CN1946336A - 使用水对近红外线的吸收的脉冲血氧计运动伪影消除 - Google Patents
使用水对近红外线的吸收的脉冲血氧计运动伪影消除 Download PDFInfo
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Abstract
本发明提供一种用于测量生理参数的方法及设备,其获得一从以一第一波长透射过一组织部分的能量导出的第一信号,所述信号包括一对应于与运动相关的事件的信号部分及一对应于动脉脉动事件的信号部分,在所述第一波长下,水为所述组织部分中电磁能量的一主要吸收剂;获得一从以一第二波长透射过一组织部分的电磁能量导出的第二信号,所述信号包括一对应于与运动相关的事件的信号部分及一对应于动脉脉动事件的信号部分,在所述第二波长下,血红蛋白为所述组织部分中电磁能量的一主要吸收剂;并将所述第一与第二信号相组合以产生一组合的体积描记图信号,所述组合信号具有一对应于与运动相关的事件的信号部分,所述信号部分小于存在于所述第一信号或第二信号中的信号部分。
Description
技术领域
本发明涉及使用近红外光谱技术处理自例如脉动式血氧计等医疗诊断器械获得的信号以消除代表一所关心生理参数的信号中的伪影或噪声影响。
背景技术
典型的脉动式血氧计测量两个生理参数:动脉血红蛋白的氧饱和度百分比(SpO2或饱和)及脉搏率。可使用各种技术来估测氧饱和度。在一常用技术中,调节并处理由光电检测器产生的光电流以确定红色信号对红外信号的调制比之比(比率之比)。人们已发现此调制比与动脉血氧饱和度密切相关。脉动式血氧计及传感器是通过针对一组病人、健康的志愿者、或动物在一系列在体内测量的动脉血氧饱和度(SaO2)内测量调制比来凭经验校准。以逆向方式根据所测量的病人的调制比的值,使用所观察到的关联性来估测血氧饱和度(SpO2)。大多数脉动式血氧计提取具有最初所确定饱和度或脉搏率的体积描记图信号,而最初所确定的饱和度及脉搏率二者均易受干扰。
通常,脉动式血氧计利用如下事实:在活的人体组织内,血红蛋白为介于500与1100nm之间的光的强吸收剂。使用在此波长范围内由血红蛋白吸收的光量可很容易地测量出流过组织的动脉血液的脉动。一随时间变化的动脉脉动波形的曲线图称作光体积描记图。体积描记波形的幅值随用于测量其的光的波长而变化,而所述光的波长取决于脉动地流过动脉的血液的吸收特性。通过将其中氧血红蛋白及脱氧血红蛋白具有不同吸收系数的两个不同波长区域中的体积描记测量相结合,便可估测动脉血液的氧饱和度。市售脉动式血氧计中所采用的典型波长为660及890nm。
已知快速运动或向一组织部位施加压力可具有改变在所述部位处或附近所测量到的光学特性的作用。与此类事件相关联的光信号变化幅度—称作运动伪影—可很容易大于因动脉脉动所引起的光信号变化幅度。在实际中,此可导致脉冲式血氧计所估测的百分比氧饱和度不精确。已知用于解决并消除所不希望的信号影响的各种技术,包括运动伪影技术。本文中所说的噪声是指不希望有的或不直接与和动脉脉动相关光学特性变化相关的信号部分,且其可包括运动伪影。噪声及运动伪影可使通过组织的光信号而劣化。一种噪声源为到达光电检测器的环境光。另一噪声源为来自其它电子仪器的电磁耦合。病人的运动也会引入噪声并影响信号。例如,检测器与皮肤或发射体与皮肤之间的接触可在运动使这两者中的任何一者移离皮肤时暂时中断。另外,由于血液为流体,因此其对惯性效应的反应与周围组织不同,从而引起血氧计探头固定位置附近的点处的体积发生瞬间变化。
运动伪影可使保健提供者所依赖的脉冲血氧计信号劣化却不为所述提供者所知。如果对病人的监控是在远程进行,运动太小以至于未能观测到,或保健提供者正在观察仪器或病人的其它部位而不是传感器部位,则会尤其如此。存在各种用于解决噪声及/或运动伪影的影响的已知技术。
例如,第4,714,341号美国专利揭示一种用于将三个波长相结合来检测是否存在运动的方法。每次使用两个波长来分别计算氧饱和度百分比。当使用不同波长组合所计算出的氧饱和度值的一致性较差时,便假定是因运动伪影所致,并放弃此值。此方法的一缺点在于:各饱和值之间的一致或不一致既可能是因运动伪影所致也可能不是因运动伪影所致。另外,此方法不能识别或消除运动伪影的影响,而是放弃看似可疑的值。
另一种方法涉及对脉动式血氧计信号进行滤波。然而,滤波方法需要作出关于所述伪影的特性的假定,而这些假定并非总是成立。另外,此方法不能测量由运动引起的信号。
第5,482,036号美国专利提供另一种方法,并阐述一种用于减少伪影的信号处理方法,所述信号处理方法在与伪影有关的信号与处于比动脉血液低的氧饱和度下的血液相关联时起作用。此种方法依赖于产生一人工噪声信号,将所述人工噪声信号与生理参数相结合来减小未知噪声信号的影响。此种用于减小伪影的影响而不单独测量运动信号的方法是建立在关于运动对体积描记信号的影响的假定之上。而假定既可能成立也可能不成立,而且许多假定是无效的。
每一种用于补偿运动伪影的已知技术均具有其自身的局限性及缺点。因此,需要设计一种在运动阶段期间更有效及更精确地报告血氧水平的脉动式血氧计系统。虽然许多人已通过作出可能无效的假定或通过舍弃所需信号值的可疑估测值来尝试着隔离所不希望有的信号部分的影响,但仍然需要对伪影信号进行定性识别、测定及测量,以在存在所不希望有的信号部分时能够对所需信号值进行精确测量。
发明内容
通过测量伪影信号,本发明使运动伪影能够与体积描记信号分离而无需使用现有已知技术中的限定性假定。本发明提供用于测量与组织的光学特性变化相关联的运动信号并使用所述测量值来补偿在其它波长下所作的体积描记测量的方法。
在一实施例中,本发明提供一种用以测量一生理参数的方法,所述方法包括:获得一从以一第一波长透射过一组织部分的电磁能量导出的第一信号,所述第一信号包括一对应于与运动相关的事件的信号部分及一对应于动脉脉动事件的信号部分,其中在所述第一波长下,水为所述组织部分中电磁能量的一主要吸收剂;获得一从以一第二波长透射过一组织部分的电磁能量导出的第二信号,所述第二信号包括一对应于与运动相关的事件的信号部分及一对应于动脉脉动事件的信号部分,其中在所述第二波长下,血红蛋白为所述组织部分中电磁能量的一主要吸收剂;并将所述第一信号与所述第二信号相组合以产生一组合的体积描记信号,以便所述组合信号具有一对应于与运动相关的事件的信号部分,所述信号部分小于存在于所述第一信号或所述第二信号中的信号部分。
在所述第一波长下,在所述组织部分中,水为一强于血红蛋白的电磁能量吸收剂,而在所述第二波长下,在所述组织部分中,血红蛋白为一强于水的电磁能量吸收剂。
为了更详尽地了解本发明各实施例的性质及优点,应结合附图阅读下文详细说明。
附图说明
图1为一实例性血氧计的一方块图。
图2为在人耳上测到的体积描记图幅值随波长而变化的一曲线图。
图3为人血液中主要成分的吸收光谱的一曲线图。
图4为一换算至典型生理浓度的人皮肤中主要成分的吸收光谱曲线图。
图5为一换算至相等体积分数浓度的人皮肤中主要成分的吸收光谱曲线图。
图6为一在4个分别为约920、1050、1180及1300nm的不同波长下在人耳上测到的体积描记图的曲线图。
图7为一通过将在2个近红外波长下所进行的测量相结合来减少实例性体积描记图伪影的一曲线图。
具体实施方式
通过测量伪影信号,本发明使运动伪影能够与体积描记信号分离而无需使用现有已知技术中的限定性假定。本发明提供用于测量与组织的光学特性变化相关联的运动信号并使用所述测量来补偿在其它波长下所测到的体积描记测量的方法。
图1为一可经配置以实施本发明各实施例的实例性脉动式血氧计的一方块图。本发明各实施例可为一由下文所述的微处理器122执行的数据处理算法。来自光源110的光进入病人组织112中,并由光电检测器114散射及检测到。一包含所述光源及光电检测器的传感器100也可包含一编码器116,编码器116提供指示光源110的波长的信号以使血氧计能够选择适用于计算氧饱和度的校准系数。编码器116可(例如)为一电阻器。
传感器100连接至一脉动式血氧计120。所述血氧计包括一连接至一内部总线124的微处理器122。一RAM存储器126及一显示器128也连接至所述总线。一时间处理单元(TPU)130向光驱动电路132提供定时控制信号,光驱动电路132控制何时点亮光源110,且如果使用多个光源,则控制不同光源的多路复用定时。TPU 130还通过一放大器133及一开关电路134来控制来自光电检测器114的信号的选通输入。如果使用多个光源,则根据点亮多个光源中的那一个光源,在适当时间对这些信号进行采样。所接收的信号经过一放大器136、一低通滤波器138及一模拟-数字转换器140。然后,将所述数字数据存储于一队列串行模块(QSM)142中,供以后在QSM 142装满时下载至RAM 126。在一实施例中,可具有多个由单独的放大器、滤波器及A/D转换器构成的并行路径来用于所接收的多个光波长或光谱。
根据由对应于光电检测器114所接收的光的接收信号值,微处理器122将使用各种算法来计算氧饱和度。这些算法需要使用对应于(例如)所使用的光的波长的系数,所述系数可凭经验来确定。这些系数存储于一ROM 146中。在一双波长系统中,为任一对波长光谱所选择的特定的一组系数取决于由编码器116所指示的对应于一特定传感器100中一特定光源的值。在一实施例中,可指配多个电阻值来选择不同组系数。在另一实施例中,使用相同的电阻器从各系数中选择适用于一与近红外光源或远红外光源配对的红外光源的系数。可通过一来自控制输入154的控制输入来选择将选择近红外组还是将选择远红外组。控制输入154可为(例如)脉动式血氧计上的开关、一键盘或一自一远程主计算机提供指令的端口。而且,可使用任一数量的方法或算法来确定病人的脉搏率、氧饱和度或任何其它所需的生理参数。例如,使用调制比进行的氧饱和度估测阐述于1998年12月29日颁予且名称为“用于使用基于模型的自适应性滤波来估测生理参数的方法及器械(METHOD AND APPARATUS FORESTIMATING PHYSIOLOGICAL PARAMETERS USING MODEL-BASED ADAPTIVEFILTERING)”的第5,853,364号美国专利及1990年3月27日颁予且名称为“用于检测光脉冲的方法及器械(METHOD AND APPARATUS FOR DETECTING OPTICAL PULSES)”的第4,911,167号美国专利中。此外,氧饱和度与调制比之间的关系进一步阐述于1997年7月8日颁予且名称为“具有调制编码方案的医用传感器(MEDICAL SENSOR WITH MODULATEDENCODING SCHEME)”的第5,645,059号美国专利中。
上文已阐述一种实例性脉动式血氧计,下文将阐述根据本发明各实施例用于减少包括所接收信号中的运动伪影影响在内的噪声的各种方法。
图2为通过36名受试者的耳垂所测量到并根据在约900nm波长下的测量值来归一化的平均体积描记幅值随波长变化的曲线图。测量值(例如图2中所示)表明光电体积描记波形的幅值在约900与1300nm之间随波长减小,在约1285nm处具有最小值。本发明的发明者已发现,在处于约900-920nm之外的波长下,水-其浓度远高于血红蛋白-也变成组织中的一主要的光吸收剂。图3为血液中所存在的某些光吸收成分的吸收率(以cm-1为单位)与波长(以nm为单位)的关系曲线图。图3显示,在约1400nm下,水的吸收率高于氧血红蛋白约60%,然而在1400nm下的体积描记幅值(图2)低于约900nm下的体积描记幅值35%。
图4为一换算至典型生理浓度的人皮肤中主要成分的吸收光谱(cm-1)随波长(nm)而变化的曲线图。此图式显示因水而引起的吸收率在约1180nm处具有一峰值,且蛋白质在略高于1150nm处、脂肪在约1200nm处存在类似峰值。
图5为一换算至相等体积分数浓度的人皮肤中主要成分的吸收光谱的曲线图。此图式显示,在约1185nm处,水、脂肪及蛋白质的经体积分数换算的吸收率大致相等。
虽然并不限于任一特定理论,然而本发明的发明者注意到,水(在低于约900及低于约1300nm的波长下)的体积描记影响弱于血红蛋白的一原因在于如下事实:血红蛋白基本上仅局限于血管中,而水则以高的浓度同时存在于血管及周围组织中。因此,通过一组织床的动脉血管的因脉动而引起的扩张会导致血红蛋白浓度局部增加,但水的浓度的净变化却较小。在血液中水的浓度等于组织中水的浓度情况下,水所吸收的光量的变化预计接近于零。
本发明的各实施例利用如下发现:与其中血红蛋白为强吸收剂而水为弱吸收剂的光谱范围相比,在其中血红蛋白的吸收性较弱而水的吸收性较强的光谱范围内,体积描记图对与运动相关的事件更加敏感。
利用体积描记图在水吸收性较强的范围内的弱幅值来使与动脉脉动相关的信号与一运动伪影信号分离。通过在一其中水为主要吸收剂的波长下测量光学体积描记图,可测量与运动或压力相关的组织光学特性的变化,而几乎不存在来自下面的动脉脉动的干扰。图6中以吸收率单位与成比例的时间(即每一点的时间为43毫秒)的关系形式来显示在四个近红外波长下通过一经历偶然运动的人耳测到的体积描记图。在约920nm处-其中血红蛋白的吸收性强而水的吸收性弱,体积描记图包含规则的动脉脉动,这些规则的动脉脉动偶尔地由与运动相关的事件中断。随着波长增加至约1300nm-其中水为主要吸收剂,动脉脉动减少且测到的信号因与运动相关的事件而变大。
通过将在一其中水为主要吸收剂的光谱范围内所测到的体积描记图与在血液为一主要吸收剂的光谱范围内测到的体积描记图相结合,可有选择地消除与运动相关的信号。图7显示在约920nm下测到的人耳的体积描记图及从在920nm下测到的体积描记图中减去在约1180nm下测到的体积描记图的一部分的结果。具体而言,图7显示在920nm下测到的人耳的体积描记图、及从在约920nm下测到的体积描记图中减去在约1180nm下测到的体积描记图的约60%而得到的结果。选择60%这一值是因为在此波长下,水的吸收率高于氧血红蛋白的吸收率约60%。对于不同的波长组合而言,根据水的吸收率与氧血红蛋白的吸收率之比或根据经验确定值来使用其它乘数。
通过对在医院环境中测量的36位病人的一多样性集合应用相同的分析,发现在910nm处体积描记图的信噪比平均增加到2倍。通过允许改变1180nm体积描记图的乘数,能实现更高的信噪比提高量。
理论模型
下文的推导证明一种如下机理:通过所述机理,使在一波长下测量的体积描记图上因运动引起的光散射的变化的影响可由一第二波长下的体积描记图测量来补偿。此推导是作为可加以补偿的因运动引起的光学变化类型的一实例,而并非是本发明可赖以起作用的唯一机理,且因此其并非旨在限制本发明的各实施例。
此分析的起点是组织中光传输的漫射理论(例如参见“Diffusion Theory of LightTransport”,Willem M.Star,Optical-Thermal Response of Laser-Irradiated Tissue,由Ashley J.Welch及Martin J.C.van Gemert编辑,Plenum Press,New York,1995,第131-206中)。在其中经传输校正的散射系数μs’远大于吸收系数μa’的情况下,由一定位于离光源一距离I处的检测器在波长λ处测量的光漫射强度I(λ)可描述如下(例如参见“Measurement ofBlood Hematocrit by Dual-Wavelength Near-IR Photoplethysmography”,Schmitt,J.M.;Guan-Xiong,G.;Miller,J.,SPIE,第1641卷,1992年,第150-161页):
对于吸收系数的较小变化,例如由动脉脉动而引起的变化,所引起的强度变化可由强度相对于吸收系数的导数来描述:
其中ΔVart为因动脉脉动而引起的分数体积变化,μa art为受测量的动脉血液的吸收系数,AC(λ)是指光信号中随时间变化的部分且DC(λ)是指光信号中的平均部分或不随时间变化的部分。
如果在两个选择成使氧血红蛋白与脱氧血红蛋白容易区分的波长λ1及λ2(例如λ1~约为660nm,λ2~约为910nm)下测量方程2所描述的AC-DC比,即会估测出动脉氧饱和度SPO2:
其中:
据此:
(方程式3c)
其中μa HHb及μa O2Hb为动脉血液中脱氧血红蛋白及氧血红蛋白各自的吸收系数,且R为AC与DC的比之比。
散射系数的较小变化(例如可能是因组织受压或运动伪影而引起)的影响如下列方程式4所列:
通过在一选择成使因血红蛋白引起的吸收较弱而因水引起的吸收较强的第三波长λ3下测量AC-DC比,通过减去经换算的在λ3下的AC-DC测量值来从在λ2下的AC-DC测量值中消除因运动引起的散射变化的影响。最后得到的经运动校正的体积描记图P可表示成:
(方程式5a)
其中:
当动脉脉动(方程式2)与运动伪影(方程式4)的影响为加性时,将方程式5扩展如下:
当在λ3处水的吸收在组织对光的吸收中占主要地位、且动脉与周围组织中的水浓度接近相等时,Δμa(λ3)近似为零,且方程式6化简成:
方程式7仅取决于在λ2处的动脉脉动的影响;运动伪影的影响已得到消除。以一类似方式,在λ3处测到的体积描记图可用于将运动影响从在λ1处测到的体积描记图中消除。然后,可将在λ1及λ2处测到的经校正的体积描记图相结合并用于估测氧饱和度,如例如方程式3所述。
已测试了介于约900与1300nm之间范围内且更具体而言介于约1150与1350nm之间范围内的几个波长并发现其可有效地自在约910nm下测得的体积描记图中减少运动伪影。处于此范围的较长波长侧处的波长具有使血红蛋白的吸收率比水的吸收率弱的优点(例如参见图3及4)。然而,处于此范围的较短端处的波长具有使随变化的组织成分的变动量减小的优点。如在其中已将组织中各主要成分归一化成相等的体积分数的图5中可见,水、脂肪及非血红蛋白蛋白质在约1185nm下均具有大致相等的吸收率。因此,在约1185nm下的组织吸收率几乎不随这些主要成分的相对浓度的变化而变化。
已知使用市售血氧计中通常所采用的硅(Si)检测器不容易实现对超过约1100nm的光的检测。例如,用于收集图2-7中所显示的数据的检测器采用砷化铟镓(InGaAs)作为光敏材料。最常见类型的InGaAs检测器对介于约800与1700nm之间的光敏感。因此,在一根据本发明各实施例设计而成的具有660及890nm常规波长的脉动式血氧计中,除一发出可被水强吸收的波长(例如约1180nm或约介于900-1400nm之间)的新光源外,还使用一个或多个附加检测器。一种这样的方案采用两个并排放置的检测器:一个Si检测器及一个InGaAs检测器。一替代方案使用一包含单独的Si层及InGaAs层的共线(“夹层”)检测器,例如可(举例而言)自Hamamatsu公司购得的检测器。或者,使用一锗检测器(Ge)来代替InGaAs检测器。
另外,上述对常规脉动式血氧定量法的增强的一替代形式为一全NIR脉动式血氧计。全NIR血氧计的一实例为一将发出约940、1040及1180nm的光的光源与单个InGaAs检测器结合使用的血氧计。除仅需一个检测器这一优点外,所述全NIR实施方案还具有与组织的光学特性相关的优点。使用脉动式血氧定量法所作的测量的精度部分地取决于不同颜色的光所传播经过的路径的相同程度。穿过组织的特定波长的光的平均路径长度及穿透深度受在所述波长下组织的吸收性及散射系数的强烈影响。在常规脉动式血氧定量法中,为了在两个波长下获得相同的平均路径长度及穿透深度,需要使在这两个波长下的散射及吸收系数相匹配。组织对光的散射随波长迅速减少,结果,出于下文所述的原因,使组织在约940、1040及1180nm处的散射特性将比组织在可见光波长与NIR波长的一组合(例如约660、890及1180nm)处的散射特性更密切地相匹配。氧及脱氧血红蛋白的吸收特性使得在高的氧饱和度值下因血红蛋白而引起的净(即氧及脱氧血红蛋白的组合影响)吸收系数将在660nm与940nm处匹配得相当好。然而,随着氧饱和度值的减小,在约660nm处的脱氧血红蛋白的高吸收系数将导致血红蛋白在约660与约940nm处的净吸收系数之间的失配越来越强。在可测量的氧饱和度值的整个范围内,血红蛋白在约940与约1040nm处的净吸收系数将较在约660与约940nm处更紧密地匹配。
对用于测量运动伪影信号的波长的选择部分地取决于对使光学路径长度与所要校正的信号的光学路径长度相匹配的需要。在超过约950nm时,为实现路径长度的紧密匹配,除血红蛋白的吸收系数外,还需要对水、蛋白质及非血红蛋白蛋白质的吸收系数加以考虑。虽然对于测量运动伪影信号而言,约1185nm为一当前较佳的波长,但其它替代波长值也可有效,例如介于约1050与1400nm之间及介于约1500与1850nm之间的波长。
可通过将光学组件直接放置于组织界面处,或者另一选择为通过用光纤向及自组织传输光,来实施本发明的各实施例。前一实施方式的优点是能更有效地传送及收集光,而后一实施方式的优点是能成本较低。成本较低的解决方案是通过如下事实来实现:当采用光纤传送时,光源及检测器可驻留于监视器而不是传感器中,且考虑到此类组件可能比光纤更昂贵,所以此将使装置更廉价。
本发明各实施例相对于用于解决运动伪影的影响的已知方法具有下文所述的几个优点。本发明各实施例提供用于测量与组织的光学特性变化相关联的运动信号并使用所述测量来补偿在其它波长下所作的体积描记图测量的方法及装置。通过测量伪影信号,本发明各实施例使运动伪影能够与体积描记信号分离而不使用现有已知技术中的限定性假定。本发明各实施例的优点在于:除识别运动处,其还提供一种用以在运动期间消除运动伪影并继续测量氧饱和度的方法。
如所属领域的技术人员所将了解,可设想出根据本发明各实施例的其它等效或替代方法来测量与组织的光学特性变化相关联的运动伪影信号并使用所述测量来补偿在其它波长下所作的体积描记图测量,此并不背离本发明的实质特征。例如,可使用可见光波长与NIR波长的一组合或一全NIR波长组合来进行测量。而且,近红外光谱领域的技术人员将认识到,可在本文中所使用的算法中添加其他项以包含在其他波长下所作的反射率测量且因此进一步提高精度。而且,除LED以外的光源或发光光学器件—包括(但不限于)适当调谐至所需波长的白炽灯及窄带光源—及相关联的光检测光学器件可放置于组织部位附近或者可定位于一远程单元中;且其通过光纤将光传送至组织部位及自组织部位接收光。另外,可使用以一背向散射模式或一反射模式来对反射率进行光学测量的传感器布置以及其它实施例(例如以一前向散射模式或一透射模式工作的实施例)来进行这些测量。这些等效形式及替代形式以及显而易见的改动及修改均打算包含于本发明范围内。因此,上文揭示内容旨在例示而非限制本发明的范围,本发明的范围是在随附权利要求书中加以规定。
Claims (24)
1、一种用以测量—生理参数的方法,其包括:
获得一从以一第一波长透射过一组织部分的电磁能量导出的第一信号,所述第一信号包括一对应于与运动相关的事件的信号部分及一对应于动脉脉动事件的信号部分,其中在所述第一波长下,水为所述组织部分中电磁能量的一主要吸收剂;
获得一从以一第二波长透射过一组织部分的电磁能量导出的第二信号,所述第二信号包括一对应于与运动相关的事件的信号部分及一对应于动脉脉动事件的信号部分,其中在所述第二波长下,血红蛋白为所述组织部分中电磁能量的一主要吸收剂;及
将所述第一信号与所述第二信号相组合以产生一包括一体积描记图的组合信号,所述组合信号具有一对应于与运动相关的事件的信号部分,所述信号部分小于存在于所述第一信号或所述第二信号中的信号部分。
2、如权利要求1所述的方法,其中在所述第一波长下,在所述组织部分中,水为一强于血红蛋白的电磁能量吸收剂。
3、如权利要求1所述的方法,其中在所述第二波长下,在所述组织部分中,血红蛋白为一强于水的电磁能量吸收剂。
4、如权利要求1所述的方法,其中所述第一波长处于约900与1850nm之间的范围内。
5、如权利要求1所述的方法,其中所述第一波长处于约1100与1400nm之间的范围内。
6、如权利要求1所述的方法,其中所述第一波长处于约1150与1250nm之间的范围内。
7、如权利要求1所述的方法,其中所述第一波长为约1185nm。
8、如权利要求1所述的方法,其中所述第二波长处于约600与950nm之间的范围内。
9、如权利要求1所述的方法,其中所述组合包括对所述第一信号应用一乘数以获得一经换算的第一信号并从所述第二信号中减去所述经换算的第一信号。
10、如权利要求9所述的方法,其中所述乘数为一在所述第一波长下血红蛋白对所述组织部分中电磁能量的吸收与在所述第二波长下血红蛋白对所述组织部分中电磁能量的吸收之比的一函数。
11、如权利要求1所述的方法,其中所述生理参数为一脉搏率。
12、如权利要求1所述的方法,其进一步包括:
获得一从以一第三波长透射过一组织部分的电磁能量中导出的第三信号,所述第三信号包括一对应于与运动相关的事件的信号部分及一对应于动脉脉动事件的信号部分,其中在所述第三波长下,血红蛋白为所述组织部分中电磁能量的一主要吸收剂;及
将所述第一信号与所述第三信号相组合以产生一包括一体积描记图的第二组合信号,所述第二组合信号具有一对应于与运动相关的事件的信号部分,所述信号部分小于存在于所述第一信号或所述第三信号中的信号部分。
13、如权利要求12所述的方法,其进一步包括:
将所述组合信号与所述第二组合信号相组合以形成一组合;及
使用所述组合来估测一氧饱和度值。
14、一种用于测量一生理参数的设备,其包括:
获得构件,其用于获得一从以一第一波长透射过一组织部分的电磁能量导出的第一信号,所述第一信号包括一对应于与运动相关的事件的信号部分及一对应于动脉脉动事件的信号部分,其中在所述第一波长下,水为所述组织部分中电磁能量的一主要吸收剂;
获得构件,其用于获得一从以一第二波长透射过一组织部分的电磁能量导出的第二信号,所述第二信号包括一对应于与运动相关的事件的信号部分及一对应于动脉脉动事件的信号部分,其中在所述第二波长下,血红蛋白为所述组织部分中电磁能量的一主要吸收剂;及
组合构件,其用于将所述第一信号与所述第二信号相组合以产生一包括一体积描记图的组合信号,所述组合信号具有一对应于与运动相关的事件的信号部分,所述信号部分小于存在于所述第一信号或所述第二信号中的信号部分。
15、如权利要求14所述的设备,其中所述用于获得一第一信号的构件包括:
经配置以将电磁能量射向所述组织部位处的发光光学器件;及
经配置以自所述组织部位接收辐射的光检测光学器件。
16、如权利要求15所述的设备,其中所述发光光学器件经配置以传送一处于约900与1850nm之间范围内的波长的电磁能量。
17、如权利要求15所述的设备,其中所述发光光学器件经配置以传送一处于约1100与1400nm之间范围内的波长的电磁能量。
18、如权利要求15所述的设备,其中所述发光光学器件经配置以传送一处于约1150与1250nm之间范围内的波长的电磁能量。
19、如权利要求15所述的设备,其中所述发光光学器件经配置以传送一处于约1185nm的电磁能量。
20、如权利要求14所述的设备,其中所述用于组合的构件包括用于对所述第一信号应用一乘数以获得一经换算的第一信号并从所述第二信号中减去所述经换算的第一信号的构件。
21、如权利要求14所述的设备,其中所述用于组合的构件包括一处理装置,所述处理装置经配置以将所述第一信号与所述第二信号相组合以产生一包括一体积描记图的组合信号,所述组合信号具有一对应于与运动相关的事件的信号部分,所述信号部分小于存在于所述第一信号或所述第二信号中的信号部分。
22、如权利要求14所述的设备,其进一步包括:
获得构件,其用于获得一从以一第三波长透射过一组织部分的电磁能量导出的第三信号,所述第三信号包括一对应于与运动相关的事件的信号部分及一对应于动脉脉动事件的信号部分,其中在所述第三波长下,血红蛋白为所述组织部分中电磁能量的一主要吸收剂;及
组合构件,其用于将所述第一信号与所述第三信号相组合以产生一包括一体积描记图的第二组合信号,所述第二组合信号具有一对应于与运动相关的事件的信号部分,所述信号部分小于存在于所述第一信号或所述第三信号中的信号部分。
23、如权利要求22所述的设备,其进一步包括:
组合构件,其用于将所述组合信号与所述第二组合信号相组合以形成一组合;及
估测构件,其用于使用所述组合来测定一氧饱和度值。
24、如权利要求14所述的设备,其中所述生理参数为一脉搏率。
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- 2005-03-08 WO PCT/US2005/007675 patent/WO2005087098A1/en active Application Filing
- 2005-03-08 EP EP05728326A patent/EP1729633B1/en not_active Not-in-force
- 2005-03-08 CN CNA2005800129844A patent/CN1946336A/zh active Pending
- 2005-03-08 KR KR1020067020214A patent/KR20070013277A/ko not_active Application Discontinuation
- 2005-03-08 JP JP2007502942A patent/JP2007528276A/ja active Pending
- 2005-03-08 CA CA2558643A patent/CA2558643C/en not_active Expired - Fee Related
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CA2558643A1 (en) | 2005-09-22 |
EP1729633A1 (en) | 2006-12-13 |
US8195263B2 (en) | 2012-06-05 |
WO2005087098A1 (en) | 2005-09-22 |
US20070106137A1 (en) | 2007-05-10 |
KR20070013277A (ko) | 2007-01-30 |
AU2005221673A1 (en) | 2005-09-22 |
US8175670B2 (en) | 2012-05-08 |
US20050203357A1 (en) | 2005-09-15 |
CA2558643C (en) | 2013-07-23 |
US20080009690A1 (en) | 2008-01-10 |
JP2007528276A (ja) | 2007-10-11 |
EP1729633B1 (en) | 2013-02-27 |
MXPA06010318A (es) | 2007-04-13 |
US7277741B2 (en) | 2007-10-02 |
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