CN1119410A - 路径长度被校正的血氧测定计 - Google Patents
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Abstract
用于细胞组织检测的一种路径长度被校正的分光光度计包括一振荡器(10),用以产生所选频率的载波波形;LED光源(22a-22c)用以产生所选波长的光,其强度由所选频率调制且被输入到一被测物体;光敏二极管(22a-22c)用以检测已入进到被测物细胞组织的光。该分光光度计通过测定光子入进路径的平均长度来确定被测细胞时上的生理特性。
Description
本发明涉及针对具体被测区细胞组织的自然条件下检验的一种适于穿着的细胞组织分光光度计。
连续波(CW)血氧测定计已被广泛地用于在生物细胞组织中确定一个光吸收色料(例如血红素、氧化血红素)的体内的浓度。这种连续波血氧测定计测量连续光在细胞组织中的衰减,并根据比尔·莱姆伯特(Beer Lambert)公式或修正的比尔莱姆伯特吸收公式来测定浓度。该比尔·莱姆伯特公式(1)描述了在吸收分量(C),吸光系数(ε),光子入进路径长度<L>和衰减光强度(I/I0)之间的关系。 CW分光光度技术不能同时确定ε、C和<L>。若假设经全部被测物的光子的路径长度均属恒定不变且均匀,那就可能采用CW血氧测定计来直接量化被分量的浓度(C)。
在细胞组织中,光子入进路径长度随着由该CW血氧测定计所检测的内部细胞组织的大小、结构及生理特性而发生变化。举例而言,在人脑中的灰、白物质及其结构因人而异。此外,光子入进路径长度本身还是吸收分量的相对浓度的一个函数。结果是,经过具有高血红素浓度的某一器官的路径长度将不同于具有低血红素浓度的同一器管的路长。此外,由于许多细胞组织成分的光吸收系数是与波长相关的,所以路径长度常常取决于光的波长。因此,当在细胞组织中进行血红素浓度量化时,最好是可能直接测量该路径长度。
本发明的一个方面是一种路径长度被校正的血氧测定计,它采用了连续波分光学以及相位调制分光学的原理,这种血氧测定计在结构上是紧凑的,可被长期动态地附着于被测体上。这种血氧测定计还适于用作当进行外科手术或与外科创伤相关状态情形中的手术室急救设施的细胞组织的监测。
这种血氧测定计被安装在与皮肤接触的一种与体形相适的支撑结构之上。该支撑结构封装有若干个发光二极管(LED)以产生入射到被测细胞组织内的不同波长的光,还封装有若干个光敏二极管检测器,带有针对波长内容检测的干涉滤波器。由于该LED和光敏二极管都直接置于皮肤之上,因此就不需用光纤。LED和光敏二极管之间距离的选择要使之适于检测一个被测细胞组织区域。该支撑结构还包括一个合适的阻挡层,放置在这些LED和这些二极管检测器之间,用以减少从光源到检测器的皮下入进光的检测。该支撑结构还可以进一步包括用于防止光子逃逸的装置,防止光子从皮肤逃逸而不被检测;这种光子逃逸防止装置被置于这些LED和光敏二极管检测器的周围。
该些LED、二极管检测器和血氧测定计的电子控制电路由一个适于携带的电池组供电,或由50/60HE标准市电供电。该电子电路包括有用于电源及检测器直接操作以及指导数据查询及处理的处理器。数据可被显示在由用户携带的读出装置上,或由遥测装置送到远端位置,或由存储器在其内累积供以后使用。
这种血氧测定计适于用来测量从光源到检测器的光的衰减度,以及用于确定光的平均入进路长。这一入进路长及其强度衰减数据再被用于细胞组织的特性的直接量化。
另一方面,本发明是通过测量光子入进路径的平均长度以实现细胞组织检测的一种分光光度计,它包括一个用于产生所选频率的载波的振荡器,在从光的输入端口到光的检测端口的路径上,该所选频率可以与在细胞组织内光子散射的平均入进时间相比较;一个光源,可操作地与振荡器相连接,用所产生所选波长的光,其强度是以该频率调制,并在输入端口被引入到被测物内;一个光敏二极管检测器,用以在检测端口处检测处于输入和输出端口间的被测物的细胞组织中已经入进的所选波长的光;一个相位检测器,可操作地连接以接收来自振荡器和二极管检测器信号,用以测量在所引入的及所检测到的光之间的相位移;以及一个处理器,用以根据其相移来计算路径长度,并根据该路径长度来确定所检测的细胞组织的生理特性。
另一方面,本发明是通过测定光子入进路径的平均长度以实现细胞组织检测的一种分光光度计,它包括一个用于产生所选频率的载波的振荡器,在从光的输入端口到光的检测端口的路径上,该所选频率可以与在细胞组织内光子散射的平均入进时间相比较;一个光源,可操作地与振荡器相连接,用以产生所选波长的光,其强度是以该频率调制,并在输入端口被引入到被测物内;一个光敏二极管检测器,用以在检测端口检测处于输入和输出端口间的被测物的细胞组织中已经入进的所选波长的光;一个分相器,用以根据载波波形来产生预定的实际不同相位的第一和第二基准相位信号;第一和第二双平衡混频器,用以使基准相位信号和被检测的辐射的信号相关联,以便从此分别地产生一个实际的输出信号和镜象输出信号;以及一个处理器,用以根据该实际的输出信号和该镜象输出信号来计算所引入的光和所检测的光之间的相位移,并根据相位移确定被检测的细胞组织的生理特性。
另一方面,本发明是通过测定光子入进的路径的平均长度来实现细胞组织检测的一种分光光度计,它包括一个用于产生第一所选频率的载波的第一振荡器,在从光的输入端口到光的检测端口的路径上,该所选频率可以与在细胞组织内光子散射的平均入进时间相比较;一个光源,可操作地与该振荡器相连接,用以产生所选波长的光,其强度是以该第一频率调制,并在输入端口被引入到被测物内;一个光敏二极管检测器,用以在检测端口检测位于输入和检测端口之间的被测物的细胞组织中已入进的所选波长的光,对应于该被检测的光,该检测器以该第一频率产生一个检测信号;一个第二振荡器,用以产生一个第二频率的载波,该第二频率从第一频率偏移104Hz的数量级;一个基准混频器,与第一和第二振荡器相连接,用于产生频率大致等于该第一和第二频率之差的一个基准信号;一个混频器,连接来接收第二振荡器信号和检测信号,并用以将该检测信号变换成差频;一个相位检测器,操作地连接来接收基准混频器的信号和被变换的检测信号,用以测量所引入光和所检测光之间的相位移;以及一个处理器,用以根据该相位移来计算路径长度,并根据该路径长度来确定被检测细胞组织的生理特性。
这些方面的最佳实施例可以包括下述特征之一或多个。
该分光光度计可进一步包括一个幅值检测器上,连接到光敏二极管检测器上,用以测量被检测光的幅值,并且该处理器还用以接收该幅值,以进行生理特性的确定。
该分光光度计可进一步包括一个低频血氧测定计电路,可切换地与信号源和光敏二极管相连接,用以确定在该波长的光的吸收特性;并且该处理器还用以从该血氧测定计电路接收该吸收值,以进行生理特性的确定。
该分光光度计可进一步包括两个自动增益控制器,用以均衡(level)对应于所引入光和所检测光的信号,两个被均衡的信号均被送入相位检测器。
该光敏二极管检测器可进一步包括一个实际单一波长滤波器。
该分光光度计可进一步包括一个第二光源,可操作地接到振荡器,用以产生第二所选波长的光,其强度以第一频率调制,其辐射在一个第二端口被引入到被测物;在检测端口,该光敏二极管检测器还可交替地用以检测已经入射进处在第一及第二输入端口和该检测端口之间的被测物的细胞组织的第一和第二波长的光;该相位检测器进一步被用以交替地接收对应于被检测的第一和第二波长的信号,并且该处理器被进一步用以交替地从相位移检测器接收相位移,这些相位移被随后用于该细胞组织的生理特性的确定。
该分光光度计可进一步包括一个第二光源,可操作地接到振荡器,用以产生第二所选波长的光,其强度以第一频率调制,其辐射在一个第二输入端口被引入到被测物;在一个第二检测端口,一个第二光敏二极管检测器用以分别检测已经入射进位于第二输入端口和第二检测端口之间的被测物的细胞组织的第二波长的光;一个第二相位检测器,可操作地连接来接收一个基准信号和来自第三二极管检测器的一个检测信号,用以测量的第二波长的所引入的和所检测的光之间的相位移;并且该处理器进一步用于接收第二波长上的一个第二相位移,该第一和第二相位移被随之用于该细胞组织的生理特性的确定。
这两种波长分光光度计可进一步包括一个第三光源,可操作地接到振荡器上,用以产生第三所选波长的光,其强度以第一频率调制,其辐射在一个第三输入端口被引入到被测物;在一个第三检测端口,一个第三光敏二极管检测器用以分别检测已经入射进位于第三输入端口和第三检测端口之间的被测物的细胞组织的第三波长的光;一个第三相位检测器,可操作地连接来接收一个基准信号和来自第三二极管检测器的一个检测信号,用以测量以第三波长所引入的和所检测的光之间的相位移;并且该处理器进一步用于接收该相位检测器的相位移,该第一、第二和第三相位移被随后用于该细胞组织的生理特性的确定。
这种两个或三个波长的分光光度计可进一步包括第一、第二(或第三)幅值检测器,分别连接到该第一、第二(或第三)光敏二极管,该幅值检测器被用以测量以每一种波长检测到光的幅度;并且该处理器进一步用以接收这些幅度,以确定被测细胞组织的生理特性。
所述光源可以是一种发光二极管,以产生可见的或红外范围内的所选波长的光。
所检光敏二极管检测器可以是一个PIN二极管或一个雪崩二极管。
被测的细胞组织的生理特性可以是血红素氧化性肌内的铁蛋白、细胞色素的铁和铜量、黑色素、葡萄糖或其它指标。
图1是根据本发明的路径长度被校正的血氧测定计的方框图。
图2是用在图1的血氧测定计中的50.1MHz(50.125MHz)的示意电路图。
图3是使用在图1中的血氧测定计的一个PIN二极管和一个放大器的电路示意图。
图4是使用在图1中的血氧测定计的一个幅值检测器的电路示意图。
图5是使用在图1中的血氧测定计的25KHz滤波器的电路示意图。
图6是图1的血氧测定计中的AGC电路示意图。
图7是图1的血氧测定计的相位检测器电路示意图。
图8A是该血氧测定计的一个光源—检测器探测器的示意图。
图8B是沿图8A中的线8B而取的横断面图,进一步反映其光子的入进情况。
路径长度被校正的血氧测定计的一个最佳实施例采用了三个LED来产生三种所选波长的光,其强度由一个50.1MHz的频率所调制并被直接耦合到被测细胞组织。在每一个波长上,被引入的光可由细胞组织所改变并由紧靠在皮肤上的宽域光敏二极管所检测。将所引入的和所检测到的辐射作比较从而确定它们的相对相移,该相移对应于光子入进路径的平均长度,并由此确定该光的衰减性。
参见图1,该血氧测定计有一个工作于50.1MHz的主振荡器10,它被接到功率放大器15,其具有足够的输出功率以驱动分别辐射具有760nm、840nm和905nm(或950nm)波长的光的LED22a、22b和22c(例如日立公司产的HLP20RG或HLP40RG)。一个第二本振14工作于50.125MHz,且混频器12用以产生25KHz的基准频率13。直接置于皮肤上的每一个LED都具有一个合适的散热片,以消除可能会改变该周边细胞组织因充血产生的不适的增温。三个PIN二极管检测器24a、24b和24c放置距这些LED50cm之外,并且有约1cm2的检测面积。那些入进进到细胞组织几个厘米深的光子被分别的PIN二极管所检测到。光源——检测器的距离可被增加或减小,以捕捉更深或更浅的入进光子。来自PIN二极管24a、24b和24c的信号分别由预放大器30a、30b和30c放大。
放大的信号(32a、32b、32c)分别送到幅值检测器36a、36b和36c以及混频器40a、40b和40c。幅值检测器用于确定将被用于公式1中的每一波长光所检测信号的强度值。连接来从本振14接收50.125MHz基准信号(41a、41b和41c)的每一个混频器将检测信号转换为25KHz的频率信号(42a、42b、42c)。这些混频器是高动态范围的混频器(例如市售的SRA—1H)。检测信号(42a、42b、42c)由滤波器45a、45b和45c分别滤波。
相位检测器60a、60b和60c被用于确定每一波长光的输入的信号和检测信号间的相位移。每一个相位检测器接收该25KHz的检测信号(54a、54b、54c)以及该25KHz的基准信号(56a、56b、56c),这两个信号都被自动增益控制电路50和52所自动均衡,以覆盖信号变化的动态范围。相位检测器60a、60b和60c产生对应于每一波长光子入进延时的相位移信号(62a、62b、62c)。每个相位移信号都正比于由处理器所执行的用于计算程序中的光子入进路径长度。
图2示出了用作50.1MHz主振荡器10和50.125MHz的本振14的电路示意图。该晶振被中性化以工作在基础的谐振状态,从而实现长期稳定性。所有的振荡器均被热耦合,以使所一旦出现频率漂移,它们的频率差被恒定保持在25KHz。
如图3所示,PIN二极管24a、24b和24c都分别与各自的预放大器30a、30b和30c连接。该血氧测定计采用的PIN硅光敏二极管S1723—04具有10mm×10mm的敏感区域,并且在320nm至1060nm范围内的光谱响应,检测信号由放大级29和31所放大,每一级都提供约20dB的放大量。NE5205N运算放大器以+8V供电,以工作在高增益域内。该8V信号由电位器33所提供。放大的检测信号(32a、32b和32c)被送到幅值检测器36a、36b和36c(图4)。其幅值(37a、37b、37c)被送到处理器70,该处理器由此按公式(1)计算光的衰减率或其对数。
参见图5,AGC电路使用的是MC1305集成电路以实现放大操作,该放大操作应保持相位检测器60的输入信号位于恒定电平。对于AGC电路50和52而言,其增益量被选成相等。信号的幅值由反馈网络53所控制。这种AGC提供了被检测的信号和基准信号的实质上的恒定值,以消除由于相位检测器中幅值与相位间的串扰而引起的被检相位移中的变异。
参考图6,每一个相位检测器包括有施密特触发器,它将实际上为正弦波的检测信号(54a、54b、54c)和基准信号(57a、56b、56c)转变成方波。该方波被送入到有互补MOS硅栅极晶体管的检测器中。该相位移信号被送到处理器70。
这种血氧测定计的校准是通过在一已知介质中的选定距离上,即利用一标准延时单元来测量相移,并通过转变连接器导线的长度来改变主振荡器10和本振14之间的电延时来完成的。
参考图8A和8B,光源—检测器探测装置20包括有安装在一个身体相适支撑构造21当中的选定波长的若干个LED(22a、22b、22c)和PIN光敏二极管(24a、24b、24c)。构造21还包括光子逃逸阻挡层27,它由选定散射和吸收特性的材料(如泡沫聚苯乙稀)构成,用以将逃逸光子反回到被测细胞组织。该支撑构造还包括第二个相适的阻挡层28,它置于LED和二极管检测器之间,用以吸收从光源到检测器直接传播的光子,从而防止了皮下入进光子的检测。支撑构造21还包括由一个电屏蔽层21a所封闭的电子电路29。
每一个PIN二极管还具有一蒸敷的单一波长薄膜滤波器(25a、25b、25c)。这种滤波器消除了不同波长信号的串扰,并能使三个光源连续地操作,即不需要时间共享。
与使用在一般的相位调制系统中的光电倍增管相比,采用光敏二极管检测器具有实际的优点。光敏二极管被直接置于皮肤之上,即不需用光纤。而且,不需使用对于光电倍增管必须的高压供电。这种光敏二极管要小得多且容易置于紧靠皮肤。光电倍增管的长处是很大的倍增增益且具有在该倍增器上直接混频的可能性,这一点对于光敏二极管来说是不及的。本发明预见到使用若干种不同的光敏二极管,例如PIN二极管,雪崩二极管以及其它二极管。
处理器使用的算法是根据由E.M.Sevick等人在1991年4月15日出版的“分析生物化学”195期330页上的“用于细胞组织氧化度确定的时间与频率分解度光谱的量化”一文中的所描述的公式。在此将该全文引作参考。
在每一个波长,相位移(θλ)(62a、62b、62c)被用来在下式中计算路径长度: 其中f是范围在10MHz到100MHz范围内的引入光的调制频率;tλ是光子入进延时时间;C是在散射介质中光子的速度;而Lλ是光子入进路径长度。
等式(2)在低调制频率,即2πf<<μαC时有效。由于LED和光敏二极管的频率局限性,选择了50MHz的调制频率。然而,对于更快的LED和光敏二极管,可以设想使用更高的调制频率以增加相位移。在高的调制频率,即2πf>>μα·C,相位移不再正比于飞行平均时间(t) 其中ρ是光源——检测器间距;(1—g)μs是有效散射系数;f是调制频率而μα λ是在波长λ处的吸收系数。
在两个波长处,吸收系数的比例由下式确定: 其中θo λ代表背景散射和吸收。
所述波长是在可见和红外光范围内,并被选择使其对于各种细胞组织成分且有吸收敏感性(或不敏感性),例如对于水、细胞色素的铁和铜、以及血红素、肌内铁蛋白、黑色素、葡萄糖及其它物质的氧化及脱氧形式。
对于氧化及脱氧的血红素,以比尔·莱姆博特关系式表示的吸收系数如下所示: 其中
和
是血红素及脱氧血红素的消失系数,可以被存储在一个查询表中;[Hb],[HbO2]分别是血红素和氧化血红素的细胞组织的浓度;
是背景吸收系数。血红素的饱合度通常是以下式定义: 对于三个波长的测量,血红素饱合度可以用公式(5)和(6)计和虎如下: 其中, 因此,处理器70利用公式(2)而依照公式(7)确定Y,以确定平均入进长度L,然后再用公式(1)确定针对波长λ1、λ2、λ3每一个的μα λ。
在另一个实施例中,这种分光光度计的电子电路部分包括有一适当的低频模块以及一个可切换的高频模块,被耦合到同一光源——检测器探测器20。这种低频模块和这种光源——检测器探测器的设计实际上与待审美国专利701,127(1991年5月16日提交)所描述的血红素测定计相类似,该申请于1992年11月26日公开,作为PCT申请WO92/20273的一部分并在此引作参考。这一低频模块对应于一个标准的血氧测定计,它具有几个Hz到104Hz范围内的调频频率,该低频模块还用于在两个或三个波长提供强度衰减数据。随后,这些LED被切换到高频相位调制单元,与图1的单元相类似,该单元确定了在每一波长光的平均路径长度。该衰减及路径长度数据被送到处理器70,用于被测细胞组织生理特性的测定。
在另一个实施例中,该路径长度被校正的血氧测定计同样利用了以所选频率正弦调制的LED光源,该所选频率可与在从该LED的光输入端口到该光敏二极管检测器(24a、24b、24c)的光检测部分的被检测细胞组织中的路径上散射光子的平均入进时间相比较,但是其电子电路部分不同。检测器输出是经过两个宽带双均衡混频器(DBM),它们是经过一个90°分相器而被耦合,从而得到实际的(R)和镜象的(I)信号部分。这种双均衡混频器最好是以调制频率工作。其相位(θλ)是这样一个角度,其正切是Iλ/Rλ。
当残余相移θ量为零,假定其相移已被去除时,幅值是这些值的平方和的平方根。
这一实施例采用求和及除法电路,以计算该调制指数,它是该幅值与该幅值和从一窄带检测器获得的直流成分相加值之比的商值。
相位处理器接收针对两个或三个波长的相位移作为相位及幅度值,并计算这些相位移的比率。
对于每一个波长,相位移和DC幅度被用于确定一个所选的细胞组织的特性,例如血红素氧化性。
Claims (21)
1.一种通过测量光子入进路径的平均长度以实现细胞组织检测的一种分光光度计,其特征在于它包括:
一个用于产生所选频率的载波的振荡器,在从光的输入端口到光的检测端口的路径上,该所选频率可以与在细胞组织内光子散射的平均入进时间相比较;
一个光源,可操作地与所说振荡器相连接,用以产生所选波长的光,其强度是以该所说频率调制,并在输入端口被引入到被测物体内;
一个光敏二极管检测器,用以在检测端口处检测处于输入和输出端口间的被测物的细胞组织中已经入进的所选波长的光;
一个相位检测器,可操作地连接以接收来自所说振荡器和所说二极管检测器的信号,用以测量在所引入的和所检测到的光之间的相位移;
一个处理器,用以根据所说的相位移来计算路径长度,以及
所说的处理器还用以根据所说的路径长度来确定所检测细胞组织的生理特性。
2.一种通过测量光子入进路径的平均长度以实现细胞组织检测的一种分光光度计,其特征在于它包括:
一个用于产生所选频率的载波的振荡器,在从光的输入端口到光的检测端口的路径上,该所选频率可以与在细胞组织内光子散射的平均入进时间相比较;
一个光源,可操作地与所说振荡器相连接,用以产生所选波长的光,其强度是以该所说频率调制,并在输入端口被引入到被测物体内;
一个光敏二极管检测器,用以在检测端口处检测处于输入和输出端口间的被测物的细胞组织中已经入进的所选波长的光;
一个分相器,用以根据所说载波波形来产生预定的实际不同相位的第一和第二基准相位信号;
第一和第二双平衡混频器,用以使所说基准相位信号和所说被检测的辐射的信号相关联,以便分此从别地产生一个实际的输出信号和一个镜象输出信号;
一个处理器,用以根据所说实际输出信号和所说镜象输出信号来计算所说引入的光和所说被检测的光之间的相位移;以及
所说处理器进一步根据该相位移确定被检测细胞组织的生理特性。
3.一种通过测量光子入进路径的平均长度以实现细胞组织检测的一种分光光度计,其特征在于它包括:
用于产生第一所选频率的载波的第一振荡器,在从光的输入端口到光的检测端口的路径上,该所选频率可以与在细胞组织内光子散射的平均入进时间相比较;
一个光源,可操作地与该振荡器相连接,用以产生所选波长的光,其强度是以所说该第一频率调制,所说光在所说输入端口被引入到被测物内;
一个光敏二极管检测器,用以在所说检测端口检测位于输入和检测端口之间的被测物的细胞组织中已入进的所说波长的光,对应于所说被检测的光,所说检测器以所说第一频率产生一个检测信号;
一个第二振荡器,用以产生一个第二频率的载波,该第二频率从所说的第一频率偏移104Hz的数量级;
一个基准混频器,与所说第一和第二振荡器相连接,用以产生频率大致等于第一和第二频率之差的一个基准信号;
连接以接收来自所说第二振荡器信号和所说检测信号的混频器,并用以将所说的检测信号转换成差频;
一个相位相测器,可操作地连接来接收所说基准混频器的信号和所说的被变换的检测信号,用以测量所说引入光和所说被检测光之间的相位移;
一个处理器,用以根据所说相位移来计算路径长度;以及
所说处理器还进一步用以根据所说路径长度来确定被测细胞组织的生理特性。
4.如权利要求1,2或3的分光光度计,其特征在于它进一步包括:
一个幅值检测器,连接到所说的光敏二极管检测器,用以测量所说被测光的幅值,以及
所说处理器进一步用以接收所说的幅值,以实现生理特性的确定。
5.如权利要求1,2或3的分光光度计,其特征在于它进一步包括:
一个低频血氧测定计电路,可切换地连接到所说光源和所说光敏二极管,用以确定在所说波长处的光吸收性;以及
所说处理器进一步用以从所说血氧测定计电路接收该吸收值,以用于所说生理特性的确定。
6.如权利要求1或3的分光光度计,其特征在于进一步包括两个自动增益控制器,用以均衡对应于所说引入光和所说被检测光的信号,所说的这两个被均衡的信号均被引入到所说的相位检测器。
7.如权利要求1或3的分光光度计,其特征在于它进一步包括:
一个幅值检测器,连接到所说的光敏二极管检测器,用以测量所说被测光的幅值;以及
两个自动增益控制器,用以均衡对应于所说引入光和所说被检测光的信号,所说的这两上被均衡的信号均被引入到所说的相位检测器。
8.如权利要求1,2或3的分光光度计,其特征在于,其中所说的光源是发光二极管,且所说的所选波长是在可见光或红外光范围内。
9.如权利要求1,2或3的分光光度计,其特征在于,其中所说的光敏二极管检测器是一个PIN二极管。
10.如权利要求1,2或3的分光光度计,其特征在于,其中所说的光敏二极管检测器是一个雪崩二极管。
11.如权利要求1,2或3的分光光度计,其特征在于,其中所说的光敏二极管检测器进一步包括一个实际单一波长的滤波器。
12.如权利要求1,2或3的分光光度计,其特征在于它进一步包括:
一个第二光源,可操作地连接到所说的振荡器,用以产生第二所选波长的光,其强度以所说的第一频率调制,所说的辐射在一个第二端口被引入一个被测物;
在检测端口,所说的光敏二极管检测器还用于交替地用以检测已经入射到位于第一和第二输入端口和所说检测端口之间的被测物细胞组织的第一和第二波长的光;
所说的相位检测器还被用以交替地接收对应于所说被检测的第一和第二波长的信号;
所说的处理器被进一步用以交替地从相位移检测器接收相位移,所说的相位移被随后用于细胞组织的生理特性的确定。
13.如权利要求12的分光光度计,其特征在于它进一步包括:
一个幅值检测器,连接到所说的光敏二极管检测器,用以测量在所说每一波长上的所说被检测光的幅值;以及
所说的处理器进一步用以接收所说幅值以进行所说生理特性的确定。
14.如要求1或3的分光光度计,其特征在于它进一步包括:
一个第二光源,可操作地连接到所说的振荡器,用以产生第二所选波长的光,其强度以所说的第一频率调制,所说的辐射在一个第二输入端口被引入一个被测物;
在一个第二检测端口处的一个第二光敏二极管检测器,用以检测已经入射到位于所说的第二输入端口和所说的第二检测端口之间的被测物的细胞组织的所说第二波长的光;
一个第二相位检测器,可操作地连接来接收一个基准信号和来自所说第二个二极管检测器的一个检测信号,用以测量以所说第二波长所引入的和被检测光之间的相位移;以及
所说处理器还被用接收以所说第二波长光的第二相位移,所说第一和第二相位移被随后用于所说生理特性的确定。
15.根据权利要求14的分光光度计,其特征在于它进一步包括:
分别连接到所说第一和第二光敏二极管检测器的第一和第二幅值检测器,所说的幅值检测器被用于测量所说每波长的的所说检测光;以及
所说处理器还被用以接收所说的幅值,用于所说生理特性的确定。
16.如权利要求14的分光光度计,其特征在于它进一步包括:
一个第三光源,可操作地连接到所说的振荡器,用以产生第三所选波长的光,其强度以所说的第一频率调制,所说的辐射在一个第三输入端口被引入到一个被测物;
在一个第三检测端口处的一个第三光敏二极管检测器,用以检测已经入射到位中所说第三输入端口和第三检测端口之间的被测物的细胞组织的所说第三波长的光:
一个第三相位检测器,可操作地连接来接收一个基准信号和来自所说第三二极管检测器的一个检测信号,用以测量具有所说第三波长的所引入的和被检测的光之间的相位移;以及
所说处理器进一被用以接收来自相位检测器的相位移,所说第一、第二和第三相位移被随后用于所说生理特性的确定。
17.如权利要求14的分光光度计,其特征在于,它进一步包括:
分别连接到所说第一、第二和第三光二极管检测器的第一、第二和第三幅值检测器,所说的幅值检测器用来测量以在所说波长的每一个来测量所说被测光的幅值;以及
所说处理器进一步用以接收所说的幅度以进行所说生理特性的确定。
18.如权利要求16的分光光度计,其特征在于,每一个所说的光源是发光二极管,且所说所选波长在可见光或红外光范围内。
19.如权利要求16的分光光度计,其特征在于其中每个所说光敏二极管检测器是PIN二极管。
20.如权利要求16的分光光度计,其特征在于其中每一个所说光敏二极管检测器是一个雪崩二极管。
21.如权利要求16的分光光度计,其特征在于其中每一个所说光敏二极管检测器进一步包括一个实际单一波长滤波器。
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US08/031,945 | 1993-03-16 |
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CN1119410A true CN1119410A (zh) | 1996-03-27 |
CN1089571C CN1089571C (zh) | 2002-08-28 |
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CN94191476A Expired - Lifetime CN1089571C (zh) | 1993-03-16 | 1994-03-15 | 检测被测组织生理学特性的分光光度计 |
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US (2) | US5564417A (zh) |
EP (1) | EP0689398B1 (zh) |
JP (1) | JPH08509880A (zh) |
CN (1) | CN1089571C (zh) |
CA (1) | CA2158435A1 (zh) |
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-
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- 1993-03-16 US US08/031,945 patent/US5564417A/en not_active Expired - Lifetime
-
1994
- 1994-03-15 DE DE69433205T patent/DE69433205T2/de not_active Expired - Lifetime
- 1994-03-15 EP EP94911595A patent/EP0689398B1/en not_active Expired - Lifetime
- 1994-03-15 CA CA002158435A patent/CA2158435A1/en not_active Abandoned
- 1994-03-15 CN CN94191476A patent/CN1089571C/zh not_active Expired - Lifetime
- 1994-03-15 JP JP6521168A patent/JPH08509880A/ja active Pending
- 1994-03-15 WO PCT/US1994/002764 patent/WO1994021173A1/en active IP Right Grant
-
1996
- 1996-10-15 US US08/731,443 patent/US6134460A/en not_active Expired - Lifetime
Cited By (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
CN100401039C (zh) * | 2001-03-21 | 2008-07-09 | 阿斯特拉曾尼卡有限公司 | 新测量技术 |
US7745789B2 (en) | 2001-03-21 | 2010-06-29 | Astrazeneca Ab | Measuring technique |
CN102846323A (zh) * | 2011-07-01 | 2013-01-02 | 中国计量学院 | 一种基于led的无创血氧饱和度检测仪 |
Also Published As
Publication number | Publication date |
---|---|
CA2158435A1 (en) | 1994-09-29 |
US6134460A (en) | 2000-10-17 |
DE69433205T2 (de) | 2004-08-19 |
CN1089571C (zh) | 2002-08-28 |
WO1994021173A1 (en) | 1994-09-29 |
JPH08509880A (ja) | 1996-10-22 |
DE69433205D1 (de) | 2003-11-06 |
EP0689398A1 (en) | 1996-01-03 |
US5564417A (en) | 1996-10-15 |
EP0689398A4 (en) | 1998-10-14 |
EP0689398B1 (en) | 2003-10-01 |
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