | Throughout the development in biomedicine, magnetic resonance imaging (MRI) has become an important approach for neuroscience research and clinical applications. Neuroscience research and clinical applications both higher spatial and higher temporal resolutions are expected to help acquire finer details of the imaging object. However, as the imaging resolution goes higher, signal-to-noise ratio (SNR) limits the accuracy of quantitative MR microscopy. Compared with conventional diffusion MRI techniques, high-temperature superconducting (HTS) radio-frequency (RF) coils have been proposed as a promising tool for tissue microscopy with high resolution because of its low-resistance characteristic for MR probe design. However, the potential of HTS RF coils on clinical applications has not been well demonstrated yet.
Therefore, the overall objective of this dissertation is threefold and targeted to facilitate the techniques of HTS RF coils for the use of MRI. First, we built the HTS RF surface coils and its applications. Second, we developed a HTS RF volume coil and its applications. Finally, we verified the HTS RF surface coils on the investigations of the clinical research. In Part I, we aim at the study of simulations and measurements of the HTS RF surface coils in a 3T MRI. Our results showed that HTS RF surface coil of a 40 mm in diameter provided an average SNR gain of approximately 3.8 folds on our 3T MRI system. Next, we concentrate on the use of the HTS surface coils in enhancing the diffusion tensor imaging. Results showed that the cooled HTS surface coil with a standard deviation of deviation angles significantly reduced from 44.38° to 18.66°. Furthermore, the fiber tractography of a rat’s corpus callosum (CC) demonstrated the advantage of using a cooled HTS surface coil to investigate the neural connectivity as well and a spontaneous tumor of rat brain is presented with a HTS surface coil. Finally, it was also demonstrated that the SNR using the HTS surface coil of 200 mm in diameter was higher than that of a copper surface coil for the MRI study of a human hand by 1.95 folds. In Part II, we focus on a new Bi-2223 superconducting saddle coil and designed for the magnetic resonance image of a mice’s whole body in a Bruker 3T MRI system. The SNR of a HTS saddle coil at 77 K doubled compared with that of a home-made copper saddle coil for a mice whole body MR study. In Part III, we focused on the studies of edilepticus-induced hippocampal injury in the pilocarpine rat model. These data suggested an enhanced image contrast that may contribute to the early targeted intervention which could minimize brain injury and its associated morbidities. Then, we focused on the three-week observation of vascular endothelial growth factor (VEGF) isoform 189 by using a HTS coil. The results helped elucidate the role of different VEGF isoforms in inducing tumor angiogenesis, the interaction between the structure of tumor angiogenesis, and the mechanisms underlying the association between the expression of a specific VEGF isoform in a tumor and the patient’s clinical outcome in human cancers. In summary, we successfully demonstrated the potential of HTS RF coils on clinical applications. Additionally, we built a HTS volume coil. The use of a HTS volume coil not only improved SNR but also enabled a simple one scan of a mouse’s whole body. Finally, we apply the HTS RF coils with the study of a spontaneous tumor of rat brain, edilepticus-induced hippocampal injury and VEGF 189. And we demonstrated the HTS RF coils be helpful in clinical research. Conclusively, our proposed methods successfully built the HTS RF coil on MRI by increasing SNR, which will be potentially useful to facilitate the neuroscience research and clinical applications. | en |
dc.description.provenance | Made available in DSpace on 2021-06-15T01:32:09Z (GMT). No. of bitstreams: 1 ntu-100-D96942030-1.pdf: 2736848 bytes, checksum: 41d1c8e997c636428b6c13b4d1927f3c (MD5) Previous issue date: 2011 | en |
dc.description.tableofcontents | CONTENTS
Acknowledgements i 中文摘要 iii ABSTRACT v CONTENTS viii LIST OF FIG.S xiii LIST OF TABLES xvii Chapter 1 Introduction 1 1.1 Motivation 1 1.2 SNR of a MRI System 3 1.2.1 Signal detected in the RF coil 3 1.2.2 Noise component in the RF coil 4 1.2.3 RF coil quality factor 6 1.2.4 Evaluation of SNR gain by Quality factor 8 1.2.5 Estimation of SNR between HTS and copper coil 9 1.3 Bi2Sr2Ca2Cu3Ox surface coil 9 1.3.1 Impedance of High-Temperature Superconductors 10 1.3.2 Tuning and Matching 11 1.4 Review on the Development of HTS RF coil in MRI 15 1.5 Outline of the dissertation 16 Part I HTS Surface Coils 18 Chapter 2 Boosted Signal-to-Noise Ratio with a 4 cm High-Temperature Superconducting Surface Coil in a 3T MRI System: Using Finite-Element Radiofrequency Simulations and Measurements 19 2.1 Introduction 19 2.2 The use of HTS coils under different condition 21 2.3 Electromagnetic modeling 22 2.3.1 Coil 23 2.3.2 Detecting coil 24 2.3.3 Boundary limitation 25 2.3.4 Quality factor of EM simulation 25 2.4 Experiments 25 2.4.1 MRI system 25 2.4.2 Temperature-stable cryostat 26 2.4.3 Bi-2223 surface coil 27 2.4.4 Copper surface coil 27 2.4.5 Sample, imaging sequence 28 2.4.6 Evaluation of SNR gain by quality factor 28 2.5 Simulation Analysis 29 2.5.1 Qs of EM simulation 29 2.5.2 The simulation relation between SNR and depth 29 2.6 Experiment results and discussion 30 2.6.1 Unloaded Qs 30 2.6.2 The relation between measured SNR and depth 32 2.6.3 Comparison between the simulated and measured results in SNR 33 2.6.4 The comparison of the stimulated quality factor and measured quality factor 33 2.6.5 Discussion 34 2.7 Conclusion 36 Chapter 3 Enhancement of Diffusion Tensor Imaging with a 4 cm High-Temperature Superconducting Surface Coil in a 3T MRI 37 3.1 Introduction 37 3.2 Material and methods 38 3.2.1 MRI experiment 38 3.2.2 HTS coil fabrication 39 3.2.3 Diffusion tensor magnetic resonance imaging 39 3.2.4 Data analysis 40 3.3 Results 41 3.3.1 Analysis of deviation angle 41 3.3.2 Comparison of fiber tracking 42 3.3.3 DTI using HTS coil for a spontaneous brain tumors in the rat 43 3.4 Discussion 45 3.5 Conclusion 46 Chapter 4 Validation of Improved Human Hand Imaging Using a 20 cm High-temperature Superconducting Surface Coil in a 3T MRI system 48 4.1 Introduction 48 4.2 Material and methods 49 4.2.1 Resonant frequency 49 4.2.2 Input impedance 50 4.2.3 Bi-2223 tape 50 4.2.4 Copper coil 50 4.3 Results and discussions 51 4.4 Conclusion 57 Part II HTS Volume Coils 58 Chapter 5 Improved Mice Whole Body Screening with a High-temperature Superconducting Volume Coils in a 3T MRI 59 5.1 Introduction 59 5.2 Material and methods 61 5.2.1 Theory 61 5.2.2 Hardware 62 5.2.3 Imaging experiment 66 5.3 Results 66 5.3.1 Phantom imaging 66 5.3.2 Mice whole body imaging 68 5.4 Discussion 69 5.4.1 Phantom imaging 69 5.4.2 Mice whole body imaging 70 5.5 Conclusion 71 Part III Application Example 73 Chapter 6 Application Example 74 6.1 Case study: HTS RF surface coil predicts status of edileptics-induced hippocampal injury in the pilocarpine rat model 74 6.1.1 Introduction 74 6.1.2 Methods 74 6.1.3 Results 75 6.1.4 Discussions 76 6.1.5 Conclusion 76 6.2 Case study: Three-week observation of vascular endothelial growth factor (VEGF) isoform 189 using a HTS coil 76 6.2.1 Introduction 76 6.2.2 Methods 78 6.2.3 Results 78 6.2.4 Discussions 79 6.2.5 Conclusion 80 Chapter 7 Discussions, Future Works, and Conclusions 81 7.1 Discussions 81 7.1.1 Relation between imaging size and frequency 81 7.1.2 Relation between imaging size and diameter of coil 82 7.1.3 YBCO thin-film 83 7.1.4 Temperature-stable cryostat 85 7.1.5 Phased array 87 7.1.6 Improvements and limitations of HTS coil development 88 7.2 Future Works 91 7.2.1 Bi-2223 tape phased array 91 7.2.2 Fabrication of YBCO thin-film 92 7.2.3 Consideration of the cryostat 93 7.3 Conclusion 94 REFERENCE 95 PUBLICATIONS AND PATENTS 106 APPENDIX A: Honors 109 LIST OF FIG.S Fig. 1.1 Equivalent Circuit of the LC loop and a Matching Coil: 13 Fig. 1.2 (a) Experiment setup to measure the quality factor, (b) Network analyzer. 15 Fig. 2.1 (a) Testing model of the resonance circuit. (b) The whole simulation model of RF circuit. 23 Fig. 2.2 The coil setup in MRI. 26 Fig. 2.3 (a) Bi-2223 coil and, (b) copper coil 28 Fig. 2.4 The relation between SNR and depth according to simulated data. (a) The normalized simulated result by using copper coil at 300K (a) The normalized simulated result by using HTS coil at 77K. (Need to mention, the maximum value of HTS coil set to one). 30 Fig. 2.5 Phantom images were acquired from (a) Copper coil at 300K and SNR=52, (b) Copper coil at 77K and SNR=88, (c) HTS coil at 77K and SNR=200. 31 Fig. 2.6 The experimental data determined the relation between SNR and depth. 33 Fig. 3.1 The 3T system setup of the rat experiment, where the matching & signal pick-up coil with a tuning variable capacitance was put in the middle of the HTS tape coil and the rat. 39 Fig. 3.2 DTI of the brain of a rat with (a) the copper surface coil at 300 K. (b) 42 Fig. 3.3 (a) The tractography of the corpus callosum using a HTS surface coil at 77 K. The tracts are 3-D visualized and superimposed with Null images. (b) The tractography of corpus callosum using copper surface coil at 300 K. The tracts are 3-D visualized and superimposed with Null images. 43 Fig. 3.4 (a) MRI T2 weighted image with rat brain tumor, (b) DTI images using a copper coil at 300 K, (c) DTI images using a HTS coil at 77 K. 44 Fig. 3.5(a) ADC map of normal rat brain, (b) FA map of normal rat brain, (c) DTI of normal rat brain, (d) ADC map of rat brain tumor using a copper coil at 300 K, (e) FA map of rat brain tumor using a copper coil at 300 K, (f) DTI of rat brain tumor using a copper coil at 300 K, (g) ADC map of rat brain tumor using a HTS coil at 77 K, (h) FA map of rat brain tumor using a HTS coil at 77 K, (i) DTI of rat brain tumor using a HTS coil at 77 K. 45 Fig. 4.1 The 3T system setup of the phantom experiment, where the matching & signal pick-up coil with a tuning variable capacitance was put in the middle of the HTS tape coil and the phantom. 51 Fig. 4.2 Coronal phantom images and mesh images comparison by Bruker fast spin-echo sequence. The background noise of mesh image acquired from the HTS coil is significantly lower than that of the home-made copper coil. (a) Phantom image acquired from the home-made copper coil with SNR=115. (b) Phantom image acquired from the HTS coil with SNR=256. (c) Photograph of a 10 cm diameter spherical phantom filled with 10 mM CuSO4. (d) Mesh image acquired from home-made copper coil (e) Mesh image acquired from HTS coil. 53 Fig. 4.3 Plots of intensities along the horizontal axis extracted from phantom images, in which the dash, solid curves denote the HTS in 77K and home-made copper coil at room temperature, respectively. 54 Fig. 4.4 Images of a human wrist by Bruker fast spin-echo sequence with (a) the HTS coil at 77 K with the SNR of 195, (b) focal magnification of (a) which the interosseous muscle is visible, (c) the copper coil at 300 K with SNR of 100 and (d) focal magnification of (c) which the interosseeous muscle is visible less conspicuity, and (e) the anatomy illustrations of (a) 56 Fig. 5.1 (a) The saddle shape was shown in plane from. (b) Receiving saddle resonator and pick-up resonator are indicated by the bottom one and the above one. (c) The equivalent circuit of the inductive coupled designed shows that RF signal is picked up by using the mutual inductive coupling. 63 Fig. 5.2 The 3T system setup of the mice experiment, where the matching & signal pick-up coil with a tuning variable capacitance was put inside of the HTS saddle coil. The cryostat includes the vacuum jacket and flowing liquid nitrogen. 64 Fig. 5.3 (a) A picture of the cylindrical phantom filled with 20 mM CuSO4 solution. (b) The home-made copper saddle coil at 300 K with SNR of 115. (c) The home-made copper saddle coil at 77 K with SNR of 182. (d) The HTS saddle coil at 77 K with SNR of 256. (e) The comparison of SNR gain with copper and HTS saddle coils and it clearly shows the benefit using HTS saddle coil. 67 Fig. 5.4 The 3T system setup of the mice experiment, where the matching & signal pick-up coil with a tuning variable capacitance was put inside of the HTS saddle coil. The cryostat includes the vacuum jacket and flowing liquid nitrogen. 69 Fig. 6.1 The changes of pilocarpine rat brain were imaged before and after status epilepticus (SE) on days 0, 1 and 4. 75 Fig. 6.2 VEGF 189 of image was obtained using a HTS coil at 300 K in (a) day 7, (b) day 14 and (c) day 21; VEGF 189 of image was obtained using a HTS coil at 77 K in (d) day 7, (e) day 14 and (f) day 21. 79 Fig. 7.1 The simulated SNR gain between imaging size and frequency 81 Fig. 7.2 The simulated SNR gain between imaging size and diameter of coil 82 Fig. 7.3The experimental SNR gain between imaging size and diameter of coil. 83 Fig. 7.4 The spiral pattern of YBCO thin-film [39]. 84 Fig. 7.5 (a) The image was obtained with the copper coil in 300 K, (b) the images was obtained with the YBCO thin-film in 77 K [39]. 85 Fig. 7.6 The detail of in-vivo rat brain image acquired from HTS tape surface coil at 77 K for long duration from rat axial view. The structure are: 1) Olfactory bulb, 2) Caudate putamen, 3) Lateral ventricle, 4) Corpus callosum, 5) Dentate gyrus, 6) Superior colliculus, 7) Inferior colliculus and 8) Cerebellar lobule. 86 Fig. 7.7 4-channel phased array coils. Inset: magnified view of one preamplifier[81]. 88 Fig. 7.8 The measurement of the cold head’s temperature inside the cryostat. 90 LIST OF TABLES Table 1.1 General specification of Bi-2223 tapes 10 Table 2.1 Measured and the simulated Qs from HTS and copper coil (Cu), u: unloaded (outside magnet) 29 Table 2.2 Predicted SNR gain and measured Qs from HTS and copper coil (Cu) (outside magnet) 32 | |
dc.language.iso | en | |
dc.title | 高溫超導線圈於磁振造影之生醫應用 | zh_TW |
dc.title | Novel Applications of High Temperature Superconducting
Coils for MR Imaging | en |
dc.type | Thesis | |
dc.date.schoolyear | 99-2 | |
dc.description.degree | 博士 | |
dc.contributor.coadvisor | 楊鴻昌(Hong-Chang Yang) | |
dc.contributor.oralexamcommittee | 郭萬祐,吳茂昆,張允中,林發暄,林慶波,姚晶,江衍偉 | |
dc.subject.keyword | 高溫超導表面線圈,高溫超導體線圈,擴散磁振造影,訊雜比, | zh_TW |
dc.subject.keyword | High-temperature superconducting RF surface coil,High-temperature superconducting RF volume coil,diffusion tensor imaging,signal-to-noise ratio, | en |
dc.relation.page | 109 | |
dc.rights.note | 有償授權 | |
dc.date.accepted | 2011-08-16 | |
dc.contributor.author-college | 電機資訊學院 | zh_TW |
dc.contributor.author-dept | 生醫電子與資訊學研究所 | zh_TW |
顯示於系所單位: | 生醫電子與資訊學研究所 |
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