[雙語翻譯]外文翻譯--通過共焦反射圖像檢測系統(tǒng)來測定血糖水平（英文）

1、Blood Glucose Level Measurement by Confocal Reflection Photodetection System Yuki Miyauchi1，Takuro Horiguchi2, Hiroaki Ishizawa3, Shin-ichirou Tezuka4 and Hitoshi Hara5 1Interdisciplinary Graduate School of Science and T

2、echnology, Shinshu University, Nagano, Japan (Tel : +81-268-21-5400; E-mail: f09a212@shinshu-u.ac.jp) 2Graduate School of Science and Technology, Shinshu University, Nagano, Japan (Tel : +81-268-21-5400; E-mail: 10fa2

3、21b@shinshu-u.ac.jp) 3Faculty of Textile Science and Technology, Shinshu University, Nagano, Japan (Tel : +81-268-21-5400; E-mail: zawa@shinshu-u.ac.jp) 4 Yokogawa Electric Corporation, Nagano, Japan (Tel : +81-265-8

4、5-5620; E-mail: Shin-ichirou.Tezuka@jp.yokogawa.com) 5 Yokogawa Electric Corporation, Nagano, Japan (Tel : +81-265-85-5620; E-mail: Hitoshi.Hara@jp.yokogawa.com) Abstract: In the present study, the confocal optical sys

5、tem 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

6、 and achieves a highly accurate measurement by confocal optical system. And the initial experiment for the development of the non-invasive blood glucose meter that presumed the blood glucose level by the near-infrared a

7、bsorption of the living body has been done. In this report, the principle of the blood glucose level measurement of this system has been confirmed. The light intensity of the reflection in the living body skin tissue ha

8、s 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 con

9、firmed. The 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,

10、 2]. The self-monitoring of blood glucose (SMBG) is necessary and indispensable to treat the diabetic. However, present SMBG has been limited to the measurement that needs collecting blood. The patient has loads of

11、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 confocal optical system has been const

12、ructed 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 pre

13、sumed the blood glucose level by the near-infrared 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 measureme

14、nt by confocal optical system [6, 7]. In this report, the focus depth by the confocal optical system of this system has been confirmed. And the principle of the blood glucose level measurement of this system was conf

15、irmed. 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 absorpt

16、ion 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 METHOD 2.1 Measuring system Fig. 1 shows th

17、e optical system for the system constructed in the present study. A near-infrared ray VCSEL (Vertical Cavity Surface Emitting Laser) [8] of wavelength 1.55 μm was used for the light source of this system, and PD (InG

18、aAs 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. Intensity of the reflected light from the sa

19、mple 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]. Beam splitterVCSELPDConfocal detection pin

20、holeObjective lensWindowImaging lensCollimating lensPDAuto power control circuit Beam splitterVCSELPDConfocal detection pinholeObjective lensWindowImaging lensCollimating lensPDAuto power control circuitFig. 1 The s

21、chematic view of the optical confocal system SICE Annual Conference 2011 September 13-18, 2011, Waseda University, Tokyo, JapanPR0001/11/0000-2686 ¥400 © 2011 SICE - 2686 --2.1-1.7-1.3-0.9-0.50 100 200 300Bloo

22、d glucose reference value (mg/dL)Log reflection light .intensity ratio0.5 mm 1.0 mm 1.5 mmFig. 5 Near-infrared absorption of the skin tissue of each depth Table1 Correlation coefficient and standard error of each depth

23、 Depth Correlation coefficient Standard error 0.5 mm -0.86 30 mg/dL 1.0 mm 0.44 50 mg/dL 1.5 mm -0.89 30 mg/dL4. DISCUSSION 4.1 The focus depth of the confocal reflection photodetection system The reflection light inte

24、nsity 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 that the reflection light

25、 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 a

26、bout 3.4 mm. It is almost corresponding to optical distance t / 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 i

27、ndex. 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 depth of the confocal reflection photodetection system is about 1.0 m

28、m. 4.2 Near-infrared absorption of a skin tissue The attenuation of the logarithm value of the reflection light intensity ratio that depended on the blood glucose level was confirmed in 0.5 mm and 1.5 mm in the depth

29、 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 rat

30、io and the correlation of the blood 01002003000 100 200 300 Blood glucose reference value (mg/dL)Blood glucose estimated value (mg/dL) ABBCCAD DEE01002003000 100 200 300 Blood glucose reference value (mg/dL)Blood glu

31、cose estimated value (mg/dL) ABBCCAD DEEFig. 6 EGA result in relation between the reference values and the predictive values glucose level. However, the attenuation of the logarithm value of the reflection light inten

32、sity 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 because the scattered structure

33、 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 rela

34、tion of the attenuation of the blood glucose reference value 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 reg

35、ression analysis. And we used Error Grid Analysis (EGA). The EGA is developed a system for the evaluation of the clinical implications of patient generated blood glucose value, which takes into account the factors. A

36、 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 glu

37、cose forecast 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

38、level measurement by this system. And it is necessary to increase the number of measurements and to confirm the stability of the measurement. 5. CONCLUSION The confocal optical system has been constructed by using the