血糖检测仪论文中英文资料对照外文翻译文献.doc

《血糖检测仪论文中英文资料对照外文翻译文献.doc》由会员分享，可在线阅读，更多相关《血糖检测仪论文中英文资料对照外文翻译文献.doc（17页珍藏版）》请在沃文网上搜索。

1、 血糖检测仪论文中英文资料英文原文 SICE Annual Conference 2011September 13-18, 2011, Waseda University, Tokyo, Japan Blood Glucose Level Measurement by Confocal Reflection Photodetection System Yuki Miyauchi，Takuro Horiguchi, Hiroaki Ishizawa, Shin-ichirou Tezuka and Hitoshi Hara Interdisciplinary Graduate School of

2、 Science and Technology, Shinshu University, Nagano, Japan (Tel : +81-268-21-5400; E-mail: f09a212shinshu-u.ac.jp)Graduate School of Science and Technology, Shinshu University, Nagano, Japan (Tel : +81-268-21-5400; E-mail: 10fa221bshinshu-u.ac.jp)Faculty of Textile Science and Technology, Shinshu Un

3、iversity, Nagano, Japan(Tel : +81-268-21-5400; E-mail: zawashinshu-u.ac.jp)Yokogawa Electric Corporation, Nagano, Japan (Tel : +81-265-85-5620; E-mail: Shin-ichirou.Tezuka)Yokogawa Electric Corporation, Nagano, Japan(Tel : +81-265-85-5620; E-mail: Hitoshi.Hara) Abstract: In the present study, the co

4、nfocal optical system has been constructed by using the near-infrared laser, and the reflection photodetection system of the living body has been developed. This system reduces the influence of a complex light scatter by the skin tissue and achieves a highly accurate measurement by confocal optical

5、system. And the initial experiment for the development of the non-invasive blood glucose meter that presumed the blood glucose level by thenear-infrared absorption of the living body has been done. In this report, the principle of the blood glucose level measurement of this system has been confirmed

6、. The light intensity of the reflection in the living body skin tissue has been measured in the constructed system, and it has been compared with the blood glucose level reference value. As a result, the absorption of the reflected light that depended on the blood glucose level has been confirmed. T

7、he possibility of measuring the blood glucose level has been shown. Keywords: Confocal Optical System, Non-invasive, Blood Glucose, Near-infrared. 1. INTRODUCTION Recently, the diabetic increases remarkably 1, 2. The self-monitoring of blood glucose (SMBG) is necessary and indispensable to treat the

8、 diabetic. However, present SMBG has been limited to the measurement that needs collecting blood. The patient has loads of pain, stress, and costs, etc. Therefore, the non-invasive blood glucose meter to be able to measure the blood glucose level is strongly expected 3-5. In the present study, the c

9、onfocal optical system has been constructed by using the near-infrared laser, and the reflection photodetection system of the living body has been developed. And the initial experiment for the development of the non-invasive blood glucose meter that presumed the blood glucose level by the near-infra

10、red absorption of the living body has been done. This system reduces the influence of a complex light scatter by the skin tissue and achieves a highly accurate measurement by confocal optical system 6, 7. In this report, the focus depth by the confocal optical system of this system has been confirme

11、d. And the principle of the blood glucose level measurement of this system was confirmed. The light intensity of the reflection in the living body skin tissue has been measured in the constructed system, and it has been compared with the blood glucose level reference value. As a result, the absorpti

12、on of the reflected light that depended on the blood glucose level has been confirmed. The possibility of measuring the blood glucose level has been shown. 2. EXPERIMENTAL METHOD2.1 Measuring system Fig. 1 shows the optical system for the system constructed in the present study. A near-infrared ray

13、VCSEL (Vertical Cavity Surface Emitting Laser) 8 of wavelength 1.55 m was used for the light source of this system, and PD (InGaAs PIN photodiode, FGA21; THORLABS) was used for the photo detector. This system is a confocal optical system 9 that has the depth resolution and high plane resolution. Int

14、ensity of the reflected light from the sample surface side to the inside of sample can be detected by moving the window up and down. The source of light has stabilized by the APC (Auto Power Control) circuit 10. Fig. 2 Appearance of the polycarbonate plate measurementFig. 3 Appearance of a living bo

15、dy blood glucose level measurement 2.2 Polycarbonate plate measurement The polycarbonate plate was set up in the vicinity of the focus of object lens. The thickness of the polycarbonate plate is 5.0 mm and refractive indexes are n = 1.5. The focus of object lens from the sample surface side to the b

16、ottom side was scanned at intervals of 0.1 mm, and the reflected light of each point was acquired. The aluminum plate was set up in the polycarbonate plate bottom as a reflector. When measuring it, the state to remove the confocal pinhole to compare it with the image optics system was measured. 2.3

17、Living body blood glucose level measurement The present study was approved because of regulations of the Shinshu University ethics committee. And it won consent from the subject by the document. The relation between the amount of near-infrared absorption measurements of this system and the reference

18、 value that depended on the living body blood glucose level was examined. The measuring object was made a palmar side of the left hand thumb root. The depth of the measurement skin tissue was assumed to be 0.5 mm, 1.0 mm, 1.5 mm, and the surface. And the living body was made to stick to the window m

19、aterial of this system, and the reflection light intensity in each depth was measured. Moreover, the blood glucose level reference value was measured by the enzyme electrode method at the same time. A male in his twenties and an able-bodied person were made a subject. They were measured twice when t

20、hey were hungry, and they were measured 9 times at intervals of 5 minutes after glucose load. 1. EXPERIMENTAL RESULT1.1 Reflection light intensity through the polycarbonate plate Fig. 4 The focus depth of the confocal reflection photodetection system Fig. 4 showed the reflection light intensity in e

21、ach point from the vicinity of the surface of the polycarbonate plate to the bottom. The peak of the scanning distance about 4.8 mm is a reflected light of the sample bottom. And it was confirmed by both of the image optics system and the confocal optical system. Moreover, the reflected light on the

22、 sample surface seen in the scanning distance about 1.4 mm was able to be confirmed only in the confocal optical system. 3.2 Near-infrared absorption of a skin tissue The logarithm value and the concentration of glucose of the skin tissue reflection light intensity are assumed to show a negative cor

23、relation from the Lambert-Beer law 11. The reflection light intensity ratio on the inside and the surface of the skin tissue was used for the reflection light intensity. As a result, the fluctuation of the light intensity of the source of light is corrected. Fig. 5 showed the relation between the lo

24、garithm value and the blood glucose level reference value of the reflection light intensity ratio of each depth of 0.5 mm, 1.0 mm, and 1.5 mm. And the correlation coefficient and the standard error of each depth were shown in Table 1. Fig. 5 Near-infrared absorption of the skin tissue of each depth

25、2. DISCUSSIO4.1 The focus depth of the confocal reflection photodetection system The reflection light intensity of the scanning in each point was overall large in the image optics system. Therefore, the reflection light peak on the sample surface was not able to be confirmed（Fig. 4）. It is shown tha

26、t the reflection light intensity on the sample surface can be confirmed in the confocal optical system, and there is a depth resolution. Moreover, the distance between peaks of the reflected light of the sample surface and the bottom is about 3.4 mm. It is almost corresponding to optical distance t

27、/ n = 3.3 mm of t = 5.0 mm in thickness in refractive index n = 1.5. It was shown to be able to select the measurement depth according to the refractive index. The full width at half maximum of the peak of the reflected light in the confocal optical system is about 1mm. It can be said that the focus

28、 depth of the confocal reflection photodetection system is about 1.0 mm. Fig. 6 EGA result in relation between the reference values and the predictive values4.2 Near-infrared absorption of a skin tissue The attenuation of the logarithm value of the reflection light intensity ratio that depended on t

29、he blood glucose level was confirmed in 0.5 mm and 1.5 mm in the depth of the measurement skin tissue. The possibility of presuming the blood glucose level from the reflection light intensity ratio logarithm value was shown from the logarithm value of the reflection light intensity ratio and the cor

30、relation of the bloodglucose level. However, the attenuation of the logarithm value of the reflection light intensity ratio that depended on the blood glucose level was not able to be confirmed by the depth of 1.0 mm. It is thought that this is because a steady measurement was not able to be done be

31、cause the scattered structure of the skin tissue is organizing and it is not uniform. It will be necessary to examine the best measurement depth in detail in the future. The single regression analysis was done to the data of 1.5mm that the relation of the attenuation of the blood glucose reference v

32、alue and the reflection light intensity was good in depth. Fig. 6 showed the relation of the predictive value forecast by the reference value and the single regression analysis. And we used Error Grid Analysis (EGA). The EGA is developed a system for the evaluation of the clinical implications of pa

33、tient generated blood glucose value, which takes into account the factors. A and B zone are clinical safety. C zone is a little danger. D and E zone are danger 12. As a result of the single regression analysis, it was in the correlation with high blood glucose reference value and blood glucose forec

34、ast value. Moreover, all data was included in A and B zone in the result of EGA. The plot was distributed clinical within the effective range. Therefore, it was shown that the validity of the blood glucose level measurement by this system. And it is necessary to increase the number of measurements a

35、nd to confirm the stability of the measurement. 5. CONCLUSIONThe confocal optical system has been constructed by using the near-infrared laser, and the reflection photodetection system of the living body has been developed. The depth resolution of the system has been confirmed by measuring the polyc

36、arbonate plate. And it has been shown to be able to select the depth when the living body was measured. The possibility of presuming the blood glucose level from the reflection light intensity ratio logarithm value has been shown from the logarithm value of the reflection light intensity ratio and t

37、he correlation of the blood glucose level. And EGA plot has been built by these data. The measurement of this system has been shown an effective possibility clinical. Therefore, the possibility of measuring the blood glucose level has been shown. However, the attenuation of the logarithm value of th

38、e reflection light intensity ratio that depended on the blood glucose level according to depth has been not able to be confirmed. This is because a steady measurement was not able to be done because the scattered structure of the skin tissue is organizing and it is not uniform. It will be necessary

39、to examine the best measurement depth in detail in the future. And it is necessary to increase the number of measurements and to confirm the stability of the measurement. It is necessary to increase the number of subjects and to confirm the interindividual variation.REFERENCES1 WHO 2010 Web Site, “h

40、ttp:/www.who.int/diabetes/en/” Accessed July 18, 2010. 2 2009 International Diabetes Web Site, “http:diabetesatlas.org/content/foreword/”. Accessed July 18, 2010.3 M. R. Robinson, R. P. Eaton, D. M. Haaland, G. W. Koepp, E. V. Thomas, B. R. Stallard, and P. L. Robinson, “Noninvasive Glucose Monitori

41、ng in Diabetic Patients: A Preliminary Evaluation”, CLIN. CHEM,38-9, pp.1618-1622,1992. 4 S. Koyama, Y. Miyauchi, H. Ishizawa, “Clinical Application of Non-invasive Blood Glucose Monitoring System”, J. Illum. Engng. Inst. Jpn., vol.95, no.5, 2011. 5 S. Koyama, Y. Miyauchi, T. Horiguchi, H. Ishizawa,

42、 “Non-invasive Measurement of Blood Glucose of Diabetic Based on IR Spectroscopy”, SICE 2010, Taipei, p.3425, 3426, 2010. 6 Y. Miyauchi, T. Horiguchi, H. Ishizawa, S. Tezuka, and H. Hara, “Basis Examination for Development of Noninvasive Blood Glucose Measuring Instrument by Near-Infrared Confocal O

43、ptical System”, SICE 2010, Taipei, pp.3427-3429, 2010. 7 Y. Miyauchi, T. Horiguchi, H. Ishizawa, S. Tezuka, and H. Hara, “Near-infrared absorption measurement of biological body for the noninvasive blood glucose measuring instrument by confocal optical system”, The 49th Japanese Society for Medical

44、and Biological Engineering, FC-34-6, 2010. 8 N.Nishiyama, C. Caneau, B.Hall, G. Guryanov, M. H. Hu, X. S. Liu, M. J. Li, R. Bhat, and C. E. Zha, “Long-Wavelength Vertical-Cavity Surface-Emitting Lasers on InP With Lattice Matched AlGaAs-InP DBR Grown by MOCVD”, J. Sel. Topics Quantum Electron, 11-5,

45、 pp990-998, 2005. 9 S. Kawada, Super-resolution optics, Japan Scientific Societies Press, pp.33-52, 2005. 10 M. Hatori, Y. Aoyama, I. Kobayashi, “Optical communication engineering (1)”, CORONA Publishing co., ltd, p.19, 20, 2001. 11 Y. Ozaki and S. Kawada, Near-infrared spectroscopy, The spectroscop

46、ical society of Japan, Serial measurement method 32, Japan Scientific Societies Press, p.44, 49, 1996. 12 S. Y. Rhee, S. Chon, G. Koh, et al, “Clinical Experience of an Iontophoresis Based Glucose Measuring System”, J Korean Med Sci 2007, 22, pp.70-73, 2007. - 2689中文译文2011年年会2011年9月13日至18日，日本东京早稻田大学

47、。通过共焦反射图像检测系统来测定血糖水平Yuki Miyauchi，Takuro Horiguchi, HiroakiIshizawa, Shin-ichirou Tezuka and Hitoshi Hara 日本长野信州大学科学和技术的跨学科研究生院。(电话 : +81-268-21-5400; 邮件: f09a212shinshu-u.ac.jp)日本长野信州大学科学科学与技术研究生院。(电话 : +81-268-21-5400; 邮件: 10fa221bshinshu-u.ac.jp)日本长野信州大学纺织科学与技术学院。(电话 : +81-268-21-5400; 邮件: zawash

48、inshu-u.ac.jp)日本长野横河电机株式会社。(电话 : +81-265-85-5620; 邮件: Shin-ichirou.Tezuka)日本长野横河电机株式会社。(电话 : +81-265-85-5620; 邮件: Hitoshi.Hara)摘要：在本研究中，共焦光学系统已经通过使用近红外激光建立，并且活体反射光检测系统也已经被开发出来了。该系统可降低皮肤组织影响的一个复杂的光散射并且实现了聚焦光学系统高度精确的测量。并且推定由近红外活体吸收血糖水平的非侵入式血糖仪发展的初步实验已经完成。在这份报告中，这个系统的血糖水平测量的原则已得到证实。在活体皮肤组织的反射光强度已在确定的系统中测量，并已与血糖水平的参考价值相比。因此，血糖水平取决于反射光的吸收已经得到证实。测量血糖水平的可能性已被证明。 关键词：共焦光学系统，非侵入性，血糖，近红外。1.引言最近，糖尿病患者显著增加1，2。自我血糖监测（SMBG）是治疗糖尿病必要的和不可缺少的。然而，目前的SMBG仅仅局限于需要采集血液的测量。患者有痛苦的负荷，压力，和花销等，因