多頻同步驅動光源之頻域式擴散光學造影研究

以作者查詢圖書館館藏

、以作者查詢臺灣博碩士

、以作者查詢全國書目

、勘誤回報

、線上人數：13

、訪客IP：13.58.39.23

姓名

許彥揚(Yan-Yang HSU) 查詢紙本館藏

畢業系所

生醫科學與工程學系

論文名稱

多頻同步驅動光源之頻域式擴散光學造影研究

相關論文

★ TFT-LCD前框卡勾設計之衝擊模擬分析與驗證研究	★ TFT-LCD 導光板衝擊模擬分析及驗證研究
★ 數位機上盒掉落模擬分析及驗證研究	★ 旋轉機械狀態監測-以傳動系統測試平台為例
★ 發射室空腔模態分析在噪音控制之應用暨結構聲輻射效能探討	★ 時頻分析於機械動態訊號之應用
★ VKF階次追蹤之探討與應用	★ 火箭發射多通道主動噪音控制暨三種線上鑑別方式
★ TFT-LCD衝擊模擬分析及驗證研究	★ TFT-LCD掉落模擬分析及驗證研究
★ TFT-LCD螢幕掉落破壞分析驗證與包裝系統設計	★ 主動式火箭發射噪音控制使用可變因子演算法
★ 醫學/動態訊號處理於ECG之應用	★ 光碟機之動態研究與適應性尋軌誤差改善
★ 具新型菲涅爾透鏡之超音波微噴墨器分析與設計	★ 醫用近紅外光光電量測系統之設計與驗証

檔案

[Endnote RIS 格式]

[Bibtex 格式]

[相關文章]

[文章引用]

[完整記錄]

[館藏目錄]

[檢視]

[下載]

本電子論文使用權限為同意立即開放。
已達開放權限電子全文僅授權使用者為學術研究之目的，進行個人非營利性質之檢索、閱讀、列印。
請遵守中華民國著作權法之相關規定，切勿任意重製、散佈、改作、轉貼、播送，以免觸法。

摘要(中)

乳癌是女性最常發生的癌症之一，且發生率有逐年攀升之趨勢。然而統計報告顯示，前期乳癌(第零到二期) 的存活率高達90%以上，說明了乳癌盡早診斷與治療的重要性。目前現有的臨床檢測設備，如：乳房X光攝影(X-ray mammography)、超音波檢測(Ultrasound) 及磁振造影(Magnetic Resonance Imaging)，有著輻射疑慮、操作者技術、價格昂貴及適用對象限制等問題；因此，擁有非輻射、非侵入性、適用年齡層廣泛等優勢的頻域式近紅外光擴散光學斷層影像(Near Infrared Frequency domain Diffuse Optical Tomography, NIR FDOT)便開始成為熱門的研發對象。
NIR FDOT係以25 - 1000 MHz交流電源驅動700 - 900 nm近紅外光照射待測物(如乳房)，並利用光接收器(如光電倍增管)接收從待測物表面射出的光資訊，即因腫瘤組織對於近紅外光之吸收及散射特性與正常組織的差異而產生的光衰減量(ΔA)與相位延遲量(Δθ)。使用越多頻率驅動光源可得到越多組的光資訊，並可預期提升重建影像的品質，但也因順序式量測而增加了檢測時間。本篇論文基於多頻驅動光源的作法，實驗中以訊號產生器(AFG3102) 輸出29 MHz方波電源驅動830 nm雷射，量測直徑80 mm，高90 mm，"μa" 及 "μs′" 為0.0074 mm-1及0.85 mm-1之圓柱形光學假體，將不同大小及光學係數對比度之橢球型腫瘤假體嵌於與背景假體相同光學係數之柱條內，以插拔式改變不同大小、對比度腫瘤之離心距，共四個案例。因方波為複合弦波的特性，在同一量測時間下能獲得相較單頻驅動光源數倍的光資訊，實驗中收集方波驅動光源前兩諧頻的光資訊，藉多頻擴散光學斷層造影重建出圓柱仿體內部"μa" 、 "μs′" 光學分佈影像，並以CSD量化後進行方波與單頻驅動光源之重建影像比較，預期大顆腫瘤假體的"μa" 、 "μs′" 重建影像之CSD量化值會較小顆高；腫瘤假體在位置淺處的"μa" 、 "μs′" 重建影像之CSD量化值會較深處高；頻率高之單頻驅動光源量測在"μs′" 重建影像之CSD量化值應較低頻優異；方波驅動光源的 "μa" 、 "μs′" 重建影像CSD量化值應較高、低單頻驅動光源優異。而結果可發現，因訊號產生器輸出的方波並非理想形式及實驗設備的限制，使方波驅動光源未有顯著的效果，期待未來能以合成複合週期訊號驅動光源量測進行改善。

摘要(英)

Breast cancer is one of the most common cancers among women, and the incidence rate is increasing year by year. However, the statistical report shows that the survival rate of early breast cancer (stages 0 to 2) is higher than 90%, indicating the importance of early diagnosis and treatment of breast cancer. Existing clinical testing equipment, such as: X-ray mammography, Ultrasound and Magnetic Resonance Imaging, have radiation doubts, highly depending on operator’s skill, expensive price or restrictions on applicable objects. Therefore, frequency-domain near-infrared frequency domain diffuse optical tomography (NIR FDOT), which has the advantages of non-radiation, non-invasiveness, and can be adapted on broad age range, recent year it has become a popular research object.
The NIR FDOT is applying 25 - 1000 MHz AC power to drive 700 - 900 nm near-infrared light to measure the object (such as breasts), and uses a light receiver (such as a photomultiplier tube) to receive the light information comes out from the surface of the object, that is the amount of light attenuation (ΔA) and phase delay (Δθ) due to the difference between the absorption and scattering characteristics of tumor tissue and normal tissue. Using more frequencies to drive the light source can obtain more sets of light information, and it is expected to improve the quality of the reconstructed image, but it also increases the detection time due to sequential measurement. This thesis is based on the method of driving the light source with multiple frequencies, yet in the experiment, the function generator (AFG3102) is used to outputs a 29 MHz square wave to drive a 830 nm laser, measuring 80 mm in diameter, 90 mm in height cylindrical optical phantoms, its "μa" and "μs′ " are 0.0074 mm-1 and 0.85 mm-1, embedding ellipsoid tumor phantoms of different sizes and contrasts of optical coefficients in columns with the same optical coefficients as the background phantom. There are four cases in which the off center distance of tumors of different sizes and contrasts is changed in a plug-in manner. Since the square wave is a characteristic of a composite sine wave, it can obtain several times light information compared to a single-frequency driving light source at the same measurement time. In the experiment, the optical information of the first two harmonic frequencies is collected, and using developed reconstructing software to reconstruct optical distribution images of "μa" and "μs′ " inside the cylindrical phantom, and quantified by CSD value. The reconstructed images of the square wave and the single frequency drive light source were compared. Expected CSD value of large tumor will be higher than small one; and the CSD value of the tumor placed shallow will higher than the one in deep; the CSD value of high frequency measurement should be higher than low frequency measurement; the CSD value of square wave measurement should be higher than both high and low single frequency measurement. As a result, it can be found that the square wave output by the signal generator is not an ideal form, also some restrictions of equipment, so that the square wave measurement has no significant effect. It is expected that the composite periodic signal driving light source measurement can be applied and improved the result in the future.

關鍵字(中)

★ 同步多頻擴散光學量測
★ 方波交流驅動電源
★ 近紅外光擴散光學斷層掃描
★ 仿乳房光學特性假體

關鍵字(英)

論文目次

摘要 i
Abstractiii
誌謝 v
目錄 vi
圖目錄 viii
表目錄 xi
一、緒論 1
1-1 研究動機與目的 1
1-2 文獻探討 3
1-3 論文範疇 4
二、理論基礎 6
2-1 乳房組織光學特性 6
2-1-1 乳房結構 6
2-1-2 乳房光學特性 8
2-2 組織擴散光學檢測機制10
2-2-1 乳房光學特性 10
2-2-2 光學檢測模式 13
2-3 擴散光學影像重建 13
三、方波擴散光學量測 21
3-1 量測系統架構 21
3-1-1 掃描量測模組 21
3-1-2 光電量測架構 24
3-1-3 系統檢測程序 29
3-2 元件與量測模組校正 30
3-3 仿乳房光學特性假體 41
3-3-1 仿乳假體光學特性 41
3-3-2 仿乳假體設計製作 43
四、檢測驗證與結果討論 44
4-1 DOT影像評估方式 44
4-2 仿體案例與實驗結果 45
4-2-1 仿體案例 45
4-2-2 實驗結果 47
五、結論與未來展望 52
5-1 結論 52
5-2 未來展望 52
參考文獻 53

參考文獻

[1] 衛生福利部國民健康署，“台灣女性10大癌症，按發生率及死亡率排序”，中華民國衛生福利部民國106年癌症登記年報，pp. 5, 2020.
[2] 國家衛生研究院癌症研究組台灣癌症臨床研究合作組織，“乳癌診斷與治療共識”，國家衛生研究院，pp. 1-2, 2004.
[3] 林洋鈺，“如何正確選擇乳房篩檢工具”，東元綜合醫院高級健檢中心。取自
https://w3.tyh.com.tw/health/b_special_p05.html
[4] E. D. Pisano, C. Gatsonis, E. Hendrick, M. Yaffe, J. K. Baum, S. Acharyya, E. F. Conant, L. L. Fajardo, L. Bassett, C. D’Orsi, R. Jong, and M. Rebner, “Diagnostic Performance of Digital versus Film Mammography for Breast-Cancer Screening,” New England Journal of Medicine, Vol. 355(17), pp. 1840-1840, 2006.
[5] 台灣癌症基金會, “乳癌- breast cancer”。取自https://www.canceraway.org.tw/cancerinfo.asp?id=EC4BC652-18B3-464C-B19D-CB0C49C64285
[6] 黃獻樑、程紹儀，“乳癌的篩檢”，台灣家庭醫學醫學會。取自https://www.tafm.org.tw/ehc-tafm/s/w/ebook/people_other/journalContent/358
[7] 偉成醫師，“乳癌檢查與知識網”。取自http://www.mdesign.tw/display/breast/examination.php
[8] M. Herranz and A. Ruibal, “Optical Imaging in Breast Cancer Diagnosis: The Next Evolution,” Journal of Oncology, pp. 1-10., 2012.
[9] S. L. Jacques, and B. W. Pogue, “Tutorial on diffuse light transport”, Journal of Biomedical Optics, Vol. 13(4), 041302, 2008.
[10] G. M. Hale and M. R. Querry, “Optical constants of water in the 200 nm to 200 µm wavelength region,” Appl. Opt. 12, pp. 555 – 563, 1973.
[11] T. J. Brukilacchio, “A diffuse optical tomography system combined with X-ray mammography for improved breast cancer detection,” Tufts University Ph.D Thesis, 1-99, 2003.
[12] A. H. Hielschera, A.Y. Bluestoneab, G. S. Abdoulaeva, A. D. Klosea, J. Laskera, M. Stewartb, U. Netzc, and J. Beuthanc, “Near-infrared diffuse optical tomography,” Disease Markers, Vol. 18(5-6), 2002.
[13] B. Pogue , M. Testorf, T. McBride, U. Osterberg, and K. Paulsen, “Instrumentation and design of a frequency-domain diffuse optical tomography imager for breast cancer detection”, US National Library of Medicine National Institutes of Health, Vol. 1(13), pp. 391-403, 1997.
[14] M. Cutler, “Transillumination as an aid in the diagnosis of breast lesions”, Surg. Gynecol. Obstet, Vol. 48, pp. 721, 1929.
[15] C. M. Gros, Y. Quenneville, and Y, Hummel, “Diaphano- logic mammaire”, J. Radiol. Electrol. Med. Nucl., 53:297, 1972.
[16] B. Ohlsson, J. Gundersen, and D. Nilsson, “Diaphanography: A Method for Evaluation of the Female Breast”, World Journal of Surgery, Vol. 4(6), pp.701-705, 1980.
[17] T. O. McBride, B. W. Pogue, U. L. Ӧisterberg, and K. D. Paulsen, “Separation of Absorption and Scattering Heterogeneities in NIR Tomographic Imaging of Tissue”, Biomedical Optical Spectroscopy and Diagnostics, TuC2, 2000.
[18] G. Gulsen, B. Xiong, O. Birgul, and O. Nalcioglu, “Design and implementation of a multifrequency near-infrared diffuse optical tomography system”, Journal of Biomedical Optics, Vol. 11(1), 014020, 2006.
[19] M. B. Unlu, O.Birgul, R. Shafiiha, G. Gulsen, O. Nalcioglu, “Diffuse optical tomographic reconstruction using multifrequency data”, Journal of Biomedical Optics, Vol. 11(5), 054008, 2006.
[20] M. A. Mastanduno, S. Jiang, R. DiFlorio-Alexander, B. W. Pogue, and K. D. Paulsen, “Automatic and robust calibration of optical detector arrays for biomedical diffuse optical spectroscopy”, Biomedical Optics Express, Vol.3(10), 2352, 2012.
[21] 財團法人乳癌防治基金會， “乳房的構造”。取自https://www.breastcf.org.tw/contents/text?cid=43&tid=22
[22] H. Q. Woodard, and D. R. White, “The composition of body tissues,” Br. J. radiol. 59(708), 1209-1219, 1986.
[23] C. Tromans, and M. Brad, “An Alternative Approach to Measuring Volumetric Mammographic Breast Density,” in IWDM 2006, S. M. Astley et al., LNCS, 4046, Springer Verlag., 2006, pp.26-33.
[24] Royal women’s hospital, Victoria Australia, “Normal changes in your breasts”.取自https://www.thewomens.org.au/health-information/breast-health/normal-changes-in-your-breasts
[25] 林哲斌，“良性腫瘤與惡性腫瘤要如何鑑別,”台灣癌症防治網。取自
http://www.tccf.org.tw/old/magazine/maz21/m8.htm
[26] Cancer Treatment Central of America, “Breast cancer symptom”. 取自
https://www.cancercenter.com/cancer-types/breast-cancer/symptoms.
[27] 衛生福利部國民健康署，“乳癌防治”，2016。取自
https://www.hpa.gov.tw/Pages/Detail.aspx?nodeid=614&pid=1124
[28] 乳房醫學中心，“乳癌簡介,”臺大醫院。取自https://www.ntuh.gov.tw/BC/AboutUs/%E8%AA%8D%E8%AD%98%E4%B9%B3%E7%99%8C.aspx
[29] L. Wang, X. L., P. Galland, P. P. Ho, and R. R. Alfano, “ True scattering coefficients of turbid matter measured by early-time gating,” Opt. Lett. 20(8), 913-915, 1995.
[30] A. G. Alkholidi and K. S. Altowij, "Contemporary issues in wireless communications," InTech Croatia, 2014.

[31] Oregon Medical Laser Center, “Optical Properties Spectra,” , 2015. 取自
http://omlc.org/spectra/.
[32] A. Cerussi, D. H., N. Shah, R. Mehta, A. Durkin, J. Butler, and B. J. Tromberg, “Predicting response to breast cancer neoadjuvant chemotherapy using diffuse optical spectroscopy,” PNAS 104(10), 4014-4019, 2006.
[33] T. Durduran, R. Choe, W. B. Baker, and A. G. Yodh, “Diffuse optics for tissue monitoring and tomography,” Reports on Progress in Physics, vol. 73, no. 7, paper # 076701, 2010.
[34] B. W. Pogue, T. O. McBride, U. L. Osterberg, and K. D. Paulsen, “Comparison of imaging geometries for diffuse optical tomography of tissue,” Opt. Express 4(8), 270-286, 1999.
[35] 甘弘暐，“多頻率同步驅動光源之三維頻域式擴散光學斷層造影數值計算研究”，國立中央大學碩士論文，2020。
[36] K. D. Paulsen, and H. Jiang, “Spatially varying optical property reconstruction using a finite element diffusion equation approximation,” Med. Phys., 22(6), 691-701,1995.
[37] S. R. Arridge, M. Schweiger, M. Hiraoka, and D. T. Delpy, “A finite element approach for modeling photon transport in tissue, ” Med. Phys., 20(2) 299-309, 1993.
[38] T. J. Farrell, M. S. Patterson, and B. C. Wilson, “A diffusion theory model of spatially resolved, steady-state diffuse reflectance for the noninvasive determination of tissue optical properties in vivo,” Med. Phys., 19(4), 879-888, 1992.
[39] W. Egan, Optical properties of inhomogeneous materials: Applications to geology, astronomy chemistry, and engineering, 2012.
[40] 嚴中成，“三維近紅外光擴散光學斷層影像重建之數值計算研究”，國立中央大學碩士論文，2016。
[41] S. R. Arridge, M. Schweiger, M. Hiraoka, and D. T. Delpy, “A finite element approach for modeling photon transport in tissue, ” Med. Phys., 20(2) 299-309, 1993.
[42] 石佩君，“多重光電倍增管校正模組設計製作及其於擴散光學斷層造影系統之應用”，國立中央大學碩士論文，2015。
[43] F. Marki, and C. Marki, “ Marki microwave mixer basics Primer a Tutorial for RF & microwave mixers,” Technical Note of Marki Microwave Inc., 2011.
[44] Hamamatsu Photonics K.K. Electron Tube Division, “ Photomultiplier Tube Modules, ”Hamamatsu Photonics K.K., pp. 24-25, 2015.
[45] F. P. Bolin, L. E. Preuss, R. C. Taylor, and R. J. Ference, “ Refractive index of some mammalian tissues using a fiber optic cladding method,” Appl. Opt. 28(12), 2297-2303, 1989.
[46] G. J. Tearney, M. E. Brezinski, J. F. Southern, B. E. Bouma, M. R. Hee, and J. G. Fujimoto, “ Determination of the refractive index of highly scattering human tissue by optical coherence tomography,” Opt. Lett. 20(21), 2258-2260, 1995.
[47] B. W. Pogue, and M. S. Patterson, “ Review of tissue simulating phantoms for optical spectroscopy, imaging and dosimetry, “J. Biomed. Opt. 11(4), 041102, 2006.
[48] G. M. Hale and M. R. Querry, “ Optical constants of water in the 200 nm to 200 µm wavelength region, ” Appl. Opt. 12(3), 555-563, 1973.
[49] B. A. Brooksby, “ Phantom design,” Chapter 5 in Combining near infrared tomography and magnetic resonance imaging to improve breast tissue chromophore and scattering assessment, ” Dartmouth College, 85-93, 2005.
[50] M. C. Pan, C. H. Chen, L. Y. Chen, M. C. Pan, and Y. M. Shyr, “Highly resolved diffuse optical tomography: a systematic approach using high-pass filtering for value-preserved images,” J Biomed Opt.,13(2):024022, 2008 Mar-Apr
[51] A. J. Welch, and M. J. C. van Gemert, “Optical-Thermal Response of Laser-Irradiated Tissue Second Edition, ” Springer SBM, Chap. 8, 2010.

指導教授

潘敏俊

審核日期

2020-8-20

推文