CN1192271A - 用于光电血色计的波长可调节光源 - Google Patents
用于光电血色计的波长可调节光源 Download PDFInfo
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Abstract
本发明的方法和设备提供了这样一种系统,其中,可以通过选择它们的驱动电流在给定的范围内调节发光二极管(LEDs)162,以便获得准确的波长。本发明还提供了一种校准和利用LED探头150的方法,这样与已知的驱动电流的变化相对应的波长移动是一个已知量。通常,为了在LED传感器的应用中更好地实现校准和增加灵活性,特别是当为了获得精确的测量结果而需要精确的波长时,利用了LED的波长随驱动电流的变化而移动的原理。本发明还提供了一种系统,在其中不需要知道精确的LED波长,而在以前的系统中需要精确的波长。最后,本发明提供了一种判定发光元件例如发光二极管的工作波长的方法和设备。
Description
发明背景
发明领域
发明涉及对发光二极管的更加有效的校准和使用。更加具体地讲,本发明涉及对与光电血色计系统一起使用的传感器中的发光二极管进行校准和使用的设备和方法。
相关技术描述
发光二极管(LED)应用于许多领域。在特定的应用中,为了获得精确的测量结果需要知道LED的具体工作波长。通常用于监测动脉氧饱和度的非侵入式光电血色计就是这样的一种应用。
在传统的确定动脉氧饱和度的光电血色测定程序中,分别具有不同波长的光能从LED射出,穿过输运血液的人体组织。通常,LED是安装在光电血色计系统上的传感器的一部分。在普通应用中,传感器附着在指尖或耳垂上。光检测器检测经血液衰减后的光能,经过分析光能判定氧饱和度。利用具有其它波长的LED可以监测血液的其它成份或特征,例如carboxyhemoglobin饱和度和散射。
New,Jr.,等的US专利第4,653,498号公开了一种脉冲式光电血色计,它利用两个LED提供两束波长虽然不同但是是经仔细挑选的光束。
在传统的光电血色计中,为了精确地计算氧饱和度,必须准确地知道传感器中的各个LED的波长。然而,为了替换或消毒,传感器必须能够从光电血色计系统上卸下来。
当替换传感器时,由于制造的误差,对于预定的LED驱动电流,新传感器上的LED可能具有稍微不同的波长。因此,传统的光电血色计为了向光电血色计指示而提供了给定传感器中的LED的具体波长。在一种已知的系统中,电阻器用于对发光LED进行编码。选择电阻器的阻值使之可以表示LED的波长。光电血色计读取传感器上的电阻值,并利用该电阻值判定LED的实际发光波长。在授予Nellcor公司的US专利第4,621,643号中公开了该校准过程。图1中展示了这种现有技术传感器。
发明概述
在为每个传感器提供LED工作波长指示的传统光电血色计中,光电血色计系统经编程对各种波长进行所期望的计算。这使得光电血色计系统的设计变得复杂,因此增加了光电血色计系统的费用。因此提供对于不同的传感器均具有相同波长特性的传感器是十分有利的。
另外,传统的传感器要求对各附加的波长具有附加的传感器。对于可替换的传感器,由于在医院中使用着大量的传感器等原因,每个LED显著地增加了总的额外开销。因此,希望提供这样一种传感器,它可以从单个LED中获得多种波长。
可以观察到作为对改变驱动电流、驱动电压、温度或其它可调节参数例如指向LED的光线的响应,许多LED会发生波长移动。本发明包括一种利用这种波长移动来校准LED的改进的方法和设备。另外,本发明还包括利用波长移动的原理使单个LED提供多个工作波长的技术。波长数目的增加提供了在不增加LED的前提下对待测媒质的附加参数进行监测的能力。在光电血色测量中,这允许在不向光电血色计系统添加额外LED的条件下监测血液中的额外成份。
本发明还包括在不知道传感器中的LED的精确工作波长的条件下,利用LED的波长移动获得关于血氧饱和度的生理学数据的技术。
本发明的一个方面提供了能够在预选的波长上发射光能的可调光发射网络。网络配置有一个可以向与电流源相连的发光二极管提供预选源电流的电流源。发光二极管是那种在选定的调节参数发生变化时其波长会随之发生移动的发光二极管。优选地,调节参数是驱动电流或驱动电压。选择与发光二极管并联的调节电阻的阻值使之至少能够吸收预选源电流的第一部分,这样预选源电流的第二部分可以流过发光二极管。选择预选源电流的第二部分使发光二极管能够发出具有预选波长的光能。
在本实施方案中,可调光发射网络还包括一个能够对发光二极管射出的光能进行响应进而产生指示光能强度的输出信号的检测器。
本发明的另一方面包括对产生光线的传感器进行预校准的方法。该方法包括几个步骤。首先确定使光源工作于预选波长所需的流经光源的电流的第一级(first level),然后定义电流的第二级(second level)。电流的第二级高于电流的第一级,电流的第二级构成了驱动电流。然后选择在与光源并联时构成可调光源网络的电阻器。选择电阻器使之在与光源并联时能够吸收足量的驱动电流,这样电流的第一级流过光源。
本发明的另一个方面是一种从单个发光二极管获得两种波长的方法。选用的发光二极管是那种在一定的驱动电流范围内波长会随着流经发光二极管的驱动电流的变化而发生移动的发光二极管。电源与发光二极管相连,以便提供驱动电流。在一定的驱动电流范围内,驱动电流的第一级驱动发光二极管使之激活并作为对驱动电流第一级的响应工作在第一波长。然后,在一定的驱动电流范围内,与驱动电流的第一级不同的驱动电流的第二级驱动发光二极管使之激活并作为对驱动电流第二级的响应工作在第二波长。
在一实施方案中,其中发光二极管向待测媒质发射光能,该方法还包括以下步骤。当发光二极管工作在第一波长时,光线作为具有第一波长的第一光能穿透待测媒质。根据在待测媒质中传播时光能的第一预定衰减特性选择第一波长。利用光检测器测量发光二极管射出的经衰减后的光能。此外,当发光二极管工作在第二波长时,具有第二波长的光能穿透待测媒质。根据在待测媒质中传播时光能的第二预定衰减特性选择第二波长。在第二波长处测量发光二极管射出的经衰减后的光能。
在一个优选实施方案中,利用该方法判定血氧饱和度,待测媒质包括具有流动血液的人体的一部分。在该实施方案中,方法还包括将能量耦合到工作在与第一和第二波长均不相同的第三波长的第二发光二极管。此外,在第一和第二波长之间的波长变化具有预定值,波长为第三波长的第三光能穿透待测媒质,在穿透待测媒质之后测量第三光能。根据测量结果,判定血氧饱和度。
在一个实施方案中,当第一波长为已知值、第一和第二波长之间的波长变化为预定值时,还可以判定与待测媒质有关的、除氧饱和度之外的参数。在该实施方案中,确定第二波长的值,然后计算关于血液的另一个参数。在一个实施方案中,另一个参数是carboxyhemoglobin饱和度。另一个参数也可以是散射。另一个参数还可以是Methhemoglobin。
优选地,利用上述的波长可调设备,利用调节电阻调节第一发光二极管,使得由驱动电流增量的变化产生的波长变化与预定的波长变化相匹配。优选地,调节过程包括并联调节电阻和第一发光二极管,选择调节电阻的阻值使得第一发光二极管随着电流增量的变化而具有预定的波长变化。
本发明的另一方面提供了具有第一发光装置的光电血色计传感器,该装置利用与第一发光装置并联的电阻产生具有第一已知波长的光线。优选地,发光装置包括一个发光二极管。在一个实施方案中,电阻器包括一个其阻值能够指示第一已知波长值的编码电阻器。编码电阻器的阻值足够高,使得在第一发光装置工作时它所吸入的电流非常小。
在另一个实施方案中,电阻器包括一个其阻值能够指示光电血色计系统是预定类型的安全电阻。此外,安全电阻的阻值足够高,使得在第一发光装置工作时它所吸入的电流非常小。
本发明的另一方面包括在一定的波长范围内调节发光二极管使之工作在预定波长的方法。该方法包括选择发光二极管使之在一定的驱动电流范围内能够随驱动电流的变化而发生波长移动,以第一驱动电流驱动发光二极管。在工作于第一驱动电流时测量发光二极管的波长,如果发光二极管没有工作在预定波长,在驱动电流和第二驱动电流之间调节该驱动电流,使得发光二极管的工作在预定波长。
本发明的另一方面包括用于发射和检测光线的传感器。传感器至少具有一个发光单元,该发光单元具有一个为心形发射波长的光辐射。传感器还具有第一和第二光检测器,发光单元的光辐射位于第一和第二光检测器的响应区内。光定向单元使发自至少一个发光单元的光线指向第一和第二光检测器。安置在第二光检测器和至少一个发光单元之间的滤波器的传输带宽包含心形发射波长。
在一个实施方案中,传感器包括一个光电血色计传感器,该至少一个发光单元包括第一和第二发光二极管。优选地,第一发光二极管具有位于红光波段的心形波长,第二发光二极管具有位于红外波段的心形波长。优选地,滤波器的传输带宽包含第一发光二极管的心形波长。
在一个优选实施方案中,光定向单元包括一个具有安置在球面上的第一和第二光检测器的集成光球,以便基本上等量地接收来自至少一个发光单元的光线。
在另一个实施方案中,光定向单元包括分束单元,该单元基本上等分来自至少一个发光单元的光线,并把基本上等分的两部分光线分别指向第一和第二光检测器。
本发明的另一方面包括判定发光单元的心形波长的方法。该方法包括提供一组复杂的预定比值,每个复杂的预定比值对应于相应的心形波长。光线从发光单元传输到第一光定向单元以便获得第一光强,光线穿过对光线进行衰减的滤波器从发光单元传输到第二光定向单元以便获得第二光强。然后计算第二光强和第一光强的比值。该比值与预定的比值组进行比较,以便查找发光单元的心形波长。
在一个实施方案中,第一和第二光检测单元包括包括相同的光检测单元。
附图简述
图1是经校准的现有技术的光电血色计探头;
图2描绘了示例出血液三种成份的消光系数与透过血液传输的传输波长之间的关系的典型曲线;
图3A和图3B描绘了典型的LED特性;
图4A描绘了根据本发明的一个方面而构造的波长可调光电血色计传感器;
图4B描绘了具有待检测手指的光电血色计系统;
图5A和5B描绘了根据本发明而使用的一个电阻器实施方案的典型图;
图6描绘了在两个发射波长相近且同时激活的LED的波长位置的平均效果;
图7描绘了根据本发明另一方面的光电血色计传感器的实施方案;
图8和8A描绘了经校准的改进型光电血色计传感器的典型实施方案;
图9A和9B描绘了根据本发明的一个方面、用于检测发光二极管波长的传感器的替代实施方案;
图10A、10B、10C和10D描绘了与本发明的波长检测方面有关的曲线;
图11和11A描绘了根据本发明的波长检测方面,各种滤波器的滤波响应的曲线图;
图12-15描绘了本发明中使用的四种不同的探头结构;
优选实施方案详述
本发明通常可以使用医用探头和LED。然而,下面对在光电血色计中应用本发明原理所作的描述有利于更好地理解本发明。
在检测患者血氧(或其它成分)饱和度的过程中,非侵入式技术所具有的优点是众所周知的。在光电血色测量法中,已知波长的光线透过待测媒质(例如人的手指如指尖)。当光线在媒质内传播时,光能被构成媒质的成份部分地吸收、部分地散射。任何确定的成份对光能的吸收和散射都决定于穿透该成份光波波长,以及其它几个参数。成份的吸收是以被称作消光系数的参数为特征的。
图2示出了三种可能血液成份的消光系数与光线波长之间的相互关系曲线100。明确地讲,第一条曲线102示例了oxyhemoglobin(氧化血红素)的消光系数与发射波长间的关系;第二条曲线104示例了少量血红素的消光系数与发射波长间的关系;第三条曲线106示例了carboxyhemoglobin(含有一氧化碳的血红素)的消光系数与发射波长间的关系。这种关系在该技术中是很容易理解的。对于媒质中的每一种独立成份都需要一个波长。选择光电血色计使用的波长使得对测量(即氧饱和度等等)的灵敏度最大。这些原理在该技术中是很容易理解的。
入射到至少具有一种待测成份的均匀媒质上的能量幅度与透过媒质的能量幅度间的关系近似用下式表达:
其中I0表示入射到媒质上的能量,I表示衰减信号,di表示光能透过的第i成份的厚度,εi表示光能透过(第i成份的光路长度)的第i成份的消光(或吸收)系数,ci表示厚度为di的第i成份的浓度。如本技术中所众知的,使用传统的光电血色测量技术,利用该基本关系获得氧饱和度。
应当理解的是为了讨论对上式进行了简化。其它因素例如多重散射也对最后的光能衰减有贡献。在Joseph M.Schmitt所著的文章“Simple Photon Diffusion Analysis of the Effects of Multiple Scatteringon Pulse Oximetry”,IEEE Transactions on Biomedical Engineering,vol.38,no.12,Dec.1991,中讨论了多重散射。
然而,为了进一步讨论,仍使用简化的等式(1)。在基于光电血色测量技术的过程中,生理测量的精度受发光LED的波长精度的影响,因为如图2所示消光系数依赖于发光LED的波长。为了获得氧饱和度,典型地利用两个LED,一个在红光波段,一个在红外波段,以便获得患者的饱和度测量。此外如等式(1)所示,消光系数是等式中的关键变量。相应地,向光电血色计提供与传感器的发光LED的具体波长有关的信息是十分重要的,然而,由于制造误差,对于相同的驱动电流,各个LED的波长是不同的,尽管是想制作为特定的波长。波长可调LED
本发明的一个方面提供了调节传感器中各个LED的设备和方法,由此控制LED的波长使它们在各个传感器之间没有显著的差异。利用许多LED所具有的、波长随驱动电流的变化而移动的特性实现波长调节。图3A和3B示例了波长移动的原理。图3A中的坐标图110(带有曲线112)展示了典型LED的、以纵轴表示的电流和以横轴表示的电压之间的关系。图3A中的坐标图110在本技术中是易懂的。在轴A和B所标出的区域内,刚好在曲线112的肩角之外,特定LED的波长随着相应的驱动电流或电压的变化以基本上为线性的方式移动。对于每个LED(设计为具有相同波长),驱动电流的每一个增量对应的波长移动量通常是不同的,正如对于相同的驱动电流,LED(设计为具有特定波长)的工作波长对不同的LED是不同的。
图3B展示了在图3A所示的肩角区域,LED的波长与驱动电流的典型坐标图120。该图在曲线122中展示了随着驱动电流的变化红光波段LED的典型波长移动。图3B中所示的曲线122的斜率对于不同的LED是不同的,波长范围也不同。然而,对于光电血色测量中使用的传统LED,通过LED的驱动电流的增量产生波长的某一增量。因为在图3A所示的曲线112的肩角之外的区域该关系基本上是线性的,在一个优选实施方案,在肩角之外的区域可以获得波长的移动。图3B的坐标图并不能代表所有的LED,而是仅仅表示随驱动电流的特定变化而发生的一种可能的波长移动。
相应地,一种获得特定波长的方法是以获得特定波长所必需的电流驱动LED。然而,这样的实施方案需要对每个传感器都需要改变LED驱动电流的光电血色计设计。
在一个优选实施方案,为了避免增加光电血色计系统设计的复杂性,把一个电阻器与LED并联,以便调节通过LED的驱动电流,并产生特定的波长。在该实施方案中,光电血色计系统对于传感器中的每个LED都工作在特定波长。另外,光电血色计只需要恒定的驱动电流。相应地,在一个实施方案中,光电血色计的设计得到简化,因为不再需要考虑不同传感器之间的波长差异。光电血色计可以简单地设计为工作在特定波长并具有恒定驱动电流。
利用波长移动原理,调节每个为光电血色计制造的LED传感器,这样传感器中的LED为光电血色计产生具有特定波长的光线。根据本发明的LED的调节方面,图4展示了与典型的光电血色计系统152相连的可调节传感器150的一个实施方案。
传感器150具有第一光源160和第二光源170,典型地是LED。与第一LED160并联的第一可调电阻162构成第一可调LED网络164。类似地,与第二LED170并联的第二可调电阻172构成第二可调LED网络174。传感器150还包括光检测器180。光电血色计系统中的电源,例如LED驱动器182,与可调LED网络164、174相连,以便向可调LED网络164、174的输入端提供预定的驱动电流。优选地,LED驱动器182在任何时候都只向可调LED网络164、174中的一个供应电流。光检测器180与光电血色计系统152中的接收-调节电路184相连。工作时,光检测器接收衰减后的光能并产生表示各个光能强度的输出信号。光电血色计系统152还包括具有支持源(supporting resourses)的控制器190和显示器192。光电血色计系统接收来自传感器150的信号并对信号进行分析以便判定关于由光能透射的媒质的信息。应当理解的是为了便于讨论,只是展示了光电血色计系统的简化图。光电血色计系统在本技术中是众知的。一种可能的光电血色计系统包括1996年5月2日发布的国际专利申请第WO96/12435号所公开的光电血色计系统。其它的光电血色计系统是众知的,并被设计为工作在特定波长。
如图4B所示,对于光电血色测量,典型的媒质可以包括手指200或耳垂,这在本技术中是众知的。媒质例如手指和耳垂通常包括多种成份,例如皮肤、组织、肌肉、动脉血和静脉血(分别具有多种成份)、和脂肪。由于不同的消光系数,各种成份对特定波长光能的吸收和散射是不同的。在普通操作中,第一LED162响应来自LED驱动器182的驱动电流而发射出入射光线.光线透过待测媒质传播。当发射的光线在媒质内传播时,光线被部分地吸收。透过媒质的衰减光线由光检测器180接收。光检测器180产生表示入射到光检测器180上的衰减光能强度的电信号。该信号被提供给光电血色计系统152,系统对信号进行分析以便判定由光能透射的媒质的特定成份的特性。
现在,参照第一LED160解释波长调节。波长调节也可以用于第二LED172。如上所述,响应于特定的驱动电流,不同的LED产生不同的波长,尽管希望把LED制造得具有相同的波长。根据本发明,调节第一LED160的方法包括判定使第一LED160工作在特定波长所必需的电流值,然后调节通过第一LED160的电流以便获得特定的波长。
例如,光电血色测量中使用的红光LED的典型工作值位于645nm和670nm之间。对于光电血色计的特定实施方案,光电血色计可以设计为工作在该区域内的某波长,例如670nm。然而,用来产生特定波长670nm的LED对于相同的驱动电流通常具有±2-10nm的制造误差。然而,对于光电血色测量中使用的典型LED,为了获得所需的LED输出波长,可以调节驱动电流。例如,如图3B所示,示出的LED对于典型的驱动电流50mA产生660nm的工作波长。如果把驱动电流增加到大约85mA,工作波长变化为本例中的特定波长(670nm)。本发明利用观测到的波长随驱动电流的变化而移动的原理调节每个LED,以便获得特定波长,例如670nm。
为了讨论,把第一LED160定义为具有图3B所示的波长特性。为了调节第一LED160,预先设定或固定来自LED驱动器182的驱动电流。在本实施方案中,优选地,驱动电流稍大于单独驱动第一LED160所必需的电流(例如100mA或更大)。这是因为第一可调电阻162分流部分来自LED驱动器182的固定驱动电流。选择第一可调电阻162使之适当地分流固定驱动电流,以便通过调节通过第一LED160的电流值而产生特定的输出波长。在本例中,电阻大约可以分流15mA(来自LED驱动器182的总电流为100mA)以便通过把流经第一LED160的电流降低为85mA而产出670nm的特定波长。因此,每个LED可用来自LED驱动器182的相同的固定驱动电流来驱动。以这种方式设计LED驱动器182,使之为与光电血色计相连的每个传感器提供相同的固定驱动电流。这样设计的光电血色计系统152能够以下面的假设为基础进行计算,即对于不同的传感器相应的波长保持恒定。
选择可调电阻的一个特别优选的方法是利用半导体衬底电阻器,例如图5A和5B所示的电阻210。图5A所示的电阻210包括半导体衬底212、电阻膜片214、和连接导线216、218。在一个实施方案中,可调LED220(即波长随驱动电流的变化而移动的LED)与半导体衬底电阻器210并联。然后,利用电流源222向由衬底电阻210和可调LED220构成的网络供应固定(预定)驱动电流。测定可调LED220的工作波长。优选地,初始衬底电阻值小于获得预期输出波长所必需的电阻值。利用激光器划割电阻片214,如图5B中的线224所示。割线224有效地去除部分电阻片214,由此增加了剩余电阻片214的电阻值,这在技术上是众知的。利用激光器,可以十分精确地控制电阻值的增加。可以激光修整电阻片214直到通过可调LED220的电流使可调LED220产生特定工作波长为止。最终的电阻器/LED对构成了可调LED网络。可调LED的高精度和低制作成本使得该调节方法很有优势。
还可以使用选择可调电阻162的其它方法,例如对于第一LED160,计算给定电流变化所对应的波长移动,然后选择合适的电阻值使得适量的电流流过LED以便获得特定的工作波长。类似地,可以使用电位计。优选地,以同样的方式调节每个传感器的每个LED,这样工作波长就是每个传感器的特定波长。例如,两个波长的光电血色计操作可以为两个波长分别为670nm和905nm的LED选择波长。对于每个传感器,第一LED的波长调节为670nm,第二LED的波长调节为905nm。
总之,本发明的波长调节部分包括利用LED的波长移动原理来调节每个LED以便获得各自的特定工作波长。
应当理解的是,对于一些LED,制造误差可能使得波长远离各自的选定波长,以至于不能通过波长移动来正确地调节LED;或者波长的移动不足以获得选定的波长。在一个实施方案中,这种LED不能使用,并认为是在误差范围之外。另外,如果可获得的波长移动不足以实现正确的调节,还有可能使用两个波长彼此非常接近且靠近预选波长的LED。一个LED的波长小于预选波长,一个LED的波长大于预选波长。如图6的坐标图所示,当两个LED均被激发且相互邻近放置时,来自两个LED的光线复合在一起构成复合波长,该波长是两个LED波长的平均波长。复合波长具有更宽的波长范围,但平均值是已知的。优选地,为了微调平均波长,通过调节上述的电阻器来实现一个或两个LED波长的移动,这样使平均波长为选定波长。相应地,可以利用两个LED(优选地根据本发明成对地进行调节)为给定的光电血色计操作提供选定波长。
作为另一种选择,如果波长移动不足以使所有的LED调节到选定波长,可以只使用一些选定波长。例如,为了判定氧饱和度,选定的红光波长为660nm、670nm和680nm。选定的红外波长为900nm、920nm和940nm,独立于红光波长。利用上述的可调电阻调节选定的红外波长,这样红光LED和红外LED分别工作在选定的红光波长和红外波长中的一个波长。然后在传感器上或与传感器相连的连接器上安装一个指示器,以便允许光电血色计判定哪一个选定的波长出现在与光电血色计相连的传感器上。另外,可以为光电血色计系统提供一个波长检测装置,以便判定哪一个选定的波长出现在与光电血色计系统相连的传感器上。尽管该实施方案需要一些装置供光电血色计判定哪一个选定的波长出现在传感器上,但是不同传感器上的选定波长是精确的。双波长LED
本发明的另一方面利用了对于确定的电流变化LED的波长会发生移动的原理,以便利用单个LED输出两个工作波长。在生理测量中,例如在光电血色测量中,这样作是有利的,因为利用每个新增的附加波长,可以测量血液中其它成份的饱和度。例如,利用双波长光电血色计,可以只精确地检测两种成份(例如氧饱和度)中的一种与两种成份之和的比值。如果用两种波长检测氧饱和度,在血液中大量存在的其它成份将影响氧饱和度的测量。
如果血液中的其它成份对读取特定患者的氧饱和度有显著的影响,那么成份检测的不准确将对患者有害。当出现在血液中时,对双波长光电血色计提供的氧饱和度读数具有显著影响的的成份的例子是一氧化碳。这是因为对于660nm附近的光能carboxyhemoglobin(如图2中的曲线106所示)的消光系数值接近于oxyhemoglobin(如图2中的曲线102所示)的消光系数值。因此,可能把carboxyhemoglobin检测为oxyhemoglobin。利用双波长光电血色计,这将导致血液中氧饱和度的错误指示(即估计过高)。以这种方式,护理医生可能错误地检测为缺氧,和患者体内的一氧化碳过高。如果在传感器上提供额外的发射波长,光电血色计就可以检测其它成份,例如carboxyhemoglobin。
根据本发明,为了利用两个适当的驱动电流驱动一个LED以便提供两个不同的波长,利用了LED的波长移动原理。在其简化形式中,首先利用产生第一已知波长的第一已知驱动电流驱动LED(其波长随驱动电流的变化而移动),然后利用产生第二已知波长的第二已知驱动电流驱动同一个LED,这样可以实现上述目的。
图7展示了根据本发明的这一方面而设计的、与光电血色计系统252相连的、用于进行光电血色测量的传感器250的一个优选实施方案。传感器250包括第一LED254和第二LED256。对于光电血色测量,第一LED254优选地工作在红光波段,第二LED256优选地工作在红外波段。传感器250还包括光检测器258。光检测器258与接收-调节电路262相连。光电血色计系统受控制器264的控制,并具有一个显示器266。如本领域中所众知的,LED驱动器260以预定的驱动电流驱动LED254、256。光检测器258检测经待测媒质衰减后的光能。光电血色计252接收和分析来自光检测器258的信号,以便判定与光能透射的媒质有关的信息。与图4中的实施方案一样,以简化的形式展示了光电血色计系统252。适用的光电血色计系统包括1996年5月2日公布的国际专利申请第WO96/12435号所公开的系统。还包括在本技术中众知的其它监视器。根据本发明修改光电血色计系统252使之以下述方式驱动波长可调LED。
在用于光电血色测量的本例中,第一LED254是波长可调LED,并用于提供两种波长。为了精确地提供两种波长,利用了波长移动原理。根据一个实施方案,在制作传感器时,对LED进行检测,并在传感器上安装一个指示器,该指示器可以由光电血色计系统252读取,并指示出为了实现期望的波长移动所需的驱动电流的变化。指示器可以包括一个位于传感器或传感器连接器上的电阻,一个位于传感器或传感器连接器上的存储器,或类似装置。另外,指示器可以向光电血色计指示波长移动量,这是通过预定的驱动电流变化而获得的。另一种选择是为光电血色计提供波长检测器268,该检测器允许光电血色计系统252检测激活的LED的发射波长。波长检测器,例如单色仪,在本技术中是众知的。然而,传统的单色仪又贵又笨重。该说明在下面给出了一种更加实用的波长检测方法。在该实施方案中,利用波长检测器268监测波长,LED驱动器260不断地调节驱动电流直到达到所需的波长为止。
在更简化的光电血色计设计的一个优选实施方案中,为了用单个LED例如第一LED254精确地提供两种波长,调节由斜率调节电阻272和第一LED构成的网络270的斜率,这样流入第一斜率调节网络的驱动电流的预定变化(ΔI)使第一LED254的波长产生预定的移动(Δλ)。换句话说,如图3B所示,每个LED的曲线122具有特定的斜率。然而,对于不同的LED,该曲线的斜率通常是不同的,甚至于对分类为具有特定波长的LED也是如此。为了简化设计以便使光电血色计获得可重复的预选波长移动,优选的是得到与相同的预选驱动电流变化(ΔI)相对应的、不同传感器中的各个第一LED的预选波长移动(Δλ)。相应地,期望的是不同探头上的第一LED(本例中)以相同的预定波长变化来响应相同的由LED驱动器260提供的驱动电流变化。换句话说,图3B所示的曲线100的斜率对于各个相应的LED网络均为相同值是有利的,因为该值通常对各个独立的LED是不同的。以这种方式,光电血色计以两级驱动电流驱动LED,其中两级驱动电流是预先选定的,并且对不同的传感器是恒定值。
当第一可调电阻162以预定的驱动电流把第一LED160调节到特定波长时,斜率调节电阻,例如斜率调节电阻272,可以用来改变特定的相应LED网络(例如第一斜率可调LED网络)所具有的曲线122的斜率。在大多数情况下,斜率调节电阻272,如果用于调节斜率,不能用来精确调节第一LED254的波长。然而,可以利用向光电血色计指示给定驱动电流产生的第一LED的特定工作波长的其它方法和过程。例如,传感器250可以具有一个指示器(例如电阻或廉价存储装置),它可以由光电血色计252读取,并提供了斜率调节LED网络的初始工作波长。
斜率调节可以以上述的、与调节半导体衬底电阻210相同的方式完成。然而,衬底电阻的功能是用作斜率调节电阻,而不是波长调节电阻(即调节衬底电阻使波长对预定的、LED/电阻网络的驱动电流变化产生预定的波长变化)。换句话说,对于第一LED254,图5A和5B所示的衬底电阻210与第一LED254相连,并构成了斜率调节电阻272。利用激光器修整电阻直到网络270的预定的驱动电流变化产生第一LED的预定波长变化。
应当注意的是,如果很容易得到对于相同的驱动电流变化能够产生相同波长移动的LED,那么就不再需要第一斜率调节电阻272。
为判定氧饱和度,第二LED工作在固定的红外波长(例如905nm)。优选地,如果红外LED具有制造误差,可以通过调节电阻274,以与调节图4中的调节电阻162相同的方式,调节红外LED使之工作在选定的红外波长。利用可调第二(红外)LED256和斜率可调第一LED254(可提供两种波长),利用传感器250可以进行三波长测量。
在使用中,首先,以初始驱动电流驱动图7中的传感器250,使第一LED254产生第一波长(例如660nm)光能。该第一波长的衰减信号由光检测器258检测,并由光电血色计252接收。然后,用根据预定的驱动电流变化而改变的、新的驱动电流驱动第一斜率可调LED254,使之产生预定的波长移动,并达到第二波长(例如675)。只要向光电血色计系统252提供初始波长,并且正确地调节第一LED网络270的斜率(由电流变化产生的波长变化)使之与预定斜率匹配,那么第二波长也是一个已知量。通过驱动第二LED256和利用光检测器258接收衰减信号,可以进行第三种测量。测量值存储在光电血色计系统252中。根据所进行的三次测量,可以判定血液中两种成份的动脉饱和度(例如carboxyhemoglobin和oxyhemoglobin),由此提供更加精确的、关于待测患者血液的生理构成的信息。
在需要监测一氧化碳和氧的光电血色计系统中,第一波长可以为660nm,第二波长可以为675nm或680nm,第三波长可以是红外波长,例如900nm或905nm。利用由两个LED提供的三种波长,可以判定血液中的carboxyhemoglobin饱和度和oxyhemoglobin饱和度。利用两个LED进行三波长测量可以降低传感器的成本,如果传感器是一次性使用的传感器或可更换传感器,那么这样作是十分有利的。
除了上述的应用之外,还应注意的是可以使用上述的波长移动原理在一个LED上获得额外的波长。无精确波长信息的测量
本发明的另一方面包括在一个LED的精确工作波长为未知的条件下对待测媒质中的特定成份(例如血液中的oxyhemoglobin)的饱和度进行测量的设备和方法。根据本发明的这一方面,如果对于已知的驱动电流变化LED的波长移动是已知的,那么如果还有其它信息,LED的工作波长就不是必需要知道的,如下面所解释的。
如上所述,可以通过调节已有的LED可以知道特定的电流变化所产生的波长移动,这样LED以预定的波长变化(Δλ)作为对预定驱动电流变化(ΔI)的响应。另外,如果可以得到对预选的电流变化可以产生重复性波长变化的LED,那些LED不经调节就可使用。参照使用双波长光电血色计的动脉氧饱和度判定过程可以解释本发明的这一方面。
如上所述,图2展示了三种血液成份的典型消光系数与通过血液传播的光线的发射波长之间的关系图。为了判定氧饱和度,感兴趣的是第一曲线102和第二曲线104。
如第一曲线102所示,对于波长大约在665nm(在图中用λ1表示)和690nm(在图中用λ2表示)之间的光线,oxyhemoglobin的消光系数基本上相等(在图2的Y轴不用对数坐标表示时更加明显)。当位于相同范围(即λ1和λ2)内的光线透射过少量血红素时(第二曲线104),少量血红素的消光系数与透射波长基本上呈线性关系。在本发明的设备和方法中利用这些已知的血液成份特性以便在两个LED中的一个的特定波长为未知的条件下获得关于氧饱和度(或其它成份的饱和度)的信息。
假设入射光用字母I0表示,衰减信号用I表示,衰减信号可以用前面的等式(1)表达。换句话说,对于图7的LED传感器250,衰减信号I由光检测器258接收,并且是环境传输的函数,如等式(1)所示。
当波长为λ的光线透射过其血液中含有两种形式的血红素(oxyhemoglobin和减少的血红素)的组织时,对于两种血液成份,等式(1)可以推广如下:
其中:
d媒质厚度,
ε1λ在波长λ处减少的血红素的消光系数,
ε2λ在波长λ处oxyhemoglobin的消光系数,
c1 减少的血红素的饱和度,
c2 oxyhemoglobin的饱和度,
εj 第j层衰减材料的吸收系数(不包括oxyhemoglobin和减少的血红素),
dj 第j层衰减材料的厚度(不包括oxyhemoglobin和减少的血红素),
cj 第j层衰减材料的浓度(不包括oxyhemoglobin和减少的血红素)。
等式(2)还可以以下面的方式表达:
其中:
s为通过利用光检测器测量I,并在取自然对数之后计算I和IBL的比值而得到的值。
为了判定氧饱和度,其中光线以第一红光波长λ1传播,等式(3)表达如下:
其中光线以红外波长λIR传播,等式(3)表达如下:
如在技术中众知的,氧饱和度定义为如下比值:氧:
或
因此:
作替换:
和
分子和分母同时乘以-1:化简:
分子和分母同时乘以d: 把等式(12)带入等式(11): 化简:
最后: 当波长λ1和λIR均为已知时,相应的成份在波长λ1和λIR处的消光系数ε1λ1’、ε2λ1’、ε1λIR’和ε2λIR’也是已知的。如上所述,通过测量I和I0,并且在工作中对不同波长处的该比值取对数可以得到S1和SIR。相应地,饱和度等式中的所有变量均是已知的或者是可以通过测量而获得的。
然而,如果发光LED的波长是未知的,消光系数ε也是未知的。根据本发明的一个方面,可以在一个LED的精确波长为未知的条件下计算氧饱和度。这里为了讨论的目的,选择红光波段的LED来说明本发明的这一部分。根据本发明,如上所述,可以调节红光LED使之具有预选的波长移动,尽管精确的波长是未知的。相应地,可以利用两个不同的驱动电流驱动红光LED以便获得两种不同的波长,波长之间的移动是预先选定的和已知的。然而,如上所述,必须至少知道起始波长的一些指示才能够知道精确的波长。根据本发明,只要预选的波长移动是已知的,就不必知道起始波长。
在消光系数随着波长发生1-3nm的移动而变化的应用场合,将有可能在没有关于波长移动的先验信息的条件下判定波长。通过计算几个(例如两个或更多)不同的LED驱动电流所对应的期望测量值(例如氧饱和度),再利用测量值的变化以及根据经验得到的、关于波长的、用来判定LED波长的数据组(即曲线),就可以实现上述目的。
如果利用预选的波长移动,光电血色计系统能够在三个波长λ1、λ2和λIR处进行测量。这样,除等式(3)和(4)之外,可以得到第三个等式。
光线以第二红光波长λ2传播时,等式(3)表达如下:
如图2所示,在650nm-700nm波段,消光系数没有显著的变化。更具体地说,在λ1-λ2=665nm-690nm波段:
还在同一波段内: Δε1是在上述波段内已知的波长移动,因为消光系数的变化Δε1基本上是线性的。
把等式(14)和(15)代入等式(4)、(5)和(14)将得到如下等式:
如上所述,通过测量I和IBL可以计算出S1、S2和SIR。相应地,S1、S2和SIR为已知值。假定红外波长LED的消光系数ε1和ε2是已知的,因为在感兴趣的红外波长波段(例如850nm-920nm,更具体地讲是在890nm-910nm),曲线102和104的消光系数基本上是恒定值。在另一个实施方案中,调节LED可以适当地提高精度。只要波长位于消光系数为恒定值的波段,波长λ1和λ2处的oxyhemoglobin的消光系数就是已知的。在本例中,该波段定义为665nm至690nm。此外,对于λ1-λ2=665nm-690nm之间的已知波长移动,减少的血红素的吸收系数变化(Δε1)是已知的,因为ε1与λ呈线性关系,所以Δε1也是一个已知量。对于大多数应用媒质的总厚度d通常是未知的。然而,对于氧饱和度的测定,如上所述,由于饱和度是一个比值,可以消去厚度(d)。
相应地,对于氧饱和度的测定,等式(17)、(18)和(19)给出了带有三个未知数(ε1λ1、c1和c2)的三个等式。利用推导等式(6)至(13)的代数方法求解这三个等式,得到氧饱和度比值c2/(c1+c2)。因此,只要第一LED254的工作波长处于已知波段,就不需要准确地知道第一LED254的工作波长,在该波段,预选的驱动电流变化将产生预选的波长变化,在该波段,一种成份的消光系数是恒定值,第二种成份的消光系数基本上为线性关系,这样预定波长变化产生的消光系数变化也是已知的。
因此,本发明的这一方面,允许使用者在不知道LED的精确工作频率的条件下获得生理数据。LED传感器的改进校准方法
本发明的另一方面包括用于光电血色计系统的改进校准技术,其中,利用电阻对LED进行编码而不是对其进行调节。如图1中的利用现有技术校准的光电血色计系统所示,编码电阻300利用独立的电连接引线,并且与公共地引线304相连。随着可更换或一次性传感器使用的持续增多,降低可替换传感器的复杂程度的任何措施都将显著地降低成本。根据本发明,可以利用图3A所示的LED特性来提供成本更加合理的、经编码或校准的光电血色计探头,其中编码或校准由编码电阻实现。
根据本发明的这一方面,一个LED电连接可以用于编码电阻。图8展示了典型光电血色计传感器的简图,其中编码电阻332可以由一个LED电连接而不是独立的电连接读取。传感器310包括第一LED312、第二LED314和光检测器316。第一LED312具有相应的第一电连接318;第二LED314具有相应的第二电连接320;光检测器316具有相应的电连接322。LED312、314和光检测器316中每一个都在其输出端与公共地电连接330相连。在本实施方案中,编码电阻332与第一LED312或第二LED314并联。在本实施方案中,编码电阻332不能用来调节第一LED312的波长或者调节第一LED网络的斜率,而是用作一个能够由相连的光电血色计系统341读取的指示器。电阻可以用来指示第一和第二LED312、314的工作波长,或更加优选地是用来指示探头的型号。换句话说,编码电阻332的阻值可以用来指示该电阻是成人探头、儿童探头、婴儿探头、一次性探头或可再用的探头。在优选实施方案中,编码电阻可以跨接在每个LED312和314上以便在不增加引线的条件下提供附加的探头信息。然而,可以使用任何不与LED并联的电阻器或阻抗元件对LED的波长变化或其它信息进行编码。
例如,编码电阻可以用于安全目的。换句话说,编码电阻的阻值和跨接LED312的配置可以保证正确地为光电血色计配置探头。例如,编码电阻可以用来指示探头来自授权的供应商,例如“Masimo”标准探头、“Patient Monitoring Company1”探头、“Patient MonitoringCompany2”探头等等。
此外,应当注意电阻可以不是无源器件。还可以利用有源电路提供编码信息,例如晶体管网络、存储器芯片,或其它标识器件,例如达拉斯半导体公司的(Dallas Semiconductor)DS 1990或DS 2401或其它自动识别芯片。
为了读取编码电阻332,光电血色计系统340以足够低的电流驱动第一LED312/编码电阻332组件,使得LED吸入的电流很小,因为如图3A的曲线所示I和V呈指数关系。如本技术中所众知的,在A轴指示的肩角区域LED被激活。电压低于A处的电压值时,LED处于非激活状态,吸入的电流很少。换句话说,流经LED312的电流可以忽略。流经第一电连接318的电流几乎全部流过编码电阻331。
对应于所加的电压,光电血色计系统通过测量流经第一电连接318的电流来测量流过编码电阻的电流。然后,光电血色计系统340判定用来指示探头类型的编码电阻332的阻值、工作波长或探头的其它参数。本质上讲,通过把第一电连接318与地之间的电压降低到不足以激活第一LED312的低电压,第一LED312可以有效地与电路分离。在本实施方案中,可以发现对于传统的、红光和红外波段的LED,优选的电压是0.5V。电压为0.5V时,流经LED的电流一般小于1uA(非常小)。
优选地,编码电阻332的阻值应当足够高,当供应给第一电连接318的电流上升到足以驱动第一LED312的水平时,编码电阻332应当能够有效地与电流分离,因为它的阻抗远高于有激活工作电流流过时第一LED312的阻抗。
因此,编码电阻可以和光电血色计LED传感器并联,而不必增加专用于编码电阻的电连接。这将降低本发明传感器的成本。
在一个优选实施方案中,通过以区别于LED驱动电流的频率提供一个0.5V的编码电阻读取信号,光电血色计能够连续地监测编码电阻。例如,如果LED驱动电流的开关频率为625Hz,可以以远低于625Hz的频率提供0.5V的编码电阻读取电压,这样利用截止频率低于625Hz、而过渡带允许0.5V信号通过的低通滤波器很容易滤过625Hz的信号。这将允许光电血色计在系统操作员更换传感器的情况下连续监测编码电阻332。
这个利用编码电阻332的优选实施方案还可以利用传统的、红光和红外LED的背-对-背配置,如在光电血色计中常用的。该配置示于图8A。图8A与图8类似,只是第一LED312和第二LED314以背-对-背的方式连接,这样需要电连接318,电压能够在正负之间变化以便吸入通过第二LED314或第一LED312的电流。这减少了与光电血色计探头的电连接,由此进一步降低了探头的成本。在图8A的背-对-背配置中,如果第二LED314是转折电压大约为2.0V的红光LED,第二LED312是转折电压大约为1.5V的红外(IR)LED,优选地在第一电连接318上施加大约为0.5V的正电压,以便测量编码电阻332。因为红光LED的转折电压为2.0V,流经红光LED的电流极小(小于1uA),并且基本上没有电流流经红外LED312(因为红外LED处于反向偏置状态)。在这种情况下,流过由第一LED312、第二LED314和编码电阻332构成的网络的电流近似等于流过编码电阻332的电流。然后,通过欧姆定律,用施加在网络上的电压除以流经该网络的电流,就可以很容易地确定编码电阻332的阻值。必须小心以确保元件(有源或无源)不会产生会降低系统信噪比的电磁噪声。波长检测
如上所述,在特定条件下,直接获得与光电血色计相连的LED的波长信息是很有用的。如图7所示,可以配备一个波长检测器268。然而,波长检测器需要一些由操作员执行的配置操作。在医院中,简化光电血色计的操作是有利的。由此,在另一个实施方案中,每个LED传感器都配备一个波长检测器。图9A和9B展示了配备有滤波器的LED传感器的可行实施方案的框图。这些传感器结构用于为传感器检测LED的波长。
如图9A所示,传感器400包括发光LED网络402、第一光检测器404、第二光检测器406、扩束器407、分束器408、光滤波器410和可选的光滤波器471。发光LED网络402、第一光检测器404和第二光检测器406均与光电血色计系统412相连。第三光检测器413也用虚线划出以表示光电血色测量用的光检测器。在下面与校准光电血色计探头400有关的讨论中不再讨论第三光检测器413。发光LED网络402优选地具有至少两个LED,一个在红光波段(例如660nm),一个在红外波段(例如905nm),下面将描述利用图9A所示的传感器配置400来判定LED网络402中的一个LED的波长。
如图9A所示,LED网络402发射出透过扩束器407的光线414。在优选的实施方案中,配备了扩束器407,以便消除光的极化,因为分束器408对偏振光很敏感,以及绝大多数LED都会发出一定比例的偏振光。然后,光线透过使其分开的分束器408。优选地,分束器408镀有一层可以部分地对感兴趣的、LED网络402中的LED波长进行反射的材料。优选地,分束器408反射大约一半的光线414并使其射向第一光检测器404。剩余的光线穿过分束器408和滤波器410,由第二光检测器406接收。光电血色计系统412接收从第一和第二光检测器404、406读出的光强值,并利用从第一和第二光检测器404、406得到的相对光强来判定LED402的发射波长的中心,下面将进一步解释。
如在技术上所众知的,制造使光束精确对分的分束器是十分昂贵的。然而,不必获得精确的百分之五十的光线分束,因为不精确的分束可以用校准补偿。在没有第二滤波器411的实施方案中,可以通过激活红外LED来校准系统。这是可能的,因为第一滤波器410对红外波长是透明的,由此,光检测器404和406检测到相同的信号。在这样的实施方案中,可以比较第一和第二光检测器404、406的光强输出,并在运行时利用校准常数使之相等。这就补偿了光检测器分束器408和扩束器407中的不精密度。
在不使用红外光校准的实施方案中,可以在与每个设备的无源或有源编码元件415一起交付使用之前,校准光检测器404和406、分束器408和扩束器407。应当理解的是,方框415表示一个或多个编码元件。应当理解的是,单个编码元件可以用来指示方框515内的所有光学设备。优选地,在该实施方案中用于校准的元件(虚线表示的、标有515的方框中的元件)安置在探头的可再用部分,这样成本不会显著增加。
由于温度敏感性和制作过程的不精密度,滤波器410可能还有一些不精密度。由此,为了校准由于温度变化而产生的滤波器410(优选地为渣球玻璃(shot glass))的不精密度,在优选实施方案中配备了温度检测器405。因为shot glass滤波器的温度敏感性是众知的,通过检测温度,可以判定滤波特性的变化。由于制作的不精密度,可以在探头上配备无源或有源编码元件415以便提供与选定(理想情况)的滤波特性(滤波器的过渡带)变化有关的信息。
图9B展示了另一个利用滤波器结构的优选实施方案。图9B展示了具有发光LED网络420、扩束器421、第一光检测器422和第二光检测器424的传感器。与图9A一样,第三光检测器431表示用于光电血色测量的光检测器。第一和第二光检测器422、424安置在集成光球426等的内球面上。如图9B所示,集成光球426具有一个孔,通过它来定向LED网络420发出的光线429,以便于监测和判定波长。进入孔的光线在光球的内表面反射,没有显著的吸收。优选地,集成光球的内表面可以反射LED网络420射出的光线。此外,集成光球426的内表面散射光线。优选地,第一和第二光检测器422、424横向跨越集成光球,孔428到第一和第二光检测器422、424的距离是相等的。以这种方式,每个第一和第二光检测器422、424都基本上接收到等量的、LED网络420射出的光线。
与图9A的实施方案一样,第二光检测器424具有一个辅助低通光滤波器430,入射到第二光检测器424的光线在到达第二光检测器之前要先通过该滤波器。由此,类似于图9A的实施方案,图9B的第二光检测器424接收经滤波器430衰减的光线,第一光检测器422接收未经滤波器430衰减的光线。
与图9A的实施方案一样,如在技术中所众知的,制作能够精确地汇聚光线的集成光球是十分昂贵的。然而,不必必需获得完美的集成光球,因为校准可以补偿这种光球(以及其它元件)的不精密度。例如,如果不使用红外滤波器(对应于图9A中的滤波器411),可以通过激活红外LED来校准图9B的系统。这是可能的,因为滤波器430对红外波长是透明的,由此,每个光检测器422、424都可以检测到未经滤波的信号(理想情况下是相等的)。在这种实施方案中,可以比较第一和第二光检测器422、424的光强输出,并在运行时利用校准常数使之相等。这就补偿了光检测器、光球和扩束器的不精密度。
与图9A的实施方案一样,如果没有使用红外光校准,可以在与每个设备的无源或有源编码元件432一起交付使用之前,校准光检测器422和424、光球426和扩束器421。
与图9A的实施方案一样,由于温度敏感性和制作过程的不精密度,滤波器430可能还有一些不精密度。由此,为了利用滤波器430(优选地是渣球玻璃(shot glass))校准由于温度变化和制作误差而产生的不精密度,在优选实施方案中配备了温度检测器425,与图9A的实施方案一样。由于制作的不精密度,可以在探头上配备无源或有源编码元件432以便提供与选定(理想情况)的滤波特性(滤波器的过渡带)变化有关的信息。
应当理解的是,在一个实施方案中,单个存储元件或其它有源或无源元件(415、432)应当具有足够的识别能力以便为每个扩束器、光检测器、滤波器和分束器(或光球)提供特征信息。例如,存储设备或晶体管网络可以具有多位设备信息。
在本实施方案中,在图9A和9B的LED网络402、432中使用了红光(例如640-680nm)和红外(例如900-940nm)LED,红光LED的波长对光电血色测量十分关键。由此,需要精确地判定LED网络402中的红光LED的中心工作波长。在这种情况下,优选地使滤波器410和430部分地衰减红光波段的光线,而让红外波段的光线无衰减地通过。
现在说明利用图9A和9B的传感器识别LED波长的原理。如在技术中所众知的,用于光电血色测量等的LED具有与图10A的曲线440所展示的发射曲线类似的发射特性。如图10A所示,理想的LED的中心波长为λ0(例如660nm)。然而,如众知的,由于制作误差,一批目标中心波长为λ0的LED的实际中心波长会有所不同。例如,如图10A示出的虚线发射曲线440A一样,发射曲线可以向右移动。在精确的光电血色测量中实际中心波长的位置是很重要的。
优选地,滤波器410和430具有图10B中的曲线450所示的响应特性。选择滤波器使其过渡带的中心位于目标中心波长λ0,优选地,滤波器的过渡带由预计的低端波长λ1一直延伸到预计的高端波长λ2。优选地,(λ1-λ2)的范围包括预计的由制造误差产生的、LED的波长变化范围。换句话说,目标中心波长为λ0的LED的制造误差范围不应超过滤波器过渡带的上边带或下边带。
对于中心波长处于滤波器过渡带区域的LED,未经滤波的、由传感器LED检测到的总强度与经滤波的、由同一传感器LED检测到的强度的比值提供了十分有用的信息,下面进一步解释。
图10C示例了波长稍稍高于目标波长λ0的LED的比值。未经滤波的LED发射谱用LED发射谱曲线440A表示。滤波后的LED发射谱用LED发射谱曲线441表示。对滤波发射谱的正确理解是滤波后的发射谱曲线441表示与未经滤波的LED发射谱相乘之后的滤波器响应曲线。重要的比值是滤波后的发射谱曲线441(用交叉影线表示)下部的面积与未经滤波的LED发射谱曲线440A下部的面积的比值。应当理解的是,对于中心波长处于λ1-λ2之间的LED,并假定具有相同的滤波器响应,该比值将在0-1之间变化。
可以根据由光检测器404、406或422、424接收到的光强的比值以下述方式确定这两块面积的比值:未经滤波的光IL(λ)的归一化光强与滤波后的光If(λ)的强度由下式表示。
光检测器404、422接收到的、未经滤波的光能可以用在LED发射谱的波长范围内的积分表示如下: 其中IL(λ)波长为(λ)时LED发射谱,P(λ)是波长为(λ)时光电二极管响应谱。
为了简化起见,令光电二极管响应谱在感兴趣的波长区域(λ1-λ2)为“1”(P(λ)=1)(换句话说,LED射出的光线落在LED的波长范围内),第一光检测器404、422(无滤波器)的输出信号表示如下:
类似地,已经通过滤波器410、430的、由第二光检测器406、424检测到的光能可以表示如下:
如果一批传感器中所有的LED在感兴趣的波长区域(λ1-λ2)内均具有相同的峰值发射谱和带宽,并且除乘性恒定值I0之外,可以用相同的等式(30)表示,那么归一化的能量比值可以定义如下:
所产生的(34)式的比值是滤波之后的LED发射谱的全部面积(在图10C中用交叉影线表示)与LED发射谱曲线下部的全部面积的比值。
函数Enorm在区域(λ1-λ2)内是单值、单调的,且只与相对于滤波器的过渡带中心λ0、LED的中心波长发生的移动有关。
因此,对于过渡带中心在λ0的滤波器,在波长范围(λ1-λ2)内,第二光检测器检测到的能量(有滤波器)与第一光检测器检测到的能量(无滤波器)的比值将处于0-1之间。精确的比值决定于待测LED的中心波长。如图10C所示,当中心波长向λ2移动时,比值接近“1”,当中心波长向λ1移动时,比值接近“0”。对于λ1=~610nm和λ2=~710nm的情况,图10D示出了这种关系。
在使用中,为处于波长范围(λ1-λ2)内的每一可能的LED波长计算这个比值。例如,利用表示波长范围在(λ1-λ2)内的LED的测试批次来计算滤波后的光强和未经滤波的光强之间的相应比值。可以利用精确的波长检测设备,例如单色仪,测量各个待测LED的中心波长。每个待测LED的中心波长与每个待测LED的测量比值一起被存储起来。这将产生归一化的光电二极管响应,参照该响应可以得到波长在(λ1-λ2)范围内、但波长值为未知的LED的波长。
换句话说,对于任何中心波长在(λ1-λ2)范围内的LED,利用图9A和9B所示的传感器,通过计算第二和第一光检测器的光强比,并参照归一化的光电二极管响应,利用该比值查找波长,就可以确定传感器中的LED的波长。在本实施方案中,利用存储在光电血色计系统的存储器中的查找表可以实现上述目的。查找表中存储了与相应的波长值相对应的比值。
因此,利用图9A和9B的传感器实施方案,光电血色计只是为了校准才简单地、连续地初始化测量过程。利用上述的方法,光电血色计计算两个光强间的比值(滤波后的和未经滤波的),并获得传感器的各个波长。这是为了测试的目的。因此,优选购买的LED或shot glass应当产生小于1、但大于0的比值,否则LED波长将是不确定的。在比值为1或0的情况下,系统将既不操作也不使用已接近极限的校准等式(例如,在本实施方案中,对于比值=0,假设波长为630nm,对于比值=1,假设波长为670nm)。
如上所述,在光电血色计探头中,关于精确的红光LED波长的知识通常要比关于精确的红外LED波长的知识重要得多。因此,在红光波长波段,图9A和9B中的传感器的滤波器具有值为λ0的过渡带中心波长。如图10B中的滤波器响应曲线所示,如果过渡带的中心处于红光波段,滤波器将不会使红外光衰减。
图11展示了优选滤波器响应的例子。图11展示了三种适应于本发明的、根据所期望的波长而选定的、滤波器的响应曲线。第一滤波器的过渡带中心位于645nm,第二滤波器的过渡带中心位于665nm,第三滤波器的过渡带中心位于695nm。根据目标中心波长的不同,还可以使用其它的滤波器。
然而,应当理解的是,如果滤波器的中心波长λ0位于预期的或目标红外波长,上述原理也适用于红外LED。另外,第二滤波器411(图9A)也可以是中心波长位于预期的或目标红外波长的那种滤波器,以便校准红外LED。换句话说,第二滤波器411将透射红光波长(对于红光LED光线是透明的),其过渡带将以900或905nm为中心。这种滤波器示于图11A。
还可以只利用一个光检测器和一个可移动滤波器完成上述的波长检测。操作员将如无滤波器的光电血色计所指示的那样初始化光强的测量。然后,操作员把滤波器放在LED和光检测器之间的光路上,并开始第二次读数。第二次读数与第一次读数的比值给出了用于查找工作波长的比值Inorm。探头实例
图12-14示例了用于医疗监测患者的三种不同的探头。
图12展示了具有与电缆504相连的辅助连接器502的绕贴式(wrap-around)探头500,电缆与光电血色计系统(未在图12中示出)相连。图12A展示了连接器502的底部,图12B展示了图12中的绕贴式探头的底视图,图12C展示了图12中的绕贴式探头的侧视图。绕贴式探头500具有一个LED发射器506、一个位于腔509端部的光检测器508、一条韧性电路510和摩擦电连接指形512。探头500还具有连接端口519。在一个实施方案中,其中探头用作图9A中的可校准探头,绕贴式探头还具有一个把部分光线从发射器506引导到连接器502的光通道514(图12B)。在该实施方案中,在图9A和9B中用虚线515和515A标识的所有探头校准元件均位于腔516的内部(图12A),通过光通道514端部上的孔,该腔接收由光通道514引导过来的、耦合到连接器502的光线。如图12A所示,连接器上的电摩擦连接器520与绕贴式探头500的电连接器512相连。韧性电路把发射器506和检测器508连接到连接指形512。
在使用中,绕贴式探头放置在患者的手指上,光检测器508安置在发射器506的对面,这样可以接收发射器506射出的、由于在肉体媒质中传播而衰减的光线。
图13展示了医疗监测婴儿的另一个绕贴式探头530的实施方案。探头具有正好能缠住婴儿手指的第一韧性部分532。与韧性第一部分532相连的是带有发射器534(LED)和光检测器536的第二韧性部件。在一个把图9A中的探头用作图13的探头的实施方案中,光纤透镜538把发射器534射出的部分光线输送到探头530的连接器接口540。以这种方式,可以与图13的婴儿型探头一起使用具有光检测器的、相同的连接器502。另外,可以利用光通道或管道替代光纤透镜,把发射器534射出的部分光线输送到连接器接口540。同样的连接器542也可以用于婴儿探头530。另外,与图12的实施方案一样,图9A和9B中的、位于点线框515和515A内部的全部校准元件均位于连接器502的内部。
图14展示了用于医疗监测的另一种探头。图14的探头包括通过电缆552与连接器接口554相连的夹形(clip-on)探头550,该连接器接口与图13的连接器接口540和图12的连接器接口519是一样的。夹形探头带有发射器556和光检测器558。在本实施方案中,发射器556射出的一些光线进入如图13中的实施方案那样将光线导入连接器接口554的光纤透镜560。位于相同连接器502内的探头校准元件优选地包含在连接器502内部,该连接器优选地与图12和13实施方案中的连接器一致。
图15-15D展示了绕贴式探头600的另一种实施方案,该探头具有一个韧性探头部分602以及与电缆506相连的辅助连接器504,该电缆与光电血色计系统(未在图15中示出)相连。图15展示了整个探头600的透视图。图15A展示了连接器604的底边,图15C展示了绕贴部分602的顶视图,图15D展示了绕贴部分602的底视图。连接器604分为两部分:发射器部分610和连接部分612。发射器部分610优选地包含具有预选波长的发射器(例如LED)。该发射器部分610可以在一段时间内重复使用,优选地为几周或几个月,由此,可以进一步降低一次性使用的绕贴式部分602的成本。换句话说,不需要为每个绕贴部分602都配备发射器。然而,发射器部分610可拆卸地与连接器604的连接部分612相连,这将允许连接部分612在更长的时间内重复使用。
在这个实施方案中,绕贴部分602是柔韧的并且在每次使用之后可以丢弃,其成本极低。绕贴部分具有由聚合物或其它韧性材料制作的韧性层626,和位于韧性层626上的连接器接口614。连接器接口614具有电指形摩擦连接器616,该连接器可以和位于连接器604的连接部分612的底部的电指形摩擦连接器620(图15A)相连。绕贴部分602的电指形摩擦连接器616连接到韧性电路618,该韧性电路与检测器622相连、并且把它屏蔽起来(未示出)。连接中的两个与检测器622相连,第三个用来屏蔽,它优选地是传统的法拉第屏蔽,以便保护检测器免受电磁场等的干扰。
绕贴式探头600具有孔624,它提供了一个为发射器部分610中的发射器射出的光能提供了一个传输窗口。发射器安置得能够使光线通过发射器部分610中的孔628(图15A)射出,当连接器604安置在连接器接口614中时,该孔与绕贴部分602中的孔624匹配。这样,当连接器604插入到连接器接口614中并且发射器被激活时,光线从发射器部分610中的发射器射出,穿过发射器部分610中的孔628,又穿过绕贴部分602中的孔624。
在使用中,绕贴部分602缠在患者的手指上(例如手指),检测器622安置得可以接收通过孔624和至少部分通过手指传输的光线。例如,绕贴部分602可以以这样的方式缠在手指上,即检测器622与有光能射出的孔624相对。
在一个实施方案中,探头600用作图9A和9B中的可校准探头。在这个实施方案中,连接部分612具有位于图9A和9B的虚线框515、515A中的、位于连接部分612中的元件。以这种方式,校准元件可以重复使用,因此可以与发射器部分610中的LED一起使用,以便构成可校准实施方案。在这样的实施方案,发射器安置在发射器部分610中,这样,大部分光能通过孔628传输,部分光能传输到连接部分612末端上的光孔620(图15B)。连接部分612包含示于方框515和515A(图9A和9B)的、安置在连接部分612中的校准元件。
图15B展示了连接部分612的端视图,它展示了光通道620和两个为发射器部分中的LED(在本实施方案中,红光LED和红外LED背对背地连接)提供连接的电连接器613A、613B。
应当理解的是本发明的设备和方法可以用于任何需要测量透射或反射能量的场合,包括,但不仅限于此,对手指、耳垂或嘴唇的测量。因此,还有许多对本领域的技术人员来说是十分明显的其它实施方案。此外,本发明的设备和方法可以在任何对波长敏感的LED应用中使用。因此在不偏离发明宗旨或基本特性的前提下,本发明还可以体现在其它具体形式中。在各个方面中,所述的实施方案只是示例性的,而不是严格的。因此,发明范围由权利要求确定。所有包括在与这些权利要求等价的含义和范围之内的变动均包括在权利要求的范围内。
Claims (31)
1.一种发射具有预选波长的光能的可调光发射网络,包括:
供应预选源电流的电流源;
与电流源相连的发光二极管,发光二极管的波长可以随着选定的调节参数的变化而移动;和
与发光二极管并联的调节元件,调节元件的值具有阻性值,调节元件至少可以吸入预选源电流的第一部分使得预选源电流的第二部分流过发光二极管,预选源电流的第二部分使发光二极管产生具有预选波长的光能。
2.根据权利要求1的可调光发射网络,其特征在于可调元件包括一个电阻。
3.根据权利要求1的可调光发射网络,其特征在于可调参数是处于驱动电流的允许范围内的驱动电流。
4.根据权利要求1的可调光发射网络,其特征在于可调参数是处于驱动电压的允许范围内的驱动电压。
5.根据权利要求1的可调光发射网络,还包括响应发光二极管射出的光能进而产生指示光能强度的输出信号的检测器。
6.一种预校准发光传感器的方法,包括以下步骤:
判定流经光源并使之工作在预选波长所需的第一级电流;
定义第二级电流,第二级电流高于第一级电流,第二级电流定义了驱动电流;
选择阻性元件,该元件与光源并联在一起构成了可调光源网络,阻性元件能够吸入足量的驱动电流以便使电流的第一级流过光源;和
连接与光源并联的电阻。
7.一种用单个发光二极管产生两种波长的方法,包括以下步骤:
选择其波长会随着在驱动电流的允许范围内的、流过发光二极管的驱动电流的变化而移动的发光二极管;
连接电源和发光二极管以提供驱动电流;
利用在驱动电流的允许范围内的第一级驱动电流驱动发光二极管,使发光二极管激活并工作在第一波长,以作为对第一级驱动电流的响应;和
利用在驱动电流的允许范围内的、与第一级驱动电流不同的第二级驱动电流驱动发光二极管,使发光二极管激活并工作在第二波长,以作为对第二级驱动电流的响应。
8.根据权利要求7的方法,其特征在于利用发光二极管向待测媒质发射光能,还包括以下步骤:
发光二极管工作在第一波长时,发射透过待测媒质具有第一波长的第一光能,根据光能在待测媒质中传播时光能的第一预定衰减特性选择第一波长,测量发光二极管射出的、经衰减后的光能;和
发光二极管工作在第二波长时,发射透过待测媒质具有第二波长的第二光能,根据光能在待测媒质中传播时光能的第二预定衰减特性选择第二波长,测量发光二极管射出的、经衰减后的光能。
9.根据权利要求8的方法,其中,所述方法包括判定血氧饱和度,待测媒质包括具有流动血液的部分人体,还包括以下步骤:
连接电源和工作在与第一和第二波长均不相同的第三波长的第二发光二极管,第一和第二波长之间的波长变化具有预选值;
发射透过待测媒质具有第三波长的第三光能;
测量透过待测媒质的第三光能;和
计算血氧饱和度。
10.根据权利要求9的方法,还包括计算与待测媒质、具有已知值的第一波长、在具有预选值的第一和第二波长之间的波长变化有关的其它参数的方法,所述方法包括以下步骤:
判定第二波长的值;和
计算血液的另一个参数。
11.根据权利要求10的方法,其特征在于另一个参数包括carboxyhemoglobin(含一氧化碳的血红素)的饱和度。
12.根据权利要求10的方法,其特征在于另一个参数包括散射。
13.根据权利要求7的方法,还包括以下步骤:
利用可调阻性元件调节第一发光二极管使得波长随电流增量的变化而发生的变化与预选的波长变化匹配。
14.根据权利要求13的方法,其特征在于可调阻性元件包括一个电阻。
15.根据权利要求13的方法,其特征在于所述调节步骤包括以下步骤:
并联可调阻性元件和第一发光二极管;
选择可调电阻的阻值使得第一发光二极管随着电流增量的变化而产生预定变化。
16.一种光电血色计传感器,包括:
产生具有第一已知波长的光线的第一发光装置,该装置在第一电压被激活;和
与第一发光装置并联的信息元件。
17.一种权利要求16的光电血色计传感器,其特征在于信息元件工作在低于第一电压值的电压值。
18.一种权利要求16的光电血色计传感器,其特征在于信息元件包括电阻。
19.一种权利要求16的光电血色计传感器,其特征在于信息元件包括阻性网络。
20.根据权利要求16的光电血色计传感器,其特征在于信息元件包括存储装置。
21.根据权利要求16的光电血色计传感器,其特征在于发光装置包括发光二极管。
22.根据权利要求16的光电血色计传感器,其特征在于信息元件包括编码电阻,编码电阻的阻值指示第一已知波长值,其阻值足够大使得在第一发光装置工作于激活状态时编码电阻不显著地吸入电流。
23.根据权利要求16的光电血色计传感器,其特征在于信息元件包括安全元件,安全元件指示光电血色传感器是否是预定的类型,安全元件的值使得当第一发光装置工作于激活状态时它吸入的电流极小。
24.根据权利要求23的光电血色计传感器,其特征在于安全元件包括电阻,其阻值足够大使得当第一发光设备工作于激活状态时电阻吸入的电流极小。
25.一种调节发光二极管使之工作在位于一定波长范围内的预选波长的方法,包括以下步骤:
选择发光二极管,其波长可以随着在驱动电流的允许范围内的驱动电流的变化而移动;
利用第一驱动电流驱动发光二极管;
当工作在第一驱动电流时,测量发光二极管的波长;和
如果发光二极管没有工作在预选波长,那么在驱动电流的允许范围内把驱动电流调节到第二驱动电流,使得发光二极管工作在预选波长。
26.一种用于发射和检测光线的传感器,包括:
至少一个发光元件,发光元件具有带有中心发射波长的发射谱;
第一和第二光检测器,发射谱位于第一和第二光检测器的响应区域内部;
光定向部件,用于把至少有一个的发光元件射出的光线指向第一和第二光检测器;和
滤波器,安置在第二光检测器和至少一个发光元件之间,滤波器的过渡带包括中心发射波长。
27.根据权利要求26的传感器,包括光电血色传感器,所述至少一个发光元件包括第一和第二发光二极管,第一发光二极管具有红光波段的中心波长,第二发光二极管具有红外波段的中心波长,滤波器的过渡带包括第一发光二极管的中心波长。
28.根据权利要求26的传感器,光定向部件包括集成光球,在其上安置有第一和第二光检测器,以便接收来自至少一个发光元件的、基本上等量的两部分光线。
29.根据权利要求26的传感器,光定向部件包括分束元件,它基本上等分来自至少一个发光元件的光线,并把基本上等分的两部分光线指向第一和第二光检测器。
30.一种判定发光元件的中心波长的方法,包括以下步骤:
提供一组预定的比值,每个预定的比值对应于相应的中心波长;
把发光元件射出的光线传输到第一光检测元件,得到第一光强;
透过使光线衰减的滤波器,把发光元件射出的光线传输到第二光检测元件,得到第二光强;
计算第二光强和第一光强的比值;和
对比该比值和所述一组预定的比值,来查找发光元件的中心波长。
31.根据权利要求30的方法,其特征在于第一和第二光检测元件包括相同的光检测元件,发射次序顺序地进行。
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
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US08/478,493 US5758644A (en) | 1995-06-07 | 1995-06-07 | Manual and automatic probe calibration |
US08/478,493 | 1995-06-07 |
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CN1192271A true CN1192271A (zh) | 1998-09-02 |
CN1113225C CN1113225C (zh) | 2003-07-02 |
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US (10) | US5758644A (zh) |
EP (3) | EP0832421B1 (zh) |
JP (2) | JP3837161B2 (zh) |
CN (1) | CN1113225C (zh) |
AT (2) | ATE223035T1 (zh) |
AU (1) | AU704383B2 (zh) |
CA (2) | CA2221446C (zh) |
DE (2) | DE69637999D1 (zh) |
DK (2) | DK1238627T3 (zh) |
ES (2) | ES2330196T3 (zh) |
HK (2) | HK1009848A1 (zh) |
PT (2) | PT832421E (zh) |
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CN105928895A (zh) * | 2011-02-09 | 2016-09-07 | 霍尼韦尔国际公司 | 用于使用浸胶带探测各种气体的波长谱分析的系统和方法 |
CN105928895B (zh) * | 2011-02-09 | 2020-01-10 | 霍尼韦尔国际公司 | 用于使用浸胶带探测各种气体的波长谱分析的系统和方法 |
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