CN1929777A - 用于检测心脉和减小传感器中功率消耗的技术 - Google Patents
用于检测心脉和减小传感器中功率消耗的技术 Download PDFInfo
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Abstract
本发明提供一种用于感测来自一传感器(101)的一信号中的心脉的低功率技术。一脉冲检测块(102)感测所述传感器信号并确定其信噪比。在将所述信噪比与一阈值相比之后，所述传感器中的发光元件的驱动电流经动态调整以减小功率消耗，同时将所述信噪比维持在一充足的电平下。所述传感器信号的信号分量可通过识别心脏收缩过渡来测量。使用一最大最小导数平均机制来检测所述心脏收缩过渡。将移动最小值(301)和移动最大值(304)与所述移动最小值和移动最大值的缩放和(312、313)相比，来识别所述心脏收缩过渡。一旦识别出所述信号分量，就将所述信号分量与一噪音分量相比以计算所述信噪比。
Description
技术领域
本发明涉及用于检测心脉和减小传感器及血氧计系统中功率消耗的技术，且更具体而言，涉及用于响应于脉冲的信噪比，将传感器信号中的心脉与噪音区分开并调整提供给发光元件的驱动电流，以便减小功率消耗的技术。
背景技术
脉冲血氧定量法是一项常用来测量血液化学特征的技术，血液化学特征包括(但不限于)动脉血中血红蛋白的血氧饱和度、供应给组织的个体血液脉动的体积，和对应于患者的每一次心跳的血液脉动率。
使用非侵入性传感器来完成这些特征的测量。传感器具有光源，诸如发光二极管(LED)，其将光散射过患者组织中有血液灌注到组织的一部分中。传感器还具有光电检测器，其光电地感测组织中不同波长的光吸收。光电检测器产生脉冲血氧计信号，表示血液所吸收的光的量。所吸收的光的量接着用来计算待测量的血液成分的量。
选择散射过组织的光，使其具有由血液吸收的、数量表示血液中的血液成分的量的一个或一个以上波长。所传输而散射过组织的光的量将根据组织中血液成分的变化量和相关的光吸收而改变。
为测量血氧含量，根据用于测量血氧饱和度的已知技术，血氧计传感器通常具有适用于产生至少两种不同波长的光的光源，且采用光电检测器感测这些波长。或者，典型的脉冲血氧计将使用两个LED以红光和红外光照射患者，以获得两个不同的检测器信号。
光电检测器产生的脉冲血氧计信号经常含有由血氧计电子设备、患者和环境引入的噪音成分。噪音信号具有低的信噪比。当脉冲血氧计信号的信噪比过低时，脉冲血氧计不能精确地识别出血氧饱和度。
为提高脉冲血氧计信号的信噪比，脉冲血氧计系统通常以大量电流来驱动LED。脉冲血氧计中的伺服系统将尽可能多的电流驱动过LED，而不导致血氧计超出范围(意即，驱动到全轨)。大的驱动电流使得LED产生更多光和消耗更多功率。因为光电检测器能感测更多的LED光，所以脉冲血氧计信号的信噪比更高。
增加LED的驱动电流以提高脉冲血氧计信号的信噪比，将使系统消耗超乎想象的大量功率。大量的功率消耗可能会成为用电池操作的血氧计系统的一大问题。
因此希望提供一种脉冲血氧计系统，其消耗较少的功率，而不会负面地折损脉冲血氧计信号的信噪比。
发明内容
本发明提供CPU循环有效技术用于感测传感器信号中的心脉。举例而言，传感器信号可以是由脉冲血氧计传感器中的光电检测器产生的脉冲血氧计信号。此传感器信号的信号分量通过识别心动周期的潜在心脏收缩过渡来加以测量。心脏收缩过渡使用导数平均机制来检测。将平均导数的移动最小值和移动最大值与最小值和最大值的缩放和相比，来识别该心脏收缩过渡。心脏收缩过渡对应于此传感器信号的一信号分量。将此信号分量与一噪音分量相比以确定信号的信噪比。
本发明还提供用于减小传感器中的功率消耗的技术。在确定了脉冲血氧计的信噪比之后，将此信噪比与一阈值相比。响应于此比较的输出，动态调整传感器中发光元件的驱动电流以减小功率消耗，且将信噪比维持在充足的电平下以用于信号处理。
本发明还提供用于感测和调整互阻抗放大器的增益以减小环境噪音在传感器中的效应的技术。增益控制反馈回路在发光元件关闭时感测传感器信号的量值。增益控制回路可包括用于有效控制互阻抗放大器的增益的此信息。
为进一步理解本发明的性质和优势，可参考结合附图所说明的以下实施方式。
附图说明
图1说明根据本发明的实施例的具有减小的功率消耗的脉冲血氧计系统的方框图；
图2是流程图，说明用于识别根据本发明的实施例的脉冲血氧计信号的心脏收缩期的过程；
图3A至图3C是曲线图，说明如何根据本发明的实施例于脉冲血氧计信号中识别心脏收缩过渡；和
图4说明根据本发明的实施例的脉冲血氧计系统的一部分，此脉冲血氧计系统具有互阻抗放大器、∑-Δ调制器、模拟到数字转换器和增益控制反馈回路。
具体实施方式
本发明的技术可用于脉冲血氧计系统的情景中。脉冲血氧计系统自脉冲血氧计传感器中的光电检测器接收脉冲血氧计信号。图1说明根据本发明的实施例的脉冲血氧计系统的方框图。此脉冲血氧计系统包括血氧计传感器101。
本发明的血氧计传感器可利用任何适当数量的发光元件。举例而言，本发明的传感器可具有1、2、3或4个发光元件。在图1的实例中，传感器101具有两个LED，110和111，其发射两种不同波长的光。
传感器101还包括光电检测器112，其在光经过患者组织之后感测来自LED 110和111的光。脉冲血氧计系统还包括反馈回路电路110和LED驱动接口104。反馈回路电路110包括脉冲检测块102和阈值比较块103。
光电检测器112将脉冲血氧计信号传输至脉冲检测块102。脉冲检测块102具有伺服系统，其通过识别心脏收缩过渡来测量脉冲血氧计信号的信号分量。脉冲检测块102和阈值比较块103形成围绕传感器的反馈回路110，以控制LED的驱动电流和脉冲血氧计信号的信噪比，此将在下文中详细论述。
心脉可分成心脏舒张期和心脏收缩期。心脏收缩期的特征通常是由于心脏收缩导致的值的快速变化。心脏舒张期的特征通常是由于心室舒张和再次充血导致的值的逐步变化。
使用三步骤最大最小导数平均机制来检测脉冲血氧计信号中的心脏收缩过渡，将在下文中进一步详细地论述此机制。接着使用鉴定程序过滤出假阳性。所得数据含有与脉冲血氧计信号中的非心脏收缩期分离的心脏收缩过渡。
接着，脉冲检测块102将脉冲血氧计信号的心脏收缩部分的振幅与噪音分量相比，以产生脉冲血氧计信号的信噪比的值。随后，阈值比较块103将此信噪比与阈值电平相比，以确定信噪比是否高到足以使脉冲血氧计信号可用于精确计算脉冲率和氧饱和度。过多的噪音会干扰信号中的脉冲率和氧饱和度信息。噪音可使信号降级到使其无法用于精确地计算脉冲率或氧饱和度的程度。
阈值比较块103较佳含有两个滞后阈值电平。在此实施例中，阈值比较块103感测信噪比是否大于最大阈值电平或小于最小阈值电平。在一个实例中，最大阈值电平可表示128∶1的信噪比，且最小阈值电平可表示8∶1的信噪比。这些仅是阈值电平的两个实例。它们并非意图限制本发明的范畴。举例而言，先前技术的血氧计系统以10000∶1或更高的信噪比运作，因为这些系统将LED驱动到尽可能得亮。
如果信噪比大于最大阈值电平，那么阈值比较块103向LED驱动接口104发送信号，以减小LED电流。基于此信噪比值，阈值比较块103可确定需要减小多少LED驱动电流来降低此信噪比，同时将此信号电平维持在最小和最大阈值电平内。LED驱动接口104通过将LED驱动电流降低到由阈值比较块103指示的值来作出回应。
反馈回路连续监测脉冲血氧计信号的信噪比，并动态调整LED驱动电流和随后的系统增益，直到信噪比小于最大阈值。血氧计系统通过大体减小LED驱动电流(相对于先前技术的系统)，同时将脉冲血氧计信号的信噪比维持在可接受的范围内，米节省功率。
信噪比还可能会因为诸多原因而跌落得过低。举例而言，如果患者的血氧饱和度降低，那么脉冲血氧计中的噪音可增加，或信号分量的强度可降低。在任何事件中，图1的系统均感测脉冲血氧计信号的量值过低的时刻并相应地增加LED驱动电流。
如果信噪比小于最小阈值电平，那么阈值比较块103向LED驱动接口104发送信号，以增加LED电流。基于此信噪比值，阈值比较可确定需要增加多少LED驱动电流来增加此信噪比，同时将此信号维持在最小和最大阈值电平内。LED驱动接口104通过将LED驱动电流增加到由阈值比较系统指示的值来作出回应。
反馈回路连续监测脉冲血氧计信号的信噪比，并动态调整LED驱动电流，直到信噪比大于最小阈值电平。最小阈值表示对于可精确计算脉冲率和氧饱和度的信噪比的最小可允许值。
如果信噪比在最大阈值电平与最小阈值电平之间，那么血氧计系统将LED驱动电流维持在稳定值。血氧计系统维持平衡，直到脉冲血氧计信号的信噪比移动到阈值范围以外。因此，本发明的血氧计系统含有如图1所示的动态反馈回路。动态反馈回路自动调整LED的驱动电流，以减小传感器中的功率消耗并将信噪比维持在可接受的电平，以实现精确计算血氧饱和度水平的目的。
根据本发明的较佳实施例，脉冲检测块102中伺服系统的硬件在LED驱动104试图驱动LED的功率与LED实际产生的辐射输出功率之间维持可预测的关系。通过在输入和输出功率之间提供可预测的关系，反馈回路更可能在明显较短的时间内自脉冲血氧计信号获得氧饱和度，而要求伺服系统的较少执行量。
随着脉冲血氧计信号的增益增加，信号分量增加大体快于噪音分量(至少在低于最高增益设置值的程度)。应理解在特定系统中增加脉冲血氧计信号的增益对信噪比的影响。增益的某些组合可使得在脉冲血氧计信号中存在更多噪音。因此，脉冲检测块中的增益级较佳利用增益对噪音可变性的特征。
举例而言，将使用模拟到数字转换器取样所得的来自光电检测器的信号馈入增益块中。增益块包括若干增益级以实现已知的响应。在每一增益级测量噪音，且接着将其存储以在稍后用于计算信噪比。
现在论述用于识别血氧计传感器所产生的脉冲血氧计信号的心脏收缩部分的技术。本发明的心脏收缩识别使用三步骤最大最小导数平均机制，以便检测心脏收缩事件。
图2说明用于识别脉冲血氧计信号的心脏收缩期的一个方法。在第一个步骤201中，得出脉冲血氧计信号的导数的移动平均数。在第二个步骤202中，得出第一个步骤201的输出的移动平均数。在第三个步骤203中，得出第二个步骤202的输出的移动平均数。
接着，在步骤204得出第三个步骤的输出的移动最大值和移动最小值。在步骤205，通过将此移动最小值和移动最大值与移动最小和最大值的缩放和相比，来检测心脏收缩过渡。举例而言，移动最小和最大值的缩放和可为最小和最大移动平均数的分数和。
当步骤204的最小输出变得小于最大和最小移动平均数的分数和时，系统确定脉冲血氧计信号正进入心脏收缩。当步骤204的最小输出变得大于最大和最小移动平均数的分数和时，系统确定脉冲血氧计信号正退出心脏收缩。
可选择两个预定分数和为任何适当值。在特定实例中，在最小导数输出变得小于第三级最小和最大移动平均数的和的1/16时，系统可确定脉冲血氧计信号正进入心脏收缩。在另一实例中，在最小导数输出变得大于第三级最大和最小移动平均数的和的1/8时，系统可确定脉冲血氧计信号正退出心脏收缩。这两个实例并非意图限制本发明的范畴。同样可使用许多其它的分数值来识别心脏收缩过渡。
本发明的这些技术可使用CPU、RAM和ROM有效算法来检测和鉴定脉冲。采用与先前技术的血氧计技术相当水平的饱和度和脉冲率性能，需要最小限度的处理器资源来执行血氧定量计算。
图3A中展示这些计算结果的实例波形。波形303是脉冲血氧计信号的导数的实例。波形301和304分别是此脉冲血氧计信号的最小和最大移动平均数的实例。波形302是三步骤移动平均数的输出信号的实例。
移动平均数的输出是脉冲血氧计信号的导数的平滑和延迟形式。最小输出追踪负走向且落后于正走向。最大输出追踪正走向且落后于负走向。这些关系是检测潜在的心脏收缩期的关键。
图3B展示最小移动平均数301的实例，其具有表示第三级最小和最大移动平均数的和的1/16的波形313。图3B还展示波形312的实例，其表示第三级最小和最大移动平均数的和的1/8。
根据本发明的一个实施例，在步骤205将波形312和313与最小移动平均数波形301相比，以识别脉冲血氧计信号的心脏收缩期。或者，可使用最小和/或最大移动平均数的其它缩放和，以识别脉冲血氧计信号中的心脏收缩期。图3B中识别信号301中心脏收缩的开始和结束。信号301与信号312/313的交叉点之间的时段界定心脏收缩期。
图3C展示应用于原始脉冲血氧计信号320时心脏收缩期识别。心脏收缩期包括脉冲血氧计信号320之峰值(意即最大值)与随后的谷值(意即最小值)之间的时间。图3C识别实际的心脏收缩期以及下一脉冲的重搏切迹。
在识别出心脏收缩期后，在步骤206对心脏收缩脉冲应用基于典型的生理脉冲特征的独特脉冲鉴定测试。完全脉冲鉴定测试移除假阳性心脏收缩检测(例如重搏切迹)和具有不充分的信噪比的脉冲。假阳性是在步骤205中被错误地识别成是心脏收缩过渡的信号部分。在步骤206中使用脉冲鉴定以过滤出步骤205中所识别的假阳性。图2的步骤可实施于软件或硬件中。
脉冲鉴定测试鉴定脉冲血氧计信号中的心脉。设计脉冲鉴定测试以识别具有足够的信噪比的心脉，以用于测量脉冲率和血氧饱和度。脉冲鉴定测试可包括任何数量的技术，包括传统的脉冲鉴定技术。
现在论述根据本发明的特定实施例的脉冲鉴定测试的一些实例。鉴定是将特定的脉冲特征与确定的阈值相比。举例而言，脉冲鉴定将心脏收缩面积、宽度和子峰值的数量与固定阈值相比。将心脏舒张面积、宽度和子峰值的数量与阈值相比。将心脏收缩面积和宽度与心脏舒张面积和宽度相比。将脉冲面积和宽度与阈值相比。以上所有各自均与所检测到的最后N个脉冲相比。
可使用通过这些鉴定的脉冲来测量脉冲率。为鉴定心脏收缩期以进行氧饱和度计算，使用以下额外的鉴定。比较红外脉冲检测与红光脉冲检测之间的落后/领先时间。将脉冲大小与经鉴定的N个脉冲相比。将红外信号与红光信号之间移动平均数的最拟合曲线的统计学有效的系数与固定阈值相比。将饱和度变化率与固定阈值相比。可使用通过这些额外鉴定的脉冲来测量氧饱和度。
在脉冲鉴定测试过滤出假阳性之后，识别心脏收缩期。心脏收缩期表示脉冲血氧计信号的信号分量。此脉冲血氧计信号的信噪比将通过比较心脏收缩期的强度与此脉冲血氧计信号的噪音分量来算得。
根据一个实施例，使用在各种增益值测量脉冲血氧计信号中的噪音的独立仪器，来预先计算脉冲血氧计传感器中的噪音分量。接着将测量得到的噪音分量存储到存储器中以供稍后使用。随后将所存储的噪音分量与特定增益值下心脏收缩脉冲的大小相比，以确定脉冲血氧计信号的信噪比。
根据另一个实施例，动态测量脉冲血氧计系统的噪音。这些噪音测量可包括电噪音、环境光造成的环境噪音和/或由患者造成的噪音(例如运动)。动态噪音测量在整个脉冲血氧计传感器的操作过程中连续更新。将更新得到的噪音分量连续与脉冲相比以计算脉冲血氧计信号的更为精确的信噪比。
一旦计算得到脉冲血氧计信号的信噪比，则确定信噪比是否在可接受的范围内。基于相关噪音分量选择此可接受的范围，以便精确计算氧饱和度和脉冲率。如果该比率在可接受的范围之外，那么上文关于图1所论述的反馈回路调整LED驱动电流以将信噪比带到该可接受的范围内。
本发明具有如下优势：与先前技术相比，特别是在出现患者运动干扰的情况下，本发明需要更少的伺服系统执行量来获得和维持信号的氧饱和度。在许多先前技术的血氧计系统中均以较大的电流驱动LED，且脉冲血氧计信号充满其整个系统的动态范围。只要患者开始移动，那么血氧计信号便超过系统的电流动态范围，且实质上便有信号丢失(意即，扁平线，无效信号)。需要额外的伺服系统执行量来重新获得信号。在伺服系统执行的同时，传感器信号不可用；因此，血氧计无法自脉冲血氧计信号计算脉冲率或氧饱和度。
另一方面，在本发明中LED驱动电流大体是减小的。动态范围相对于脉冲血氧计信号的大小大大增加，因为信号已通过削减LED驱动电流而大大减小。现在血氧计信号可在该动态范围内有更大的空间移动，而无需额外的伺服系统执行量或对LED设置值进行改变。在本发明中，患者可保持精力旺盛到处移动，而不会使伺服系统执行来试图重新获得信号。本发明的技术可允许血氧计系统赋予患者运动大得多的容忍度。
脉冲检测块102可包括互阻抗(I-V)放大器或转换器401，其将来自光电检测器112的电流信号转换成电压信号，如图4所示。周围环境中的环境光将直流偏压分量添加到脉冲血氧计信号中。此直流偏压将脉冲血氧计信号变换到更高，使得更接近互阻抗放大器的动态范围轨。
根据本发明的实施例，当LED 110-111接通或关闭以对进入传感器101中的环境光和/或噪音提供连续实时的测量的时段内，模拟到数字(A-D)转换器402对互阻抗放大器401的输出信号进行取样。此部件还可用于提供在A-D转换器402之输出端的信号的量值的有关信息。
将来自A-D转换器402之信号量值的有关信息反馈而使其经过增益控制反馈回路403，来为互阻抗放大器401选择适当的增益。举例而言，增益控制反馈回路403使互阻抗放大器401的互阻抗增益增加或降低，来减小和/或调节环境直流偏压对信号的影响。此实时测量还可用于确定传感器关闭条件，测量电学和光学噪音，检测信号中的瞬变过程，和检测患者运动。
在传感器的正常操作期间，可采用任何适当的方式对LED施加脉冲和撤销脉冲，以对环境光和其它噪音源提供连续(多路)实时的测量。举例而言，可采用以下方式交替接通和关闭一个红光LED和一个红外LED：接通红光LED且关闭红外LED，接着关闭红光LED且接通红外LED，接着关闭两个LED，接着接通红光LED且关闭红外LED等，以此序列重复。在另一实例中，可采用以下方式交替接通和关闭一个红光LED和一个红外LED：接通红光LED且关闭红外LED，接着关闭两个LED，接着关闭红光LED且接通红外LED，接着关闭两个LED，接着接通红光LED且关闭红外LED等，以此序列重复。这些模式仅用作实例，而并不意图限制本发明的范畴。
∑-Δ调制器410也接收互阻抗放大器402的输出信号。调制器410将来自光电检测器的信号解调成独立的红光和红外分量。可使用由微控制器运行的软件和韧件程序在数字域中执行解调函数。使用∑-Δ调制的多位ADC的进一步细节将在被共同转让给EthanPetersen等人的共同待决的美国专利申请案中论述(与本案同时申请)，(代理人案号009103-020300US)，该案以引用的方式并入本文中。
如所属领域的技术人员所了解，本发明可以其它特定形式来体现，而不脱离本发明的本质特征。因此，前述描述意在对以上权利要求书中所阐述的本发明的范畴进行说明而非限制。
举例而言，图4中所示的脉冲检测块102中的组件可实施于除了脉冲血氧计系统以外的系统中。这些组件也可减小来自其它类型传感器的信号中的噪音的影响。
Claims (24)
1.一种脉冲血氧计系统，其包含：
一驱动接口，其控制一脉冲血氧计传感器中的发光元件的驱动电流；和
一反馈回路，其耦合在所述脉冲血氧计传感器和所述驱动接口周围，所述反馈电路基于在一脉冲血氧计信号的一信噪比与一阈值之间进行一比较所得的结果，动态调整所述发光元件的所述驱动电流，
其中所述脉冲血氧计信号由所述脉冲血氧计传感器中的一光电检测器来产生。
2.根据权利要求1所述的脉冲血氧计系统，其中如果所述脉冲血氧计信号的所述信噪比大于一最大阈值，那么所述反馈回路使所述发光元件的所述驱动电流降低，且如果所述脉冲血氧计信号的所述信噪比小于一最小阈值，那么所述反馈回路使所述发光元件的所述驱动电流增加。
3.根据权利要求1所述的脉冲血氧计系统，其中所述反馈回路进一步包含：
一脉冲检测块，其计算所述脉冲血氧计信号的所述信噪比；和
一比较器，其执行所述脉冲血氧计信号的所述信噪比与所述阈值的所述比较。
4.根据权利要求3所述的脉冲血氧计系统，其中所述脉冲检测块计算所述脉冲血氧计信号的一导数的一移动平均数以产生一第一输出，计算所述第一输出的一移动平均数以产生一第二输出，计算所述第二输出的一移动平均数以产生一第三输出，和识别所述第三输出的一移动最小值和一移动最大值。
5.根据权利要求4所述的脉冲血氧计系统，其中所述脉冲检测块将所述第三输出的所述移动最小值和所述移动最大值与所述第三输出的所述移动最小值和所述移动最大值的一缩放和相比，以产生识别一心脏收缩期的一第四输出。
6.根据权利要求5所述的脉冲血氧计系统，其中所述脉冲血氧计系统使用脉冲鉴定测试过滤出所述第四输出中的假阳性，以产生所述脉冲血氧计信号的一信号分量。
7.根据权利要求6所述的脉冲血氧计系统，其中所述脉冲血氧计系统将所述第四输出中的心脏收缩面积、宽度和子峰值的数量与第一阈值相比；将所述第四输出中的心脏舒张面积、宽度和子峰值的数量与第二阈值相比；将心脏收缩面积和宽度与心脏舒张面积和宽度相比；将脉冲面积和宽度与第三阈值相比。
8.根据权利要求6所述的脉冲血氧计系统，其中所述脉冲血氧计系统将所述第四输出中的心脏收缩面积、宽度和子峰值的数量；所述第四输出中的心脏舒张面积、宽度和子峰值的数量；及脉冲面积和宽度与所检测到的N个心脉相比。
9.根据权利要求6所述的脉冲血氧计系统，其中所述脉冲血氧计系统执行额外的鉴定测试，以通过将红外脉冲检测与红光脉冲检测之间的落后/领先时间相比，将脉冲大小与经鉴定的N个脉冲相比，将所述红外信号与所述红光信号之间一移动平均数的一最拟合曲线的一统计学有效的系数与阈值相比，及将一饱和度变化率与阈值相比，来产生所述信号分量。
10.根据权利要求6所述的脉冲血氧计系统，其中所述脉冲血氧计系统将所述信号分量与一确定的噪音分量相比，以计算所述信噪比。
11.根据权利要求6所述的脉冲血氧计系统，其中所述脉冲血氧计系统将所述信号分量与一噪音分量相比，所述噪音分量是通过对所述脉冲血氧计信号中的噪音进行一连续更新的测量来获得。
12.根据权利要求1所述的脉冲血氧计系统，其中一减小数量的处理器资源被要求来用于对所述脉冲血氧计信号执行血氧定量计算。
13.根据权利要求6所述的脉冲血氧计系统，其中所述脉冲检测块使用CPU、RAM和ROM有效算法来检测和鉴定脉冲。
14.一种用于减小一脉冲血氧计传感器中的功率消耗的方法，所述方法包含：
向所述脉冲血氧计传感器中的发光元件提供驱动电流；和
确定由所述脉冲血氧计传感器中的一光电检测器产生的一脉冲血氧计信号的一信噪比；和
基于在所述脉冲血氧计信号的所述信噪比与一阈值之间进行一比较所得的结果，动态调整所述发光元件的所述驱动电流。
15.根据权利要求14所述的方法，其中动态调整所述发光元件的所述驱动电流进一步包含：
如果所述脉冲血氧计信号的所述信噪比小于一最小阈值，那么增加提供给所述发光元件的所述驱动电流；和
如果所述脉冲血氧计信号的所述信噪比大于一最大阈值，那么降低提供给所述发光元件的所述驱动电流。
16.根据权利要求15所述的方法，其中确定所述脉冲血氧计信号的所述信噪比进一步包含：
计算所述脉冲血氧计信号的一导数的一移动平均数以产生一第一输出；
计算所述第一输出的一移动平均数以产生一第二输出；
计算所述第二输出的一移动平均数以产生一第三输出；和
识别所述第三输出的一移动最小值与一移动最大值。
17.根据权利要求16所述的方法，其中确定所述脉冲血氧计信号的所述信噪比进一步包含：
将所述第三输出的所述移动最小值和所述移动最大值与所述第三输出的所述移动最小值和所述移动最大值的一缩放和相比，以产生识别一心脏收缩期的一第四输出。
18.根据权利要求17所述的方法，其中确定所述脉冲血氧计信号的所述信噪比进一步包含：
使用脉冲鉴定测试过滤出所述第四输出中的假阳性，以产生所述脉冲血氧计信号的一信号分量。
19.根据权利要求18所述的方法，其中确定所述脉冲血氧计信号的所述信噪比进一步包含：
将所述信号分量与一确定的噪音分量相比，以计算所述信噪比。
20.根据权利要求18所述的方法，其中确定所述脉冲血氧计信号的所述信噪比进一步包含：
将所述信号分量与一噪音分量相比，所述噪音分量是通过对所述脉冲血氧计信号中的噪音进行一连续更新的测量来获得。
21.一种用于识别由一脉冲血氧计传感器产生的一脉冲血氧计信号中的心脏收缩过渡的方法，所述方法包含：
计算所述脉冲血氧计信号的一导数的一移动平均数以产生一第一输出；
计算所述第一输出的一移动平均数以产生一第二输出；
计算所述第二输出的一移动平均数以产生一第三输出；
识别所述第三输出的一移动最小值与一移动最大值；
将所述第三输出的所述移动最小值和所述移动最大值与所述第三输出的所述移动最小值和所述移动最大值的一缩放和相比，以产生一第四输出；和
使用脉冲鉴定程序过滤出所述第四输出中的假阳性，以产生对应于所述脉冲血氧计信号中的一心脏收缩过渡的一第五输出。
22.一种耦合至一传感器的系统，所述系统包含：
一互阻抗放大器，其自所述传感器接收一电流信号，并基于一互阻抗增益将所述电流信号转换成一电压信号；
一模拟到数字转换器，其将所述电压信号转换成一数字信号；和
一反馈回路，其提供一反馈信号，所述反馈信号用于在所述传感器中的发光元件接通或关闭时，指示来自所述互阻抗放大器的所述电压信号的一量值，
其中所述互阻抗增益响应于所述反馈信号加以调整，以调节所述电压信号上的环境直流偏压。
23.根据权利要求22所述的系统，其中所述传感器是含有一光电检测器的一脉冲血氧计传感器。
24.根据权利要求22所述的系统，其进一步包含：
一脉冲检测器，其计算来自所述传感器的所述信号的所述信噪比；
一比较器，其将所述信噪比与一阈值相比；和
一驱动接口，其控制所述发光元件的驱动电流。
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| EP (1) | EP1722674B1 (zh) |
| JP (1) | JP4756027B2 (zh) |
| CN (1) | CN1929777A (zh) |
| AT (1) | ATE391454T1 (zh) |
| AU (1) | AU2005216976A1 (zh) |
| CA (1) | CA2556724C (zh) |
| DE (1) | DE602005005964T2 (zh) |
| ES (1) | ES2306122T3 (zh) |
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2005
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- 2005-02-25 ES ES05723887T patent/ES2306122T3/es active Active
- 2005-02-25 WO PCT/US2005/006208 patent/WO2005082240A1/en active Application Filing
- 2005-02-25 AU AU2005216976A patent/AU2005216976A1/en not_active Abandoned
- 2005-02-25 DE DE602005005964T patent/DE602005005964T2/de active Active
- 2005-02-25 CA CA2556724A patent/CA2556724C/en active Active
- 2005-02-25 EP EP05723887A patent/EP1722674B1/en active Active
- 2005-02-25 JP JP2007501032A patent/JP4756027B2/ja not_active Expired - Fee Related
- 2005-02-25 MX MXPA06009754A patent/MXPA06009754A/es not_active Application Discontinuation
- 2005-02-25 AT AT05723887T patent/ATE391454T1/de not_active IP Right Cessation
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| US10426360B2 (en) | 2013-05-15 | 2019-10-01 | Pulseon Oy | Portable pulse measuring device |
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| WO2020150973A1 (zh) * | 2019-01-24 | 2020-07-30 | 深圳市汇顶科技股份有限公司 | 信号调节方法、装置、芯片、设备及存储介质 |
| CN109863703B (zh) * | 2019-01-24 | 2022-07-08 | 深圳市汇顶科技股份有限公司 | 信号调节方法、装置、芯片、设备及存储介质 |
| CN111529829A (zh) * | 2020-07-07 | 2020-08-14 | 深圳市汇顶科技股份有限公司 | 一种ppg设备的信号调整方法和ppg设备 |
Also Published As
| Publication number | Publication date |
|---|---|
| CA2556724A1 (en) | 2005-09-09 |
| EP1722674B1 (en) | 2008-04-09 |
| US20050187446A1 (en) | 2005-08-25 |
| JP2007523732A (ja) | 2007-08-23 |
| US20070208240A1 (en) | 2007-09-06 |
| US7499740B2 (en) | 2009-03-03 |
| CA2556724C (en) | 2014-02-18 |
| EP1722674A1 (en) | 2006-11-22 |
| US7162288B2 (en) | 2007-01-09 |
| JP4756027B2 (ja) | 2011-08-24 |
| WO2005082240A1 (en) | 2005-09-09 |
| DE602005005964D1 (de) | 2008-05-21 |
| DE602005005964T2 (de) | 2009-05-20 |
| ES2306122T3 (es) | 2008-11-01 |
| ATE391454T1 (de) | 2008-04-15 |
| AU2005216976A1 (en) | 2005-09-09 |
| MXPA06009754A (es) | 2007-03-15 |
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