CN1933769A - 血氧计环境光取消 - Google Patents
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Abstract
一种脉冲血氧计方法和设备,其(1)以一在一调制频率与一通用电力线频率(50、60、100和120)的公倍数之间的间隔提供一陷波滤波器(46),并且(2)也提供一大于人体的最高脉冲率且低于50、60、100或120Hz的任何谐波的解调频率,以对环境光干扰进行滤波,同时选择一避免来自陷波滤波器或来自线干扰的谐波的干扰的最佳解调频率。而且,在光发射器波长中的每一波长之前和之后都测量对于例如电力线干扰的任何低频干扰的环境光,并且随后从所检测的信号中减去环境光的平均量。
Description
技术领域
本发明涉及血氧计,且更特定而言,涉及用于脉冲血氧计中的环境光取消的技术。
背景技术
脉冲血氧定量法通常用于测量各种血液流动特征,包括(但不限于):动脉血中血红蛋白的血氧饱和度、供应给组织的个别血液脉动的体积,和对应于患者的每一次心跳的血液脉动率。这些特征的测量已由使用非侵入性传感器来完成。所述传感器将光散射而穿过患者组织中有血液灌注到组织的一部分中,且光电地感测光在上述组织中的吸收。所吸收的光的量接着用来计算所测量的血液成分的量。
选择散射过组织的光以具有一个或一个以上的波长,其由血液吸收且吸收数量表示血液中的血液成分的量。所传输散射穿过组织的光的量将根据组织中的血液成分的变化量和相关的光吸收而改变。根据用于测量血氧饱和度的已知技术,为测量血氧含量,这些传感器通常已具有适用于产生具有至少两种不同波长的光的光源,且具有对那两种波长敏感的光电检测器。
已知非侵入性传感器包括紧固到身体的一部分(例如,手指、耳朵或头皮)上的装置。在动物和人类中,这些身体部分的组织灌注有血液并且组织表面能够由传感器所接近。
关于血氧计测量的一个麻烦在于:除接收针对组织的光以外,光电检测器也检测周围光。可作出尝试来遮蔽环境光,但通常将检测到若干量的环境光。特别要考虑处于荧光或其他灯的电力线频率的光,其在美国为60Hz而在欧洲和其他国家为50Hz。
由于通常使用一单个光电检测器,因此具有不同波长的光(例如红光和红外光)为时间分隔多路传输。必须对所检测的信号进行多路分解。多路分解频率必须足够地高以使得其远大于脉冲率。然而,选择一多路分解频率也受环境光干扰影响。一个问题为:AC电力线频率的谐波混叠。U.S.专利第5,713,355号论述根据以各频率检测的环境干扰的量而改变多路分解频率的技术。
U.S.专利第5,885,213号论述从所检测的光信号中减去一暗信号(所检测的环境光)。这通过以下方式来完成:停止红光发射器和红外光发射器,在中间接通它们使得可检测假定包含存在环境光的“暗”信号。这可随后从期望信号中减去。处理环境光问题的专利的其他实例为U.S.专利第6,385,471号、第5,846,190号和第4,781,195号。
U.S.专利第6,449,501号论述使用一陷波滤波器来滤出线路频率。然而,取样率描述为设置为电力线干扰的基频的两倍,从而留下电力线干扰的更高谐波成为麻烦,并且不清楚如何在不对调制频率进行滤波的情况下对干扰进行滤波。所使用的陷波滤波器的另一实例陈述于U.S.专利第4,802,486号中,其中陷波滤波器用于EKG信号。
发明内容
本发明提供一种脉冲血氧计方法和设备,其(1)以一在一调制频率与一通用电力线频率(50、60、100和120)的公倍数之间的间隔提供一陷波滤波器(46),并且(2)也提供一大于人体的最高脉冲率且低于50、60、100或120Hz的任何谐波的解调频率。本发明因此允许对环境光干扰的主要源进行滤波,同时选择一避免来自陷波滤波器或来自电力线干扰的谐波的干扰的最佳解调频率。
在一个实施例中,所述公倍数为1200,其中解调频率在与1200相差5与20Hz之间,在一个实施例中,优选为大约1211。
在本发明的另一方面中,在光发射器波长(在一个实施例中为红光和红外光)中的每一波长之前和之后都测量暗信号、或环境光。替代简单地减去暗等级中的一者,将两个暗等级平均,并且随后从所检测的信号中减去所述平均结果。这补偿由于所检测的信号期间的环境光中的变化,从而降低电力线干扰或任何其他低频干扰的效应。
在本发明的另一方面中,在数字域中完成数字滤波和分样。当在前端硬件中的增益设置上或在LED功率上发生改变时,预先加载滤波器以将值放入其存储器中,以对应于对新增益或功率设置处的输出的稳定值的估计。这预先加载加速了有效数据可用于滤波器的输出的时间。
附图说明
图1是并入本发明的血氧计的方框图。
图2是包括一陷波滤波器的本发明的一个实施例中的数字操纵的一部分的方框图。
图3是说明在本发明的一个实施例中平均的多个暗等级的图。
图4是说明根据本发明的一个实施例的数字滤波器和分样器的预先加载的图。
具体实施方式
整体系统
图1说明并入本发明的血氧定量法系统的实施例。传感器10包括红光LED和红外光LED以及光电检测器。电缆12将它们连接到电路板14。由一LED驱动接口16提供LED驱动电流。将从传感器接收到的光电流提供到一I-V接口18。随后将IR电压和红光电压提供到一并入本发明的∑-Δ接口20。将∑-Δ接口20的输出提供给一微控制器22。微控制器22包括用于程序的闪存,和用于数据的EEPROM存储器。所述血氧计也包括一个连接到闪存26的微处理器芯片24。最后,使用一个时钟28并且提供一个接口30以用于传感器10中的数字校准。一独立主机32接收经处理的信息,并且在线34上接收一模拟信号以用于提供模拟显示。
陷波滤波器
图2展示一个模拟到数字转换器40,其提供一个待由图1的微控制器22操纵的数字信号。微处理器应包括一个解调器42、四级滤波器/分样器44、利用一陷波的低通滤波器46,以及用于如此项技术中已知的用于数字操纵信号和计算氧饱和度的其他区块。在解调后仅展示红光通道,但类似通道用于IR.信号。
陷波滤波器46处理电力线干扰,在美国,其来自在60Hz或120Hz(根据电源要求而定)上操作的光。欧洲和其他区域使用50Hz或100Hz。50、60、100和120Hz的一公倍数为1200Hz。调制频宽经选择为高于最高可能人体脉冲率,优选高于5Hz。同时,其经选择为低于电力线干扰信号的任何谐波。将二十赫兹选择为一希望的上限,因为2450的第二谐波将在2025Hz混叠。在一个实施例中,将调制频率选择为1211.23Hz。这距1200Hz有11.23Hz间隔(在5-20Hz的范围内)。因此,在一优选实施例中,在陷波滤波器中以11.23Hz提供零。在一个实施例中,利用陷波的低通滤波器(46)为在11.25Hz下利用陷波的8极贝塞耳(Bessel)滤波器。
本发明因此提供一种消除来自电力干扰的干扰的有效方法,所述干扰可混叠入所检测的信号中,例如荧光灯上的纹波。虽然已在一解调器之前在硬件中提供防混叠滤波器,但仍难以使这些防混叠滤波器有效,且因此在数字域中将存在待处理的所检测信号中的一些残余线干扰。
平均环境暗等级以减少低频干扰
图3说明本发明的另一方面:通过平均取样周期之前和之后的环境暗等级来解释来自电力线或其他源的低频干扰,而减少环境干扰。图3展示在2400的取样率下的信号。图3中的向上倾斜线是由于60Hz电力线干扰。需要消除这向上倾斜(其在60Hz(或50Hz等)的其他部分中将向下)信号。
图3展示在调制的不同周期期间所检测的信号。所检测的信号电平由线50说明。在一第一暗周期52期间,红光LED或IR LED均未接通,从而允许对暗、或环境光取样。在这个取样之后,在一时间周期54期间,红光LED接通,其中信号50随着红光LED到达其完全强度而在这周期期间上升。在时间周期56期间,所检测的信号对应于接通状态的红光LED。
在周期58期间红光LED关闭且信号衰减,之后,取样一第二暗周期60。
随后,IR LED在周期62期间接通,且在周期64期间经取样。其在一周期66期间关闭且信号衰减,其中在周期68期间进行一第三暗取样。所述第三暗取样也对应于第一暗周期52,因为过程自身重复。
如在图3中可见,如果仅使用所述暗等级中的一个暗等级,那么如果环境等级例如由于低频干扰而改变,那么可测量不准确的环境等级。通过针对一特定波长将取样周期之前和之后的暗周期平均化,可获得对环境暗等级信号的一个更准确地测量。例如,在红光调制周期56期间的环境干扰是由测量周期52期间的暗1信号、周期60期间的暗2信号并且平均这些信号来确定。类似地,对于红外光调制周期64,平均周期60期间的暗2信号和周期68期间的暗3信号并且从所检测的IR信号中减去所述平均结果以消除环境干扰。所有这些计算将通过图1的微控制器22在数字域中完成。
预先加载分样和贝塞耳(Bessel)滤波器
图4说明本发明的另一方面,其中预先加载滤波器和软件。在模拟输入信通过∑-Δ调制器和多位模拟数字转换器处理之前,其通常在一硬件放大器84中放大。在由∑-Δ调制器86处理并且转换为数字域之后,由分样器88对其进行分样以降低取样率并且由贝塞耳(Bessel)滤波器滤波。一控制器92使用对输出的稳定值将为何值的估计预先加载贝塞耳(Bessel)滤波器和分样器的存储器。这将显著减少滤波器在其输入上的阶跃变化之后的稳定时间。所述输入上的阶跃变化可由放大器84的增益设置上的改变而发生。或者,阶跃变化可为所激活的特定LED、LED的功率或前端硬件的其他增益设置上的改变的结果。由于控制器92将激活所述改变,因此,其将了解何时使用正确值来预先加载滤波器和分样器。虽然这些在图4中展示为区块,但应了解,在优选实施例中,这是由充当控制器92、滤波器88和分样器90的软件程序完成。滤波器和分样器的这预先加载通过缩短稳定时间提供可更快使用的有效数据。
如所属领域的技术人员将了解,本发明可以其它特定形式体现,而不脱离本发明的本质特征。例如,可使用两种以上不同波长的光。或者,应选择不同解调频率。另外,陷波滤波可在对所检测信号进行其他数字处理之前或之后完成。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。
Claims (18)
1.一种用于操作一脉冲血氧计的方法,其包含:
使用一距50、60、100和120的一公倍数一预定间隔的调制频率以两种波长交替产生光;
所述预定间隔大于一人体的一最高脉冲率且小于50、60、100或120的任何谐波的一间隔;
将所述光引导到一组织位置处;
检测一散射离开所述组织位置的所检测的光信号;
以一为所述公倍数的频率对所述所检测的光信号进行陷波滤波。
2.根据权利要求1所述的方法,其进一步包含:
数字化所述所检测的光信号,以提供一数字化信号;和
所述陷波滤波是对所述数字化信号执行的。
3.根据权利要求1所述的方法,其中所述公倍数为1200。
4.根据权利要求1所述的方法,其中所述预定间隔在5赫兹与20赫兹之间。
5.根据权利要求1所述的方法,其中所述预定间隔为大约11赫兹。
6.根据权利要求1所述的方法,其中所述陷波滤波是通过在一数字滤波器中以所述间隔提供一零而执行的。
7.根据权利要求1所述的方法,其中
所述调制频率用于在产生具有所述第一波长的光的一第一周期、没有光产生的一暗周期与产生具有所述第二波长的光的一第二周期之间交替;
通过平均所述第一周期之前和之后的所述暗周期中的所述所检测的光信号的一数量,来估计在所述第一周期期间在所述所检测的光信号中的一环境光等级;
通过平均所述第二周期之前和之后的所述暗周期中的所述所检测的光信号的一数量,来估计在所述第二周期期间在所述所检测的光信号中的一环境光等级。
8.一种用于测量在一脉冲血氧计中的一所检测光信号的方法,其包含:
使用一调制频率以两个波长交替产生光;
将所述光引导在一组织位置处;
检测一散射离开所述组织位置的所检测的光信号;
使用所述调制频率在产生具有所述第一波长的光的一第一周期、没有光产生的一暗周期与产生具有所述第二波长的光的一第二周期之间交替;
通过平均所述第一周期之前和之后的所述暗周期中的所述所检测的光信号的一数量,来估计在所述第一周期期间在所述所检测的光信号中的一环境光等级;和
通过平均所述第二周期之前和之后的所述暗周期中的所述所检测的光信号的一数量,来估计在所述第二周期期间在所述所检测的光信号中的一环境光等级。
9.根据权利要求8所述的方法,其进一步包含:
从所述所检测的光信号中减去一估计环境光等级。
10.一种脉冲血氧计,其包含:
至少一光发射器;
一控制电路,其用于使用一距50、60、100和120的一公倍数一预定间隔的调制频率从所述至少一光发射器以两种波长交替产生光;
所述预定间隔大于一人体的一最高脉冲率且小于50、60、100或120的任何谐波的一间隔;
一检测器,其用于检测一散射离开一组织位置的所检测的光信号;
一处理电路,其用于处理所述所检测的光信号,所述处理电路包括一陷波滤波器,
所述陷波滤波器经配置用来以一为所述公倍数的频率对所述所检测的光信号进行滤波。
11.根据权利要求10所述的脉冲血氧计,其进一步包含:
一模拟到数字转换器,其用于数字化所述所检测的光信号以提供一数字化信号;和
所述陷波滤波器是一数字滤波器。
12.根据权利要求10所述的脉冲血氧计,其中所述公倍数为1200。
13.根据权利要求10所述的脉冲血氧计,其中所述预定间隔在5赫兹与20赫兹之间。
14.根据权利要求10所述的脉冲血氧计,其中所述预定间隔为大约11赫兹。
15.根据权利要求10所述的脉冲血氧计,其中所述陷波滤波器在一数字滤波器中以所述间隔提供一零。
16.根据权利要求1所述的脉冲血氧计,其进一步包含:
所述控制电路经配置以在产生具有所述第一波长的光的一第一周期、没有光产生的一暗周期与产生具有所述第二波长的光的一第二周期之间交替;
所述处理电路经配置,以通过平均所述第一周期之前和之后的所述暗周期中的所述所检测的光信号的一数量,来估计在所述第一周期期间在所述所检测的光信号中的一环境光等级,并且通过平均所述第二周期之前和之后的所述暗周期中的所述所检测的光信号的一数量,来估计在所述第二周期期间在所述所检测的光信号中的一环境光等级。
17.一种脉冲血氧计,其包含:
至少一光发射器;
一控制电路,其用于使用一调制频率从所述至少一光发射器以两种波长交替产生光;
一检测器,其用于检测一散射离开所述组织位置的所检测的光信号;
所述控制电路经配置以在产生具有所述第一波长的光的一第一周期、没有光产生的一暗周期与产生具有所述第二波长的光的一第二周期之间交替;
一处理电路,其经配置以通过平均所述第一周期之前和之后的所述暗周期中的所述所检测的光信号的一数量,来估计在所述第一周期期间在所述所检测的光信号中的一环境光等级,并且通过平均所述第二周期之前和之后的所述暗周期中的所述所检测的光信号的一数量,来估计在所述第二周期期间在所述所检测的光信号中的一环境光等级。
18.一种血氧计设备,其包含:
一∑-Δ调制器,其具有一经耦合以接收一模拟传感器信号的输入端;
一硬件放大器,其用于放大一传感器信号以提供一经放大的信号作为所述模拟传感器信号;
一多位模拟到数字转换器,其耦合到所述∑-Δ调制器的所述输出端以提供一数字输出;
一分样器,其经配置以对所述数字输出进行操作;
一数字滤波器,其经配置以对所述数字输出进行操作;和
一控制程序,其用于在修改所述硬件放大器的增益之后,使用对一稳定输出值的
一估计预先加载所述分样器和数字滤波器。
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2004
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- 2005-02-24 WO PCT/US2005/006336 patent/WO2005082242A1/en active Application Filing
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- 2005-02-24 AU AU2005216985A patent/AU2005216985A1/en not_active Abandoned
- 2005-02-24 KR KR1020067018453A patent/KR20070024488A/ko not_active Application Discontinuation
- 2005-02-24 DE DE602005008718T patent/DE602005008718D1/de active Active
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- 2006-07-28 US US11/495,415 patent/US7400919B2/en not_active Expired - Lifetime
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CN102713569A (zh) * | 2010-01-28 | 2012-10-03 | 霍夫曼-拉罗奇有限公司 | 尤其是用于血糖确定的测量系统和测量方法 |
CN102713569B (zh) * | 2010-01-28 | 2014-12-31 | 霍夫曼-拉罗奇有限公司 | 尤其是用于血糖确定的测量系统和测量方法 |
CN102512178A (zh) * | 2011-12-23 | 2012-06-27 | 深圳市理邦精密仪器股份有限公司 | 一种血氧测量装置和方法 |
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CN104706336A (zh) * | 2014-12-31 | 2015-06-17 | 歌尔声学股份有限公司 | 一种光电式脉搏信号测量方法、装置及测量设备 |
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CN106031639A (zh) * | 2015-03-07 | 2016-10-19 | 上海贝瑞电子科技有限公司 | 一种高精度血氧检测管理方法及系统 |
CN115266583A (zh) * | 2022-07-16 | 2022-11-01 | 北京津发科技股份有限公司 | 环境光滤除方法、系统、计算机设备及计算机可读存储介质 |
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AU2005216985A1 (en) | 2005-09-09 |
CA2556748A1 (en) | 2005-09-09 |
KR20070024488A (ko) | 2007-03-02 |
EP1722675B1 (en) | 2008-08-06 |
US20130123593A1 (en) | 2013-05-16 |
ATE403397T1 (de) | 2008-08-15 |
US7190985B2 (en) | 2007-03-13 |
ES2311980T3 (es) | 2009-02-16 |
US8315684B2 (en) | 2012-11-20 |
CA2556748C (en) | 2013-02-12 |
US8874181B2 (en) | 2014-10-28 |
US20060264721A1 (en) | 2006-11-23 |
US20090005662A1 (en) | 2009-01-01 |
WO2005082242A1 (en) | 2005-09-09 |
JP2007523717A (ja) | 2007-08-23 |
US7400919B2 (en) | 2008-07-15 |
DE602005008718D1 (de) | 2008-09-18 |
EP1722675A1 (en) | 2006-11-22 |
MXPA06009755A (es) | 2007-03-15 |
US20050187448A1 (en) | 2005-08-25 |
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