血糖检测仪中英文对照外文翻译文献

中英文资料原文:BloodGlucoseLevelMeasurementbyConfocalReflectionPhotodetectionSystemAbstract:Inthepresentstudy,theconfocalopticalsystemhasbeenconstructedbyusingthenear-infraredlaser,andthereflectionphotodetectionsystemofthelivingbodyhasbeendeveloped.Thissystemreducestheinfluenceofacomplexlightscatterbytheskintissueandachievesahighlyaccuratemeasurementbyconfocalopticalsystem.Andtheinitialexperimentforthedevelopmentofthenon-invasivebloodglucosemeterthatpresumedthebloodglucoselevelbythenear-infraredabsorptionofthelivingbodyhasbeendone.Inthisreport,theprincipleofthebloodglucoselevelmeasurementofthissystemhasbeenconfirmed.Thelightintensityofthereflectioninthelivingbodyskintissuehasbeenmeasuredintheconstructedsystem,andithasbeencomparedwiththebloodglucoselevelreferencevalue.Asaresult,theabsorptionofthereflectedlightthatdependedonthebloodglucoselevelhasbeenconfirmed.Thepossibilityofmeasuringthebloodglucoselevelhasbeenshown.Keywords:ConfocalOpticalSystem,Non-invasive,BloodGlucose,Near-infrared.1.INTRODUCTIONRecently,thediabeticincreasesremarkably[1,2].Theself-monitoringofbloodglucose(SMBG)isnecessaryandindispensabletotreatthediabetic.However,presentSMBGhasbeenlimitedtothemeasurementthatneedscollectingblood.Thepatienthasloadsofpain,stress,andcosts,etc.Therefore,thenon-invasivebloodglucosemetertobeabletomeasurethebloodglucoselevelisstronglyexpected[3-5].Inthepresentstudy,theconfocalopticalsystemhasbeenconstructedbyusingthenear-infraredlaser,andthereflectionphotodetectionsystemofthelivingbodyhasbeendeveloped.Andtheinitialexperimentforthedevelopmentofthenon-invasivebloodglucosemeterthatpresumedthebloodglucoselevelbythenear-infraredabsorptionofthelivingbodyhasbeendone.Thissystemreducestheinfluenceofacomplexlightscatterbytheskintissueandachievesahighlyaccuratemeasurementbyconfocalopticalsystem[6,7].Inthisreport,thefocusdepthbytheconfocalopticalsystemofthissystemhasbeenconfirmed.Andtheprincipleofthebloodglucoselevelmeasurementofthissystemwasconfirmed.Thelightintensityofthereflectioninthelivingbodyskintissuehasbeenmeasuredintheconstructedsystem,andithasbeencomparedwiththebloodglucoselevelreferencevalue.Asaresult,theabsorptionofthereflectedlightthatdependedonthebloodglucoselevelhasbeenconfirmed.Thepossibilityofmeasuringthebloodglucoselevelhasbeenshown.2.EXPERIMENTALMETHOD2.1MeasuringsystemFig.1showstheopticalsystemforthesystemconstructedinthepresentstudy.Anear-infraredrayVCSEL(VerticalCavitySurfaceEmittingLaser)[8]ofwavelength1.55μmwasusedforthelightsourceofthissystem,andPD(InGaAsPINphotodiode,FGA21;THORLABS)wasusedforthephotodetector.Thissystemisaconfocalopticalsystem[9]thathasthedepthresolutionandhighplaneresolution.Intensityofthereflectedlightfromthesamplesurfacesidetotheinsideofsamplecanbedetectedbymovingthewindowupanddown.ThesourceoflighthasstabilizedbytheAPC(AutoPowerControl)circuit[10].Fig.2AppearanceofthepolycarbonateplatemeasurementFig.3Appearanceofalivingbodybloodglucoselevelmeasurement2.2PolycarbonateplatemeasurementThepolycarbonateplatewassetupinthevicinityofthefocusofobjectlens.Thethicknessofthepolycarbonateplateis5.0mmandrefractiveindexesaren=1.5.Thefocusofobjectlensfromthesamplesurfacesidetothebottomsidewasscannedatintervalsof0.1mm,andthereflectedlightofeachpointwasacquired.Thealuminumplatewassetupinthepolycarbonateplatebottomasareflector.Whenmeasuringit,thestatetoremovetheconfocalpinholetocompareitwiththeimageopticssystemwasmeasured.2.3LivingbodybloodglucoselevelmeasurementThepresentstudywasapprovedbecauseofregulationsoftheShinshuUniversityethicscommittee.Anditwonconsentfromthesubjectbythedocument.Therelationbetweentheamountofnear-infraredabsorptionmeasurementsofthissystemandthereferencevaluethatdependedonthelivingbodybloodglucoselevelwasexamined.Themeasuringobjectwasmadeapalmarsideofthelefthandthumbroot.Thedepthofthemeasurementskintissuewasassumedtobe0.5mm,1.0mm,1.5mm,andthesurface.Andthelivingbodywasmadetosticktothewindowmaterialofthissystem,andthereflectionlightintensityineachdepthwasmeasured.Moreover,thebloodglucoselevelreferencevaluewasmeasuredbytheenzymeelectrodemethodatthesametime.Amaleinhistwentiesandanable-bodiedpersonweremadeasubject.Theyweremeasuredtwicewhentheywerehungry,andtheyweremeasured9timesatintervalsof5minutesafterglucoseload.EXPERIMENTALRESULTReflectionlightintensitythroughthepolycarbonateplateFig.4ThefocusdepthoftheconfocalreflectionphotodetectionsystemFig.4showedthereflectionlightintensityineachpointfromthevicinityofthesurfaceofthepolycarbonateplatetothebottom.Thepeakofthescanningdistanceabout4.8mmisareflectedlightofthesamplebottom.Anditwasconfirmedbybothoftheimageopticssystemandtheconfocalopticalsystem.Moreover,thereflectedlightonthesamplesurfaceseeninthescanningdistanceabout1.4mmwasabletobeconfirmedonlyintheconfocalopticalsystem.3.2Near-infraredabsorptionofaskintissueThelogarithmvalueandtheconcentrationofglucoseoftheskintissuereflectionlightintensityareassumedtoshowanegativecorrelationfromtheLambert-Beerlaw[11].Thereflectionlightintensityratioontheinsideandthesurfaceoftheskintissuewasusedforthereflectionlightintensity.Asaresult,thefluctuationofthelightintensityofthesourceoflightiscorrected.Fig.5showedtherelationbetweenthelogarithmvalueandthebloodglucoselevelreferencevalueofthereflectionlightintensityratioofeachdepthof0.5mm,1.0mm,and1.5mm.AndthecorrelationcoefficientandthestandarderrorofeachdepthwereshowninTable1.Fig.5Near-infraredabsorptionoftheskintissueofeachdepthDISCUSSIO4.1ThefocusdepthoftheconfocalreflectionphotodetectionsystemThereflectionlightintensityofthescanningineachpointwasoveralllargeintheimageopticssystem.Therefore,thereflectionlightpeakonthesamplesurfacewasnotabletobeconfirmed（Fig.4）.Itisshownthatthereflectionlightintensityonthesamplesurfacecanbeconfirmedintheconfocalopticalsystem,andthereisadepthresolution.Moreover,thedistancebetweenpeaksofthereflectedlightofthesamplesurfaceandthebottomisabout3.4mm.Itisalmostcorrespondingtoopticaldistancet/n=3.3mmoft=5.0mminthicknessinrefractiveindexn=1.5.Itwasshowntobeabletoselectthemeasurementdepthaccordingtotherefractiveindex.Thefullwidthathalfmaximumofthepeakofthereflectedlightintheconfocalopticalsystemisabout1mm.Itcanbesaidthatthefocusdepthoftheconfocalreflectionphotodetectionsystemisabout1.0mm.Fig.6EGAresultinrelationbetweenthereferencevaluesandthepredictivevalues4.2Near-infraredabsorptionofaskintissueTheattenuationofthelogarithmvalueofthereflectionlightintensityratiothatdependedonthebloodglucoselevelwasconfirmedin0.5mmand1.5mminthedepthofthemeasurementskintissue.Thepossibilityofpresumingthebloodglucoselevelfromthereflectionlightintensityratiologarithmvaluewasshownfromthelogarithmvalueofthereflectionlightintensityratioandthecorrelationofthebloodglucoselevel.However,theattenuationofthelogarithmvalueofthereflectionlightintensityratiothatdependedonthebloodglucoselevelwasnotabletobeconfirmedbythedepthof1.0mm.Itisthoughtthatthisisbecauseasteadymeasurementwasnotabletobedonebecausethescatteredstructureoftheskintissueisorganizinganditisnotuniform.Itwillbenecessarytoexaminethebestmeasurementdepthindetailinthefuture.Thesingleregressionanalysiswasdonetothedataof1.5mmthattherelationoftheattenuationofthebloodglucosereferencevalueandthereflectionlightintensitywasgoodindepth.Fig.6showedtherelationofthepredictivevalueforecastbythereferencevalueandthesingleregressionanalysis.AndweusedErrorGridAnalysis(EGA).TheEGAisdevelopedasystemfortheevaluationoftheclinicalimplicationsofpatientgeneratedbloodglucosevalue,whichtakesintoaccountthefactors.AandBzoneareclinicalsafety.Czoneisalittledanger.DandEzonearedanger[12].Asaresultofthesingleregressionanalysis,itwasinthecorrelationwithhighbloodglucosereferencevalueandbloodglucoseforecastvalue.Moreover,alldatawasincludedinAandBzoneintheresultofEGA.Theplotwasdistributedclinicalwithintheeffectiverange.Therefore,itwasshownthatthevalidityofthebloodglucoselevelmeasurementbythissystem.Anditisnecessarytoincreasethenumberofmeasurementsandtoconfirmthestabilityofthemeasurement.5.CONCLUSIONTheconfocalopticalsystemhasbeenconstructedbyusingthenear-infraredlaser,andthereflectionphotodetectionsystemofthelivingbodyhasbeendeveloped.Thedepthresolutionofthesystemhasbeenconfirmedbymeasuringthepolycarbonateplate.Andithasbeenshowntobeabletoselectthedepthwhenthelivingbodywasmeasured.Thepossibilityofpresumingthebloodglucoselevelfromthereflectionlightintensityratiologarithmvaluehasbeenshownfromthelogarithmvalueofthereflectionlightintensityratioandthecorrelationofthebloodglucoselevel.AndEGAplothasbeenbuiltbythesedata.Themeasurementofthissystemhasbeenshownaneffectivepossibilityclinical.Therefore,thepossibilityofmeasuringthebloodglucoselevelhasbeenshown.However,theattenuationofthelogarithmvalueofthereflectionlightintensityratiothatdependedonthebloodglucoselevelaccordingtodepthhasbeennotabletobeconfirmed.Thisisbecauseasteadymeasurementwasnotabletobedonebecausethescatteredstructureoftheskintissueisorganizinganditisnotuniform.Itwillbenecessarytoexaminethebestmeasurementdepthindetailinthefuture.Anditisnecessarytoincreasethenumberofmeasurementsandtoconfirmthestabilityofthemeasurement.Itisnecessarytoincreasethenumberofsubjectsandtoconfirmtheinterindividualvariation.REFERENCES[1]S.Y.Rhee,S.Chon,G.Koh,etal,“ClinicalExperienceofanIontophoresisBasedGlucoseMeasuringSystem”,JKoreanMedSci2007,22,pp.70-73,2007.[2]2009InternationalDiabetesWebSite,“http:/content/foreword/”.[AccessedJuly18,2010].[3]M.R.Robinson,R.P.Eaton,D.M.Haaland,G.W.Koepp,E.V.Thomas,B.R.Stallard,andP.L.Robinson,“NoninvasiveGlucoseMonitoringinDiabeticPatients:APreliminaryEvaluation”,CLIN.CHEM,38-9,pp.1618-1622,1992.[4]S.Koyama,Y.Miyauchi,H.Ishizawa,“ClinicalApplicationofNon-invasiveBloodGlucoseMonitoringSystem”,J.Illum.Engng.Inst.Jpn.,vol.95,no.5,2011.[5]S.Koyama,Y.Miyauchi,T.Horiguchi,H.Ishizawa,“Non-invasiveMeasurementofBloodGlucoseofDiabeticBasedonIRSpectroscopy”,SICE2010,Taipei,p.3425,3426,2010.[6]Y.Miyauchi,T.Horiguchi,H.Ishizawa,S.Tezuka,andH.Hara,“BasisExaminationforDevelopmentofNoninvasiveBloodGlucoseMeasuringInstrumentbyNear-InfraredConfocalOpticalSystem”,SICE2010,Taipei,pp.3427-3429,2010.[7]Y.Miyauchi,T.Horiguchi,H.Ishizawa,S.Tezuka,andH.Hara,“Near-infraredabsorptionmeasurementofbiologicalbodyforthenoninvasivebloodglucosemeasuringinstrumentbyconfocalopticalsystem”,The49thJapaneseSocietyforMedicalandBiologicalEngineering,FC-34-6,2010.[8]N.Nishiyama,C.Caneau,B.Hall,G.Guryanov,M.H.Hu,X.S.Liu,M.J.Li,R.Bhat,andC.E.Zha,“Long-WavelengthVertical-CavitySurface-EmittingLasersonInPWithLatticeMatchedAlGaAs-InPDBRGrownbyMOCVD”,J.Sel.TopicsQuantumElectron,11-5,pp990-998,2005.[9]S.Kawada,"Super-resolutionoptics",JapanScientificSocietiesPress,pp.33-52,2005.[10]M.Hatori,Y.Aoyama,I.Kobayashi,“Opticalcommunicationengineering(1)”,CORONAPublishingco.,ltd,p.19,20,2001.[11]Y.OzakiandS.Kawada,"Near-infraredspectroscopy,ThespectroscopicalsocietyofJapan,Serialmeasurementmethod32",JapanScientificSocietiesPress,p.44,49,1996.译文:通过共焦反射图像检测系统来测定血糖水平摘要：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，因此，能够测量血糖水平的非侵入性血糖仪被寄予强烈厚望[3-5]在本研究中，使用近红外激光共焦光学系统已经建立，活体的反射光检测系统也已经被开发。并且推定血糖水平的近红外吸收的活体的非侵入式血糖仪发展的初步实验已经完成。该系统减少了一个复杂的散射光对皮肤组织的影响，，通过聚焦光学系统[6,7]实现高度精确的测量。在这份报告中，共焦光学系统的焦深已得到证实。并且本系统的血糖水平测量的原则得到了确认。在活体皮肤组织的反射光强度已在建造的系统中得到测量，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也已被证明。2.实验方法2.1测量系统图图1显示了在本研究构建了系统的光学系统。一个波长为1.55微米的近红外光的VCSEL（垂直腔表面发射激光器）[8]用作该系统的光源，PD（砷化铟镓的PIN光电二极管，FGA21;THORLABS）用作光电探测器。这个系统是一个有深入解析和高度分辨率的聚焦的光学系统[9]。向上和向下移动窗口，可以检测从样品表面侧到样品内的反射光强度。由于使用的APC（自动功率控制）电路[10]，因此光源很稳定。图1光学聚焦系统示意图2.2聚碳酸酯板测量聚碳酸酯板成立于物镜的焦点附近。聚碳酸酯板的厚度为5.0毫米，折射率n=1.5。物镜的焦点从样品表面侧的底部扫描间隔为0.1毫米，每一个点的反射光都已经测得。铝板作为一个反射器，位于聚碳酸酯板底部。测量时，消除共焦针孔的状态是为了和影像光学系统作比较。图2聚碳酸酯板测量示意图2.3生物体内的血糖水平测量本研究由于符合信州大学伦理委员会的法规，所以被批准了，并且此研究得到了主题文档的准许。本系统的近红外吸收测量量和参考价值之间的关系取决于生物体内的血糖水平已经得到检验。测量对象是左手拇指根部旁边的手掌。被测量的皮肤组织的深度被假定为0.5毫米，1.0毫米，1.5毫米，以及表面。生物体被要求坚持本系统的窗口材料，测量每个深度的反射光强度。此外，与此同时用酶电极法测定血糖水平的参考价值，对一个二十多岁的男性和一个身强力壮的人的作了一个课题。在他们处于饥饿的时候测量两次，他们在血糖浓度偏高时每隔5分钟测量一次，如此测量9次。图3生物体内的血糖水平测量示意图3.实验结果3.1通过聚碳酸酯板的反射光的强度图4显示了从聚碳酸酯板表面附近到底部的每个点的反射光强度。扫描距离约4.8毫米的高峰是一个样品底部的反射光。别且它通过图像的光学系统和光学聚焦系统得到了证实。此外，约1.4毫米的扫描距离样品表面的反射光，只有通过共焦光学系统才能得到证实。图4共焦反射光检测系统的焦深3.2近红外吸收皮肤组织郎伯-比尔定律[11]假定皮肤组织反射光强度的对数值和的血糖浓度呈负相关。皮肤组织内部与表面的反射光强度比被用来衡量反射光的强度。因此，纠正了光源的光强波动。图5显示了对数值与深度为0.5毫米，1.0毫米和1.5毫米的反射光强度比的血糖水平参考价值之间的关系。表一显示了各深度的相关系数和标准偏差。图5各深度的皮肤组织的近红外吸收表1各深度的相关系数和标准偏差4.讨论4.1焦点深度的聚焦反射光电探测系统在光学系统中反射光的强度在每个点扫描图像中整体偏大。因此，对样品表面的反射光峰是不是能够得到证实的（图4）。结果表明，样品表面的反射光强度可以在共焦光学系统得以证实，并可以得到深入的解析。此外，样品表面和底部的反射光峰之间的距离大约是3.4毫米。这几乎是对应的光学距T/N=3.3，厚度T=5.0毫米，折射率n=1.5毫米。这说明可以根据折射率来选择测量深度。在共焦光学系统中反射光在半峰高处的最大峰宽为1mm左右。可以说，聚焦反射光检测系统的焦深约为1.0毫米。4.2皮肤组织的近红外吸收取决于血糖浓度的反射光强度比的对数值的衰减，在皮肤组织深度为0.5毫米和1.5毫米处的测量中得到了证实。假定反射光强度比值的对数值中血糖水平可能是从反射光的强度比的对数值和血糖水平的相关性表现出来的。然而，取决于血糖浓度的反射光强度比的对数值的衰减，不能在皮肤组织深度为1.0毫米处的测量中得到证实。人们认为，由于皮肤组织是分散的、不统一的结构组织，因此不能够做稳定的测量。对最好的测量深度进行更详细的研究是未来必须要做的工作。在深度为1.5mm处，对血糖的参考价值的衰减和反射光强度的数据进行单回归分析，发现它们相关性很好。图6显示的是通过参考价值和单一的回归分析进行与猜测的预测值的关系。我们用错误网格分析（EGA）。EGA被发展成一个评估临床上血糖浓度值影响因素的系统，血糖浓度值影响因素是需要考虑的因素。A和B区，在临床是安全的。C区就有一点危险了。D和E区就很危险了[12]。作为单回归分析的结果，它呈现了高血糖的参考价值与血糖的预测值的相关性。此外，在EGA中，所有数据都被包含在A和B区。这些情况都分布在临床有效范围内。因此，这表明，通过这个体统对血糖水平的测量是有效的。并且提高测量的数量来确认测量的稳定性是必须的。5.结论共焦光学系统已通过近红外激光建成，活体的反射光检测系统也已经开发出来了。对该系统的深度解析也已经通过对聚碳酸酯板的测量得到确证。当进行活体测定时，我们也能够选择深度。假定反射光强度比值的对数值中血糖水平可能是从反射光的强度比的对数值和血糖水平的相关性表现出来的。EGA的各种情况也已通过这些数据建成。该系统额测量也是具有临床有效的可能性的。因此，我们得到了测量血糖水平的可能性。然而，取决于依据深度的血糖浓度水平的反射光强度比的对数值的衰减一直无法得到证实。由于皮肤组织是分散的、不统一的结构组织，因此不能够做稳定的测量。对最好的测量深度进行更详细的研究是未来必须要做的工作。提高测量的数量来确认测量的稳定性也是必须的。增加课题数量和确认个体差异也是未来必须要做的工作。参考文献：[1]S.Y.Rhee,S.Chon,G.Koh,etal,“ClinicalExperienceofanIontophoresisBasedGlucoseMeasuringSystem”,JKoreanMedSci2007,22,pp.70-73,2007.[2]2009InternationalDiabetesWebSite,“http:/content/foreword/”.[Accessed