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VeröffentlichungsnummerCN101933810 B
PublikationstypErteilung
AnmeldenummerCN 201010272884
Veröffentlichungsdatum16. Sept. 2015
Eingetragen3. Sept. 2010
Prioritätsdatum3. Sept. 2010
Auch veröffentlicht unterCN101933810A
Veröffentlichungsnummer201010272884.8, CN 101933810 B, CN 101933810B, CN 201010272884, CN-B-101933810, CN101933810 B, CN101933810B, CN201010272884, CN201010272884.8
Erfinder胡丽丹, 王干兵
Antragsteller深圳市索莱瑞医疗技术有限公司
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一种血氧饱和度检测方法 A method for detecting blood oxygen saturation übersetzt aus folgender Sprache: Chinesisch
CN 101933810 B
Zusammenfassung  übersetzt aus folgender Sprache: Chinesisch
本发明公开了一种血氧饱和度检测方法。 The present invention discloses a method for detecting blood oxygen saturation. 首先进行信号采集,然后进行预处理和自适应归一化处理;再进行FFT处理,将检测数据从时域变换到频域;最后进行R值计算并根据R值计算血氧饱和度。 First signal acquisition, and then pretreated and adaptive normalized; then FFT processing, the test data from the time domain to the frequency domain; and finally R value calculation and calculate oxygen saturation based on the R value. 采用了本发明技术方案血氧饱和度检测方法的一种血氧饱和度检测系统,由于从频域中计算血氧饱和度且采用了新公式来计算归一化后的值,因而计算更简单,而且可以减小随机干扰,因而检测精度更高。 Oximetry uses a detection system aspect of the invention a method of detecting blood oxygen saturation, as calculated from the oxygen saturation in the frequency domain and the use of a new formula to calculate the normalized value of one of the post, and thus easier to calculate , and random noise can be reduced, and thus a higher detection accuracy.
Ansprüche(1)  übersetzt aus folgender Sprache: Chinesisch
1. 一种血氧饱和度检测方法,包括如下步骤: 51) 、信号采集,通过信号采集装置来采集携带血氧信号的红光检测信号Red和红外光检测信号Ir; 52) 、自适应归一化处理,利用自适应归一化处理装置,对预处理后的检测数据进行归一化处理; 53) 、FFT处理,通过FFT装置将归一化处理后的数据采用快速傅里叶变换,从时域变换到频域; 54) 、R值计算,根据FFT处理处理后得到的频域归一化后的数据,计算出R值; 55) 、血氧饱和度计算,利用所计算出的R值,根据查表法得到对应的血氧饱和度值; 步骤S2)中的归一化处理是分别计算红光的交流分量Ra。 A method for detecting blood oxygen saturation, comprising the steps of: 51), signal acquisition, signal acquisition means to acquire by carrying red blood oxygen signal detection signal Red and infrared light detection signal Ir; 52), the adaptive normalization A treatment, using adaptive normalization processing means for detecting data preprocessing were normalized after treatment; 53), FFT processing, data by the FFT means after the normalization process of using fast Fourier transform, from the time domain to the frequency domain; 54), R value calculation, based on data in the frequency domain FFT post-processing treatment was normalized to calculate the R value; 55), oxygen saturation calculated using the calculated R value, to obtain the corresponding oxygen saturation values based on a lookup table; step S2) in the normalization process is calculated separately AC component Ra red. 与直流分量Rd。 And the DC component Rd. 和红外光的交流分量IRa。 And infrared light AC component IRa. 与直流分量IRd。 And the DC component IRd. ,然后通过如下公式得到归一化后的值VI和V2, Then obtained by the following formula normalized values VI and V2,
Figure CN101933810BC00021
V2 =IRac, 式中,Ra。 V2 = IRac, where, Ra. 是红光的交流分量;Rd。 AC component is red; Rd. 是红光的直流分量;IRa。 DC component is red; IRa. 是红外光的交流分量;IRd。 AC component of the infrared light; IRd. 是红外光的直流分量。 DC component of infrared light.
Beschreibung  übersetzt aus folgender Sprache: Chinesisch
一种血氧饱和度检测方法 A method for detecting blood oxygen saturation

技术领域 TECHNICAL FIELD

[0001] 本发明涉及医疗器械技术领域,具体涉及血氧饱和度检测技术,特别涉及一种血氧饱和度检测方法。 [0001] The present invention relates to the field of medical devices, and more particularly oxygen saturation detection technology, particularly to a method for detecting blood oxygen saturation.

背景技术 Background technique

[0002] 无创血氧饱和度检测是基于动脉血液对光的吸收量随动脉波动而变化的原理。 [0002] Non-invasive blood oxygen saturation detection is the principle artery fluctuate with changes based on light absorption of arterial blood. 透射式血氧饱和度检测中,当透光区域动脉血管搏动时,动脉血液对光的吸收量将随之变化,称为脉动分量或交流量(AC);而皮肤、肌肉、骨骼和静脉血等其他组织对光的吸收是恒定不变的,称为直流量(DC)。 Transmissive blood oxygen saturation test, when the transparent area artery pulsatility, arterial blood absorption of light will change, known as the ripple component or AC quantities (AC); and the skin, muscle, bone and blood Absorption of other organizations and other light is constant, called straight flow (DC). 如果忽略由于散射、反射等因素造成的衰减。 If you ignore the attenuation due to scattering, reflection and other factors. 根据比尔-朗伯定律(Beer-LambertLaw)可以知道, According to Beer - Lambert law (Beer-LambertLaw) can know,

[0003] [0003]

Figure CN101933810BD00031

[0004] 其中,Iwt是光电探测器的输出电流,Iin是二极管的输入电流(对应不同的红光和红外光),C是血液的浓度,L是两个LED和探测器之间的距离,S是饱和度,0。 [0004] where, Iwt is the photodetector output current, Iin is the input current of the diode (corresponding to a different red and infrared light), C is the concentration of the blood, L is the distance between the two LED and detector, S is the saturation, 0. 和0 ^分别表示材料系数。 And 0 ^ denote material factor.

[0005] 血氧饱和度计算中常常先计算比率值R(RatioofRatios),再根据R来计算血氧饱和度,血氧饱和度测量的关键也就在于R值的计算。 [0005] The calculation is often first calculate the value of the ratio R (RatioofRatios), and then the R key to calculate oxygen saturation, oxygen saturation measured R value also lies in oxygen saturation calculation. 如果R值的计算精度得以提高,那么血氧饱和度的测量精度就相应的提高。 If the R-value calculation accuracy is improved, then the measurement accuracy of oxygen saturation is correspondingly increased.

[0006] 目前,对R值的计算广泛使用的是峰-峰值法。 [0006] Currently, the R value is widely used to calculate peak - law. 在每个脉搏期间红光/红外光的波形具有一个最大值和最小值,分别为RH,其中,&对应的是心脏收缩时,即动脉血体积最大时的值;RH对应的是心脏舒张时,即动脉血体积最小时的值。 In each of the pulse waveform during the red / infrared light having a maximum and minimum, respectively, RH, wherein, & correspond to the systolic, i.e., the maximum value of arterial blood volume; RH corresponds to a diastolic the value of the arterial blood volume that is most hours. 考虑到光通过均匀介质的延时系数,可以表示为: Considering the light through a homogeneous medium delay factor, it can be expressed as:

[0007] [0007]

Figure CN101933810BD00032

[0008] 其中,I。 [0008] wherein, I. 表不入射光强度,a表不组织吸光率,a&表不动脉血吸光率,A!;表不吸光系数,d表示穿透距离,Ad表示心脏收缩和舒张造成的变化量。 Table no incident light intensity, a table does not organize absorbance, a & table does not arterial absorbance, A !; table does not extinction coefficient, d represents penetration distance, Ad represents the amount of change in systolic and diastolic caused.

[0009] 相似地, [0009] Similarly,

[0010 [0010

Figure CN101933810BD00033

[0011] 烙以h面个笺式作一个hk值,得到 [0011] h face branded with a scratch pad for a hk value to give

[0012] [0012]

Figure CN101933810BD00034

[0013] 两边取对数,得到 [0013] The logarithmic both sides to give

[0014] [0014]

Figure CN101933810BD00035

[0015] 同样地,红外光可以得到 [0015] Similarly, the infrared light can be obtained

[0016] [0016]

Figure CN101933810BD00041

[0017] 其中,风表示红外光最小值;IRH表示红外光最大值。 [0017] where wind represents the minimum value of the infrared light; IRH represents infrared light maximum.

[0018] 诵讨以h公式,可以得到 [0018] In h chanting discuss formulas, you can get

[0019] [0019]

Figure CN101933810BD00042

[0020] 从以上公式描述中可以看出,采用峰-峰值法计算的比率值仅与脉搏信号的峰值点和谷值点信号相关,因此这种算法的信噪比不高,比率值容易受到干扰信号的影响。 [0020] As can be seen from the above formula describes, using peak - the ratio value is only related to the peak point of the pulse signal point signal peaks and troughs calculated, so this algorithm is not high signal to noise ratio, the ratio of the value of vulnerable interference signal.

[0021] 为了提高信噪比,最近又出现了一种叫做微分法的方法,与峰-峰值法不同的是, 微分法并不选择峰值点和谷值点进行计算,而是在峰值和谷值之间选取一段样本点进行微分计算,即分别计算相邻两点之间红光/红外光交流量的差值与其直流值的比值,两个比值再求比值。 [0021] In order to improve the signal to noise ratio, and recently there has been a method called differential method, and peak - peak method is different, the differential method does not choose the peak point and valley point calculations, but the peaks and valleys Choose between values over the sample point differential calculation, namely calculate the ratio between the adjacent two red / infrared light amount of the difference between the exchange and its current value, and then seek the ratio of two ratios. 最后,将得到的所有比率值平均后得到该段数据的平均比率值。 Finally, after all the obtained value of the ratio of the mean value of the average ratio obtained segment of data. 微分法计算公式如下: Calculate the differential method using the following formula:

[0022] [0022]

Figure CN101933810BD00043

[0023] 其中,Iwt是光电探测器的输出电流,Iin是二极管的输入电流(对应不同的红光和红外光),C是血液浓度,L是LED灯与探测器之间的距离,S是饱和度,0 ^和0 ^分别表示材料系数。 [0023] where, Iwt is the photodetector output current, Iin is the input current of the diode (corresponding to a different red and infrared light), C is a blood concentration, L is the distance between the LED and detector, S is saturation, and 0 ^ 0 ^ denote material factor.

[0024] 又由 [0024] and by the

Figure CN101933810BD00044

[0028] 将两个波形相除,即可得到比率 [0028] The division of the two waveforms, you can get rate

[0029] [0029]

Figure CN101933810BD00045

[0030] 即 [0030] That

[0031] [0031]

Figure CN101933810BD00051

[0032] 求平均后得到「00331 [0032] After averaging get "00331

Figure CN101933810BD00052

[0034] 从以上微分法的计算公式中可以知道,比率值计算方式与选取的每个样本点的交流量相关,即通过增加样本点的方式,提高了算法的信噪比。 [0034] From the above formula can know the differential method, the ratio of the value calculated with the exchange volume for each sample point selection of relevant, by increasing the sample points the way to improve the signal to noise ratio of the algorithm. 但是,由于微分法是选取脉搏波形中任意一段数据,这样的方式没有考虑到脉搏波形各段在计算血氧饱和度时所占的权重,降低了血氧饱和度计算的精度。 However, due to the differential method is to select any period of the pulse waveform data, this approach does not take into account in the calculation of the pulse waveform oxygen saturation percentage of the weight of each segment, reducing the accuracy of the oxygen saturation calculation.

[0035] 此外,从人体采集到的脉搏信号,经前置通道进入处理器时,就伴随着各种各样的噪声和干扰,如工频干扰、基线漂移、运动干扰、低灌注等,这些都会影响到R值,最终影响血氧饱和度测量的准确性。 [0035] In addition, the human body collected pulse signal, when the front channel into the processor, it is accompanied by a variety of noise and interference, such as frequency interference, baseline drift, movement interference, low perfusion, these It will affect the R-value, and ultimately affect the accuracy of oximetry measurements.

[0036] 综上所述,目前为了能够提高血氧饱和度测量的精度,主要采用了峰-峰值法和微分法来计算比率值。 [0036] In summary, the present in order to improve the accuracy of oximetry, mainly in the peak - and differential methods to calculate the value of the ratio. 对于峰-峰值法,当人体血氧饱和度低于80%时,峰-峰值法得到的血氧饱和度曲线峰值并不能够准确地表示血氧饱和度,因此并不能很好地解决低饱和度的问题。 For peak - law, when the body is less than 80% oxygen saturation, peak - peak peak oxygen saturation curve method was not able to accurately represent oxygen saturation, and therefore not a good solution low in saturated question of degree. 对于微分法,由于通过计算每相邻两点之间的比率值来求得该段样本点的比率值,虽然可以降低噪声对信号的影响,但是由于其比率值与每相邻的样本点的比率值相关,当出现一个或一组噪声信号时,最后通过计算得到的平均比率值将受到很大的影响。 For the differential method, since the calculation of the ratio between the values obtained for each ratio of adjacent points to the value of the segment sample point, although you can reduce the effects of noise on the signal, but because of its value and the ratio of adjacent sample points each the ratio of the value of the relevant, when there is one or a group of the noise signal, the final value is obtained by calculating the average ratio will be greatly affected.

[0037] 其实现有技术还存在一个不那么引人注意的问题,那就是现有技术一般都是从时域计算R值,然后就根据R值计算出血氧饱和度。 [0037] In fact, the prior art there is a less interesting problem that the prior art are generally calculated R value from the time domain, and then calculated based on the R value oxygen saturation. 这就导致计算过程较为复杂,而且不能充分发挥时域和频域的优势,最终导致R值的计算结果不够精确。 This results in the calculation process is more complex and can not take full advantage of the time domain and frequency domain, resulting in the calculation result R value is not precise enough. 所以,现有检测血氧饱和度的方法均存在检测精度不高的问题,需要改进。 Therefore, the existing method for detecting blood oxygen saturation exist in detection accuracy is not high, need to be improved.

发明内容 SUMMARY OF THE INVENTION

[0038] 本发明所要解决的技术问题是提供一种血氧饱和度检测方法,解决现有技术中血氧饱和度检测技术复杂而且精度不够高的问题。 [0038] technical problem to be solved by the present invention is to provide an oxygen saturation detection methods, to solve the prior art oximetry testing technology complexity and accuracy is not high enough problems.

[0039] 为解决上述技术问题,本发明采用如下技术方案: [0039] In order to solve the above technical problem, the present invention adopts the following technical scheme:

[0040] 一种血氧饱和度检测方法,包括如下步骤: [0040] A blood oxygen saturation detection method comprising the steps of:

[0041] S1)、信号采集,通过信号采集装置来采集携带血氧信号的红光检测信号Red和红外光检测信号Ir; [0041] S1), signal acquisition, through the signal acquisition device to collect blood oxygen carrying red signal detection signal Red and infrared light detection signal Ir;

[0042] S2)、预处理,即通过预处理装置去掉红光检测信号Red和红外光检测信号Ir中环境光和高频干扰; [0042] S2), pre-treatment, that is, remove red detection signal Red and infrared light detection signal Ir in ambient light and high-frequency interference by pretreatment unit;

[0043]S3)、自适应归一化处理,主要是利用自适应归一化处理装置,对预处理后的检测数据进行归一化处理; [0043] S3), adaptive normalization process, mainly using adaptive normalization processing means for detecting data preprocessing normalized after treatment;

[0044] S4)、FFT处理,通过FFT装置将归一化后的数据VI和V2采用快速傅里叶变换,从时域变换到频域; [0044] S4), FFT processing by FFT means normalized data VI and V2 using fast Fourier transform from the time domain to the frequency domain;

[0045]S5)、R值计算,根据FFT处理处理后得到的频域归一化后的数据,计算出R值; [0045] S5), R value calculation, based on data in the frequency domain after FFT processing treatment obtained after normalization, to calculate the R value;

[0046] S6)、血氧饱和度计算,利用R值的曲线,根据查表法得到对应的血氧饱和度值; [0046] S6), oxygen saturation calculations, the use of R-value curve, to obtain the corresponding oxygen saturation value based on the look-up table;

[0047] 步骤S3)中所述归一化处理时,分别计算红光的交流分量Ra。 [0047] Step S3) in the normalization process, the AC component are calculated Ra red. 与直流分量Rd。 And the DC component Rd. 和红外光的交流分量IRa。 And infrared light AC component IRa. 与直流分量IRd。 And the DC component IRd. ,然后通过如下公式得到归一化后的值VI和V2, Then obtained by the following formula normalized values VI and V2,

[0048] [0048]

Figure CN101933810BD00061

[0049] V2 =IRac, [0049] V2 = IRac,

[0050] 式中,Ra。 [0050] where, Ra. 是红光的交流分量;Rd。 AC component is red; Rd. 是红光的直流分量;IRa。 DC component is red; IRa. 是红外光的交流分量; IRd。 AC component of the infrared light; IRd. 是红外光的直流分量。 DC component of infrared light.

[0051] 本发明的有益效果是: [0051] the beneficial effects of the present invention are:

[0052] 采用了本发明技术方案的一种血氧饱和度检测方法,由于从红光和红外光的频域中计算血氧饱和度,相对于现有技术从时域计算血氧来讲更简单,而且可以减小随机干扰,因而检测精度更高。 [0052] using a blood oxygen saturation detection method aspect of the present invention, since the calculation of oxygen saturation from the red and infrared light in the frequency domain, as opposed to the prior art in terms of oxygen is calculated from the time domain more simple and random interference can be reduced, and thus a higher detection accuracy. 实验证明,采用本发明基于频域的血氧估计法,能计算灌注强度为〇. 3%的脉搏信号,且血氧饱和度值在70% -100%能获得精度在1%以内的血氧饱和度值。 Experiments show that the use of the present invention is based on oxygen estimation in the frequency domain, can calculate the intensity of perfusion billion. 3% of the pulse signal, and oxygen saturation value of 70% -100% accuracy can be obtained in less than 1% of oxygen saturation value.

附图说明 Brief Description

[0053] 图1是本发明具体实施方式中血氧饱和度检测系统的组成原理示意框图。 [0053] FIG. 1 is a specific embodiment of the present invention is composed of the principles of the way oxygen saturation detection system schematic diagram.

[0054] 图2是本发明具体实施方式中血氧饱和度检测方法的流程图。 [0054] FIG. 2 is a flow chart showing the oxygen saturation detection method embodiment of the present invention.

[0055] 图3是本发明具体实施方式中检测信号经FFT后的幅度谱。 [0055] FIG. 3 is a specific embodiment, the amplitude detection signal by the FFT spectrum after the present invention.

[0056] 下面将结合附图对本发明作进一步详述。 [0056] the following with reference to the present invention will be further described in detail.

具体实施方式 DETAILED DESCRIPTION

[0057] 如图1所示,本具体实施方式提供的一种血氧饱和度检测系统,包括顺序连接的: 信号采集装置、陷波器、低通滤波器、自适应归一化装置、FFT(FastFourierTransform,快速傅氏变换)装置、R值计算装置、卡尔曼滤波装置和血氧饱和度计算装置;其中陷波器、低通滤波器可以合称前置处理装置。 [0057] As shown, the present embodiment provides a specific oxygen saturation detection system, including the sequence of connections: signal acquisition device, notch filter, low pass filter, adaptive normalization means, FFT (FastFourierTransform, Fast Fourier Transform) unit, R value calculating means, Kalman filtering apparatus and oxygen saturation computing means; wherein the notch filter, low-pass filter can be collectively referred to as pre-processing unit.

[0058] 如图2所示,本具体实施方式提供的一种血氧饱和度检测方法,包括如下步骤: [0058] shown in Figure 2, an oxygen saturation detecting method of the present embodiment provides a specific, comprising the steps of:

[0059] 1、信号采集,通过信号采集装置来采集携带血氧信号的红光检测信号Red和红外光检测信号Ir。 [0059] 1, signal acquisition, through the signal acquisition device to collect blood oxygen carrying red signal detection signal Red and infrared light detection signal Ir.

[0060] 2、预处理,即通过陷波器和低通滤波器,对红光检测信号Red和红外光检测信号Ir进行预处理,主要去掉环境光和高频干扰。 [0060] 2, pretreatment, namely through the notch filter and low-pass filter, the detection signal Red to red and infrared light detection signal Ir pretreatment, mainly to remove the ambient light and high-frequency interference.

[0061] 陷波器可以去掉检测信号中环境光的干扰,而低通滤波器可以去掉检测信号中的高频干扰。 [0061] notch filter can remove the interference of ambient light detection signal and the low-pass filter can remove high-frequency interference detection signal. 如图1所示,Redl是经过陷波器滤波后的红光;Irl是经过陷波器滤波后的红外光;Red'是经过低通滤波器后的红光;Ir'是经过低通滤波器后的红外光。 Figure 1, Redl is through the red notch filtered; Irl is after notch filter filtering infrared light; Red 'is the result of a low-pass filter red; Ir' is a low-pass filter Infrared light is after.

[0062] 需要说明的是,由于一般只考虑脉搏信号的基波、二次谐波和三次谐波,所以对于带宽为0. 5HZ-5HZ的脉搏信号,一般使用截止频域为15HZ的低通滤波器即可达到满意效果。 [0062] It should be noted that, due to generally consider only the fundamental, second harmonic and third harmonic of the pulse signal, so the bandwidth of the pulse signal 0. 5HZ-5HZ generally used as a low-pass cutoff frequency domain of 15HZ Filters can achieve satisfactory results. 当然,必要时还可以根据需要确定滤波器的阶数。 Of course, if necessary, to determine the order of the filter as needed.

[0063] 3、自适应归一化处理,主要是利用自适应归一化处理装置,对预处理后的检测数据进行归一化处理得到VI和V2 ; [0063] 3, adaptive normalization process, mainly using adaptive normalization processing means for detecting data preprocessed normalized to give VI and V2;

[0064] [0064]

Figure CN101933810BD00071

[0065]V2 =IRac(公式2) [0065] V2 = IRac (Equation 2)

[0066] 式中,Ra。 [0066] where, Ra. 是红光的交流分量;Rd。 AC component is red; Rd. 是红光的直流分量;IRa。 DC component is red; IRa. 是红外光的交流分量; IRd。 AC component of the infrared light; IRd. 是红外光的直流分量。 DC component of infrared light.

[0067] 4、FFT处理,通过FFT装置将归一化后的数据VI和V2采用快速傅里叶变换,从时域变换到频域。 [0067] 4, FFT processing by FFT means normalized data VI and V2 using fast Fourier transform from the time domain to the frequency domain.

[0068]FFT部分通过对VI和V2进行FFT变换,获得如图3所示VI和V2在频域的幅度谱。 [0068] FFT section VI and V2 by performing an FFT VI and V2 obtained as shown in FIG. 3 in the frequency domain amplitude spectrum.

[0069]VI和V2在FFT变换前可以进行加窗处理,如加矩形窗或布莱克曼窗等,而FFT变换的长度可以是1〇24、2048、4096等,这些参数根据需要而定。 [0069] VI and V2 can be carried out before the FFT transform windowing processing, such as rectangular window or Blackman windows, etc., and the length of the FFT transform can be 1〇24,2048,4096 etc. These parameters may be required.

[0070] 其中的VI和V2就是下面的两个表达式对应的变量,理论上直接用下面的比值公3 [0070] where VI and V2 is the following two expressions corresponding variable, with the following ratio theoretically direct public 3

Figure CN101933810BD00072

求R值,即分别对Rac;/Rd。 Seeking R value, namely for Rac; / Rd. 和IRac;/IRd。 And IRac; / IRd. 进行FFT变换,然后根据它们在脉搏 FFT transform, then according to their pulse

Figure CN101933810BD00073

基波处的比值得到R值,但是很多处理器只能处理整数,用这个公式就不适合(因为Ra。/RdcXl,IRac;/IRdc;〈l),就可以将公式变珀比种情况下遇到的问题是,Rac*IRd。 R ratio obtained at the fundamental value, but a lot of the processor can only handle integer, use this formula does not fit (because Ra / RdcXl, IRac;. / IRdc; <l), you can change the formula than the kind of case Mrs problems encountered, Rac * IRd. 的乘积很大或IRac*Rd。 The product of large or IRac * Rd. 的乘积很大,导致®埋益》出,而解决它们的最好办法是将分别对 The product is large, resulting in ® buried benefits "out, and the best way to resolve them is to separately

Figure CN101933810BD00074

1与IRa。 1 and IRa. 进行FFT变换,再在它们的频域得到R比值,这种方法可以在更多的处理器上实现。 FFT transform, frequency domain and then get in their R ratio, this method can be in more processor.

[0071] 5、R值计算,根据FFT处理处理后得到的频域检测数据,计算出R值。 [0071] 5, R value calculation, based on the frequency domain processing test data obtained after FFT processing to calculate the R value. R值计算属于现有技术,本文对此不再详述。 R values which belong to the prior art, this article will not elaborate. 本具体实施具体而言,可先在FV1和FV2 (FV1和FV2分别是VI和V2经过FFT变换后的信号)的频域各自选出最大的20个峰值,在这些峰值中查询信号的基波和谐波处FV1/FV2是否在某个很小的范围内,如果在某个很小的范围内则此处的基波为脉率,且此处的FV1/FV2就是R值。 The specific implementation specifically, first in FV1 and FV2 (FV1 and FV2 VI and V2 are converted via the signal FFT) frequency domain each elect 20 largest peak, the interrogation signal peaks in these fundamental and harmonic FV1 / FV2 whether within a small range, fundamental if within a small range of pulse rate is here, and FV1 / FV2 here is the R value.

[0072] 6、卡尔曼滤波,可以防止随机噪声引起的干扰,防止信号发生突变,即对R值起到平滑的作用。 [0072] 6, Kalman filtering, you can prevent random noise interference caused by mutations prevent signal that the R value the role played smooth.

[0073] 需要强调的是,在对R值进行卡尔曼滤波时,需要根据残差和信号质量指数FSQI 判断是否继续进行卡尔曼滤波,如果残差太大或信号质量指数小则放弃卡尔曼滤波,其中信号质量指数根据V2在频域的幅度谱确定,具体计算公式如下: [0073] It should be emphasized that, in the value of R Kalman filter, you need to determine whether to continue the Kalman filter based on a residual and signal quality index FSQI, if the residual signal quality index is too large or small the abandonment Kalman Filter wherein the signal quality index based on V2 in the frequency domain amplitude spectrum to determine the specific formula is as follows:

[0074] [0074]

Figure CN101933810BD00081

[0075] 其中,S是V2在频域脉率处的幅度,N1、N2…N512是V2在频域非直流的幅度。 [0075] where, S is V2 amplitude in the frequency domain at the pulse rate, N1, N2 ... N512 amplitude in the frequency domain is a non-V2 DC.

[0076] 7、血氧饱和度计算,利用R值的曲线,根据查表法得到对应的血氧饱和度值,该部分属于现有技术,本文不再详述。 [0076] 7, oxygen saturation calculated using curve R value, based on look-up table to obtain the corresponding oxygen saturation value, which in part, prior art, the paper will not elaborate.

[0077] 本具体实施方式的血氧饱和度计算系统,采用本具体实施方式的血氧饱和度检测方法,从红光和和红外光的频域中计算血氧饱和度,相对与现有技术从时域计算血氧来讲更简单,而且可以减小随机干扰。 [0077] The specific embodiments of oxygen saturation computing system, according to this particular embodiment of the oxygen saturation detection method, calculated from the red and infrared light and oxygen saturation in the frequency domain, as opposed to the prior art oxygen is calculated from the time domain in terms of more simple, and can reduce random noise. 实验证明,采用本发明基于频域的血氧估计法,能计算灌注强度为〇. 3%的脉搏信号,且血氧饱和度值在70% -100%能获得精度在1 %以内的血氧饱和度值。 Experiments show that the use of the present invention is based on oxygen estimation in the frequency domain, can calculate the intensity of perfusion billion. 3% of the pulse signal, and oxygen saturation value of 70% -100% accuracy can be obtained in less than 1% of oxygen saturation value.

[0078] 以上内容是结合具体的优选实施方式对本发明所作的进一步详细说明,不能认定本发明的具体实施只局限于这些说明。 [0078] The above is described in further detail with reference to specific preferred embodiments of the present invention is made, can not identify a specific embodiment of the present invention is limited to these instructions. 对于本发明所属技术领域的普通技术人员来说,在不脱离本发明构思的前提下,还可以做出若干简单推演或替换,都应当视为属于本发明的保护范围。 For ordinary skill in the art of the present invention, without departing from the inventive concept premise, you can also make a number of simple deduction or replacement should be considered as belonging to the scope of the present invention.

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