WO2017193593A1 - 一种血压测量方法及装置 - Google Patents

一种血压测量方法及装置 Download PDF

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WO2017193593A1
WO2017193593A1 PCT/CN2016/113115 CN2016113115W WO2017193593A1 WO 2017193593 A1 WO2017193593 A1 WO 2017193593A1 CN 2016113115 W CN2016113115 W CN 2016113115W WO 2017193593 A1 WO2017193593 A1 WO 2017193593A1
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sequence
signal
decomposition
difference
pulse
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郑晓波
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Guangzhou Shiyuan Electronics Thecnology Co Ltd
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Guangzhou Shiyuan Electronics Thecnology Co Ltd
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording for evaluating the cardiovascular system, e.g. pulse, heart rate, blood pressure or blood flow
    • A61B5/021—Measuring pressure in heart or blood vessels
    • A61B5/022—Measuring pressure in heart or blood vessels by applying pressure to close blood vessels, e.g. against the skin; Ophthalmodynamometers
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7221—Determining signal validity, reliability or quality
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7225—Details of analogue processing, e.g. isolation amplifier, gain or sensitivity adjustment, filtering, baseline or drift compensation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7235—Details of waveform analysis
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7235—Details of waveform analysis
    • A61B5/725—Details of waveform analysis using specific filters therefor, e.g. Kalman or adaptive filters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7235—Details of waveform analysis
    • A61B5/7253—Details of waveform analysis characterised by using transforms

Definitions

  • the present invention relates to the field of signal detection and processing technologies, and in particular, to a blood pressure measurement method and apparatus.
  • Blood pressure is the pressure that acts on the blood vessel wall when blood flows through a blood vessel. It is the driving force that pushes blood through the blood vessels.
  • the ventricle contracts and blood flows from the ventricle into the artery. At this time, the blood has the highest pressure on the artery, called systolic blood pressure (SBP).
  • SBP systolic blood pressure
  • the ventricle is dilated, the arteries are elastically retracted, and the blood continues to flow forward slowly, but the blood pressure drops.
  • the pressure at this time is called diastolic blood pressure (DBP).
  • DBP diastolic blood pressure
  • blood pressure refers to arterial blood pressure, which is an important physiological parameter of cardiovascular function.
  • the current measurement method of blood pressure is the oscillometric method, including the ascending oscillometric method and the descending oscillometric method.
  • the principle of the ascending oscillometric method is to inflate the cuff at a certain rate, detect the change of the amplitude of the oscillation wave during the pumping process, and obtain the envelope of the oscillation amplitude variation.
  • the pressure at the position where the maximum amplitude is located is the average pressure, and the pressure at which the amplitude of the amplitude is multiplied by a coefficient As is the systolic pressure, and the amplitude of the amplitude is multiplied by a coefficient Ad.
  • the pressure at the site is diastolic, where both As and Ad parameters are calibrated by clinical trials.
  • the oscillometric method needs to detect the amplitude change of the pulse signal, identify the pulse amplitude sequence on the pulse signal to obtain an envelope, and then calculate the blood pressure according to the envelope.
  • the pulse signal has interference, directly identifying the pulse signal is prone to error, resulting in a pulse envelope calculation error, which in turn causes a blood pressure calculation error.
  • the embodiment of the invention provides a blood pressure measuring method and device, which can improve the accuracy of blood pressure measurement.
  • Embodiments of the present invention provide a blood pressure measurement method, including:
  • the blood pressure of the user is calculated based on the effective pulse signal.
  • the decomposing the pulse signal into the decomposition signals in the N preset frequency ranges specifically includes:
  • a band pass filter is used to decompose the pulse signal into decomposition signals within N preset frequency ranges.
  • the calculating the difference sequence mean of the pulse maximum value sequence in each of the decomposition signals, and using the decomposition signal with the smallest difference of the difference sequence as the effective pulse signal specifically includes:
  • the difference sequence mean of all the decomposition signals is compared, and the decomposition signal with the smallest difference of the difference sequence is used as the effective pulse signal.
  • the pulse maximum sequence is a sequence of maximum signal amplitudes in a neighborhood;
  • the first-order differential value sequence is a sequence of differences between adjacent two pulse maxima; and
  • the second-order differential value sequence is A sequence of differences between two adjacent first-order difference values.
  • an embodiment of the present invention further provides a blood pressure measuring device, including:
  • a signal detection module for detecting a pulse signal of the user
  • a signal decomposition module configured to decompose the pulse signal into decomposition signals in N preset frequency ranges; wherein, N ⁇ 1;
  • An effective pulse signal acquisition module configured to calculate a difference sequence mean of the pulse maximum sequence in each of the decomposition signals, and use the decomposition signal with the smallest difference of the difference sequence as the effective pulse signal;
  • a blood pressure calculation module configured to calculate a blood pressure of the user according to the effective pulse signal.
  • the signal decomposition module is specifically configured to decompose the pulse signal into decomposition signals in N preset frequency ranges by using a wavelet transform algorithm;
  • a band pass filter is used to decompose the pulse signal into decomposition signals within N preset frequency ranges.
  • the effective pulse signal acquisition module specifically includes:
  • An obtaining unit configured to acquire a sequence of pulse maxima in each of the decomposition signals one by one;
  • a first calculating unit configured to calculate, according to the pulse maximum value sequence, a first-order difference value sequence of the decomposition signal
  • a second calculating unit configured to calculate, according to the first-order differential value sequence, a second-order differential value sequence of the decomposition signal
  • a processing unit configured to perform normalization processing on the second-order differential value sequence to obtain a difference sequence mean value of the decomposition signal
  • the comparison unit is configured to compare the difference sequence mean of all the decomposition signals, and use the decomposition signal with the smallest difference of the difference sequence as the effective pulse signal.
  • processing unit specifically includes:
  • a first obtaining subunit configured to obtain an average of the second order difference value sequence
  • a calculating subunit configured to calculate a difference sequence mean value of the decomposition signal according to an average of the second order difference value sequence and an average of the pulse maximum value sequence.
  • the pulse maximum sequence is a sequence of maximum signal amplitudes in a neighborhood;
  • the first-order differential value sequence is a sequence of differences between adjacent two pulse maxima; and
  • the second-order differential value sequence is A sequence of differences between two adjacent first-order difference values.
  • the blood pressure measuring method and device provided by the embodiment of the invention can decompose the detected pulse signal of the user into decomposition signals in different frequency ranges, and then identify the effective pulse from the decomposition signal according to the average value of the difference sequence of each decomposition signal.
  • the signal calculates the user's blood pressure based on the effective pulse signal, thereby accurately identifying the effective pulse signal and improving the accuracy of the blood pressure measurement.
  • FIG. 1 is a schematic flow chart of one embodiment of a blood pressure measuring method provided by the present invention.
  • FIG. 2 is a waveform diagram of a fourth-order decomposition signal of wavelet transform in the blood pressure measurement method provided by the present invention
  • FIG. 3 is a waveform diagram of a fifth-order decomposition signal of wavelet transform in the blood pressure measurement method provided by the present invention.
  • FIG. 4 is a waveform diagram of a sixth-order decomposition signal of wavelet transform in the blood pressure measurement method provided by the present invention.
  • FIG. 5 is a waveform diagram of a seventh-order decomposition signal of wavelet transform in the blood pressure measurement method provided by the present invention.
  • Fig. 6 is a schematic structural view of an embodiment of a blood pressure measuring device provided by the present invention.
  • a schematic flowchart of an embodiment of a blood pressure measuring method provided by the present invention includes:
  • the pulse signal is decomposed into decomposition signals in N preset frequency ranges; wherein, N ⁇ 1;
  • the pulse signal is decomposed, the pulse signal is decomposed into different frequency ranges, the effective pulse signal is separated from the interference signal, and the decomposed signals in different frequency ranges are calculated.
  • the differential sequence mean of the pulse maxima sequence, wherein the decomposition signal with the smallest mean value of the difference sequence is the effective pulse signal.
  • the pulse envelope is calculated according to the pulse amplitude sequence of the effective pulse signal, and then the blood pressure of the user is calculated according to the pulse envelope, thereby realizing accurate identification of the effective pulse signal and improving the accuracy of the blood pressure measurement.
  • the decomposing the pulse signal into the decomposition signals in the N preset frequency ranges specifically includes:
  • a band pass filter is used to decompose the pulse signal into decomposition signals within N preset frequency ranges.
  • the parameters of the wavelet transform are set according to the N preset frequency ranges, and then the pulse signal is decomposed into N decomposition signals having different frequency ranges according to the wavelet transform algorithm.
  • N band pass filters are set according to N preset frequency ranges, wherein each band pass filter has a different bandwidth, and then the pulse signals are decomposed according to the N band pass filters. It is N decomposition signals with different frequency ranges.
  • the calculating the difference sequence mean of the pulse maximum value sequence in each of the decomposition signals, and using the decomposition signal with the smallest difference of the difference sequence as the effective pulse signal specifically includes:
  • the difference sequence mean of all the decomposition signals is compared, and the decomposition signal with the smallest difference of the difference sequence is used as the effective pulse signal.
  • the pulse maximum sequence is a sequence of maximum signal amplitudes in a neighborhood; the first-order difference value sequence is a sequence of differences between adjacent two pulse maxima; and the second-order differential value sequence is a phase A sequence of differences between two first-order difference values.
  • the local pulse maximum sequence of the signal can be used.
  • the difference sequence mean of each decomposition signal can be obtained. Comparing the differential sequence mean of all the decomposed signals, and obtaining the decomposition signal with the smallest mean value of the difference sequence, is the effective pulse signal.
  • the decomposition signals in different frequency ranges are different, and the difference sequence mean value is calculated according to the pulse maximum value sequence of each decomposition signal, and the seventh-order decomposition of the wavelet transform can be obtained.
  • the differential sequence mean of the signal is the smallest, so that the wavelet transform seventh-order decomposition signal is used as an effective pulse signal to calculate the user's blood pressure.
  • the blood pressure measurement method provided by the embodiment of the invention can decompose the detected pulse signal of the user into decomposition signals in different frequency ranges, and then identify the effective pulse signal from the decomposition signal according to the average value of the difference sequence of each decomposition signal. Further, the user's blood pressure is calculated according to the effective pulse signal, and the accurate identification of the effective pulse signal is realized, and the accuracy of the blood pressure measurement is improved.
  • the present invention also provides a blood pressure measuring device capable of realizing all the processes of the blood pressure measuring method in the above embodiment.
  • FIG. 6 is a schematic structural diagram of an embodiment of a blood pressure measuring device provided by the present invention, including:
  • a signal detecting module 1 configured to detect a pulse signal of a user
  • the signal decomposition module 2 is configured to decompose the pulse signal into decomposition signals in N preset frequency ranges; wherein N ⁇ 1;
  • the effective pulse signal acquisition module 3 is configured to calculate a differential sequence mean of the pulse maximum sequence in each of the decomposition signals, and use the decomposition signal with the smallest difference of the difference sequence as the effective pulse signal;
  • the blood pressure calculation module 4 is configured to calculate the blood pressure of the user according to the effective pulse signal.
  • the signal decomposition module is specifically configured to decompose the pulse signal into decomposition signals in N preset frequency ranges by using a wavelet transform algorithm;
  • a band pass filter is used to decompose the pulse signal into decomposition signals within N preset frequency ranges.
  • the effective pulse signal acquisition module specifically includes:
  • An obtaining unit configured to acquire a sequence of pulse maxima in each of the decomposition signals one by one;
  • a first calculating unit configured to calculate, according to the pulse maximum value sequence, a first-order difference value sequence of the decomposition signal
  • a second calculating unit configured to calculate, according to the first-order differential value sequence, a second-order differential value sequence of the decomposition signal
  • a processing unit configured to perform normalization processing on the second-order differential value sequence to obtain a difference sequence mean value of the decomposition signal
  • the comparison unit is configured to compare the difference sequence mean of all the decomposition signals, and use the decomposition signal with the smallest difference of the difference sequence as the effective pulse signal.
  • processing unit specifically includes:
  • a first obtaining subunit configured to obtain an average of the second order difference value sequence
  • a calculating subunit configured to calculate a difference sequence mean value of the decomposition signal according to an average of the second order difference value sequence and an average of the pulse maximum value sequence.
  • the pulse maximum sequence is a sequence of maximum signal amplitudes in a neighborhood;
  • the first-order differential value sequence is a sequence of differences between adjacent two pulse maxima; and
  • the second-order differential value sequence is A sequence of differences between two adjacent first-order difference values.
  • the blood pressure measuring device provided by the embodiment of the invention can decompose the detected pulse signal of the user into decomposition signals in different frequency ranges, and then identify the effective pulse signal from the decomposition signal according to the average value of the difference sequence of each decomposition signal. Further, the user's blood pressure is calculated according to the effective pulse signal, and the accurate identification of the effective pulse signal is realized, and the accuracy of the blood pressure measurement is improved.

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Abstract

一种血压测量方法，包括：检测用户的脉搏信号（S1）；将所述脉搏信号分解为N个预设频率范围内的分解信号；其中，N≥1（S2）；计算每个分解信号中的脉搏极大值序列的差分序列均值，并将差分序列均值最小的分解信号作为有效脉搏信号（S3）；根据所述有效脉搏信号计算用户的血压（S4）。相应的，还公开了一种血压测量装置。该血压测量方法能够提高血压测量的准确性。

Description

一种血压测量方法及装置 技术领域
本发明涉及信号检测与处理技术领域，尤其涉及一种血压测量方法及装置。
背景技术
血压(blood pressure，BP)是血液在血管内流动时，作用于血管壁的压力，它是推动血液在血管内流动的动力。心室收缩，血液从心室流入动脉，此时血液对动脉的压力最高，称为收缩压(systolic blood pressure，SBP)。心室舒张，动脉血管弹性回缩，血液仍慢慢继续向前流动，但血压下降，此时的压力称为舒张压(diastolic blood pressure，DBP)。由于血管分动脉、毛细血管和静脉，所以，也就有动脉血压、毛细血管压和静脉血压。通常所说的血压是指动脉血压，它是心血管功能的重要生理参数。
目前血压的测量方法为示波法，包括上升式示波法和下降式示波法。其中，上升式示波法的原理是，给袖套按照一定的速率打气，在打气过程中检测振荡波幅度的变化，求出振荡波幅变化的包络。其中，波幅最大值所处位置的压力为平均压，波幅最大值乘以一个系数As后计算出的波幅所处位置的压力为收缩压，波幅最大值乘于一个系数Ad后计算出的波幅所处位置的压力为舒张压，其中As和Ad两个参数通过临床试验标定。
但是，示波法需要检测脉搏信号的幅值变化，通过在脉搏信号上识别脉搏幅值序列以求得包络，再根据包络计算血压。当脉搏信号有干扰时，直接对脉搏信号进行识别容易出错，导致脉搏包络计算错误，进而造成血压计算错误。
发明内容
本发明实施例提出一种血压测量方法及装置，能够提高血压测量的准确性。
本发明实施例提供一种血压测量方法，包括：
检测用户的脉搏信号；
将所述脉搏信号分解为N个预设频率范围内的分解信号；其中，N≥1；
计算每个分解信号中的脉搏极大值序列的差分序列均值，并将差分序列均值最小的分解信号作为有效脉搏信号；
根据所述有效脉搏信号计算用户的血压。
进一步地，所述将所述脉搏信号分解为N个预设频率范围内的分解信号，具体包括：
采用小波变换算法，将所述脉搏信号分解为N个预设频率范围内的分解信号；
或者，采用带通滤波器，将所述脉搏信号分解为N个预设频率范围内的分解信号。
进一步地，所述计算每个分解信号中的脉搏极大值序列的差分序列均值，并将差分序列均值最小的分解信号作为有效脉搏信号，具体包括：
逐一获取每个分解信号中的脉搏极大值序列；
根据所述脉搏极大值序列，计算获得所述分解信号的一阶差分值序列；
根据所述一阶差分值序列，计算获得所述分解信号的二阶差分值序列；
对所述二阶差分值序列进行归一化处理，获得所述分解信号的差分序列均值；
比较所有分解信号的差分序列均值，将差分序列均值最小的分解信号作为有效脉搏信号。
进一步地，所述对所述二阶差分值序列进行归一化处理，获得所述分解信号的差分序列均值，具体包括：
求取所述二阶差分值序列的均值；
求取所述脉搏极大值序列的均值；
根据所述二阶差分值序列的均值和所述脉搏极大值序列的均值，计算获得所述分解信号的差分序列均值。
进一步地，所述脉搏极大值序列为邻域内最大信号幅值的序列；所述一阶差分值序列为相邻两个脉搏极大值的差值的序列；所述二阶差分值序列为相邻两个一阶差分值的差值的序列。
相应地，本发明实施例还提供一种血压测量装置，包括：
信号检测模块，用于检测用户的脉搏信号；
信号分解模块，用于将所述脉搏信号分解为N个预设频率范围内的分解信号；其中，N≥1；
有效脉搏信号获取模块，用于计算每个分解信号中的脉搏极大值序列的差分序列均值，并将差分序列均值最小的分解信号作为有效脉搏信号；以及，
血压计算模块，用于根据所述有效脉搏信号计算用户的血压。
进一步地，所述信号分解模块具体用于采用小波变换算法，将所述脉搏信号分解为N个预设频率范围内的分解信号；
或者，采用带通滤波器，将所述脉搏信号分解为N个预设频率范围内的分解信号。
进一步地，所述有效脉搏信号获取模块具体包括：
获取单元，用于逐一获取每个分解信号中的脉搏极大值序列；
第一计算单元，用于根据所述脉搏极大值序列，计算获得所述分解信号的一阶差分值序列；
第二计算单元，用于根据所述一阶差分值序列，计算获得所述分解信号的二阶差分值序列；
处理单元，用于对所述二阶差分值序列进行归一化处理，获得所述分解信号的差分序列均值；以及，
比较单元，用于比较所有分解信号的差分序列均值，将差分序列均值最小的分解信号作为有效脉搏信号。
进一步地，所述处理单元具体包括：
第一求取子单元，用于求取所述二阶差分值序列的均值；
第二求取子单元，用于求取所述脉搏极大值序列的均值；以及，
计算子单元，用于根据所述二阶差分值序列的均值和所述脉搏极大值序列的均值，计算获得所述分解信号的差分序列均值。
进一步地，所述脉搏极大值序列为邻域内最大信号幅值的序列；所述一阶差分值序列为相邻两个脉搏极大值的差值的序列；所述二阶差分值序列为相邻两个一阶差分值的差值的序列。
实施本发明实施例，具有如下有益效果：
本发明实施例提供的血压测量方法及装置，能够将检测到的用户的脉搏信号分解为不同频率范围内的分解信号，再根据每个分解信号的差分序列均值，从分解信号中识别出有效脉搏信号，进而根据有效脉搏信号来计算用户的血压，实现对有效脉搏信号的准确识别，提高血压测量的准确性。
附图说明
图1是本发明提供的血压测量方法的一个实施例的流程示意图；
图2是本发明提供的血压测量方法中小波变换第四阶分解信号的波形图；
图3是本发明提供的血压测量方法中小波变换第五阶分解信号的波形图；
图4是本发明提供的血压测量方法中小波变换第六阶分解信号的波形图；
图5是本发明提供的血压测量方法中小波变换第七阶分解信号的波形图；
图6是本发明提供的血压测量装置的一个实施例的结构示意图。
具体实施方式
下面将结合本发明实施例中的附图，对本发明实施例中的技术方案进行清楚、完整地描述，显然，所描述的实施例仅仅是本发明一部分实施例，而不是全部的实施例。基于本发明中的实施例，本领域普通技术人员在没有作出创造性劳动前提下所获得的所有其他实施例，都属于本发明保护的范围。
参见图1，本发明提供的血压测量方法的一个实施例的流程示意图，包括：
S1、检测用户的脉搏信号；
S2、将所述脉搏信号分解为N个预设频率范围内的分解信号；其中，N≥1；
S3、计算每个分解信号中的脉搏极大值序列的差分序列均值，并将差分序列均值最小的分解信号作为有效脉搏信号；
S4、根据所述有效脉搏信号计算用户的血压。
需要说明的是，在检测到用户的脉搏信号后，先对脉搏信号进行分解，将脉搏信号分解到不同频率范围内，使有效脉搏信号与干扰信号分开，再计算不同频率范围内的分解信号的脉搏极大值序列的差分序列均值，其中，差分序列均值最小的分解信号即为有效脉搏信号。在识别出有效脉搏信号后，根据有效脉搏信号的脉搏幅值序列计算脉搏包络，进而根据脉搏包络计算用户的血压，从而实现对有效脉搏信号的准确识别，提高血压测量的准确性。
进一步地，所述将所述脉搏信号分解为N个预设频率范围内的分解信号，具体包括：
采用小波变换算法，将所述脉搏信号分解为N个预设频率范围内的分解信号；
或者，采用带通滤波器，将所述脉搏信号分解为N个预设频率范围内的分解信号。
在一个优选地实施方式中，根据N个预设频率范围，设置小波变换的参数，进而根据小波变换算法，将脉搏信号分解为N个具有不同频率范围的分解信号。在另一个优选地实施方式中，根据N个预设频率范围，设置N个带通滤波器，其中，每个带通滤波器的带宽不同，进而根据N个带通滤波器，将脉搏信号分解为N个具有不同频率范围的分解信号。
进一步地，所述计算每个分解信号中的脉搏极大值序列的差分序列均值，并将差分序列均值最小的分解信号作为有效脉搏信号，具体包括：
逐一获取每个分解信号中的脉搏极大值序列；
根据所述脉搏极大值序列，计算获得所述分解信号的一阶差分值序列；
根据所述一阶差分值序列，计算获得所述分解信号的二阶差分值序列；
对所述二阶差分值序列进行归一化处理，获得所述分解信号的差分序列均值；
比较所有分解信号的差分序列均值，将差分序列均值最小的分解信号作为有效脉搏信号。
其中，所述脉搏极大值序列为邻域内最大信号幅值的序列；所述一阶差分值序列为相邻两个脉搏极大值的差值的序列；所述二阶差分值序列为相邻两个一阶差分值的差值的序列。
需要说明的是，在识别有效脉搏信号时，先获取每个分解信号中的脉搏极大值序列P(i)，i＝1，2，3，...，n，其中，获取每个分解信号局部的脉搏极大值序列即可。再根据脉搏极大值序列P(i)，计算每个分解信号的一阶差分值序列PD1(i)＝P(i+1)-P(i)，i＝1，2，3，...，n，进而根据一阶差分值序列PD1(i)，计算每个分解信号的二阶差分值序列PD2(i)＝PD1(i+1)-PD1(i)，i＝1，2，3，...，n。对每个分解信号的二阶差分值序列PD2(i)进行归一化处理，即可获得每个分解信号的差分序列均值。比较所有分解信号的差分序列均值，获取差分序列均值最小的分解信号，即为有效脉搏信号。
进一步地，所述对所述二阶差分值序列进行归一化处理，获得所述分解信号的差分序列均值，具体包括：
求取所述二阶差分值序列的均值；
求取所述脉搏极大值序列的均值；
根据所述二阶差分值序列的均值和所述脉搏极大值序列的均值，计算获得所述分解信号的差分序列均值。
需要说明的是，在对二阶差分值序列进行归一化处理时，先求取二阶差分值序列PD2(i)的均值Mean(PD2)＝(PD2(i)+PD2(i+1)+...)/n，再求取脉搏极大值序列P(i)的均值Mean(P)＝(P(i)+P(i+1)+...)/n，进而根据二阶差分值序列的均值Mean(PD2)和脉搏极大值序列的均值Mean(P)，计算分解信号的差分序列均值Y＝Mean(PD2)/Mean(P)，完成归一化操作。
如图2、图3、图4和图5所示，位于不同频率范围的分解信号不同，根据每个分解信号的脉搏极大值序列计算其差分序列均值，可以得出小波变换第七阶分解信号的差分序列均值最小，从而将小波变换第七阶分解信号作为有效脉搏信号来计算用户血压。
本发明实施例提供的血压测量方法，能够将检测到的用户的脉搏信号分解为不同频率范围内的分解信号，再根据每个分解信号的差分序列均值，从分解信号中识别出有效脉搏信号，进而根据有效脉搏信号来计算用户的血压，实现对有效脉搏信号的准确识别，提高血压测量的准确性。
相应的，本发明还提供一种血压测量装置，能够实现上述实施例中的血压测量方法的所有流程。
参见图6，是本发明提供的血压测量装置的一个实施例的结构示意图，包括：
信号检测模块1，用于检测用户的脉搏信号；
信号分解模块2，用于将所述脉搏信号分解为N个预设频率范围内的分解信号；其中，N≥1；
有效脉搏信号获取模块3，用于计算每个分解信号中的脉搏极大值序列的差分序列均值，并将差分序列均值最小的分解信号作为有效脉搏信号；以及，
血压计算模块4，用于根据所述有效脉搏信号计算用户的血压。
进一步地，所述信号分解模块具体用于采用小波变换算法，将所述脉搏信号分解为N个预设频率范围内的分解信号；
或者，采用带通滤波器，将所述脉搏信号分解为N个预设频率范围内的分解信号。
进一步地，所述有效脉搏信号获取模块具体包括：
获取单元，用于逐一获取每个分解信号中的脉搏极大值序列；
第一计算单元，用于根据所述脉搏极大值序列，计算获得所述分解信号的一阶差分值序列；
第二计算单元，用于根据所述一阶差分值序列，计算获得所述分解信号的二阶差分值序列；
处理单元，用于对所述二阶差分值序列进行归一化处理，获得所述分解信号的差分序列均值；以及，
比较单元，用于比较所有分解信号的差分序列均值，将差分序列均值最小的分解信号作为有效脉搏信号。
进一步地，所述处理单元具体包括：
第一求取子单元，用于求取所述二阶差分值序列的均值；
第二求取子单元，用于求取所述脉搏极大值序列的均值；以及，
计算子单元，用于根据所述二阶差分值序列的均值和所述脉搏极大值序列的均值，计算获得所述分解信号的差分序列均值。
进一步地，所述脉搏极大值序列为邻域内最大信号幅值的序列；所述一阶差分值序列为相邻两个脉搏极大值的差值的序列；所述二阶差分值序列为相邻两个一阶差分值的差值的序列。
本发明实施例提供的血压测量装置，能够将检测到的用户的脉搏信号分解为不同频率范围内的分解信号，再根据每个分解信号的差分序列均值，从分解信号中识别出有效脉搏信号，进而根据有效脉搏信号来计算用户的血压，实现对有效脉搏信号的准确识别，提高血压测量的准确性。
以上所述是本发明的优选实施方式，应当指出，对于本技术领域的普通技术人员来说，在不脱离本发明原理的前提下，还可以做出若干改进和润饰，这些改进和润饰也视为本发明的保护范围。

Claims (10)

  1. 一种血压测量方法，其特征在于，包括：
    检测用户的脉搏信号；
    将所述脉搏信号分解为N个预设频率范围内的分解信号；其中，N≥1；
    计算每个分解信号中的脉搏极大值序列的差分序列均值，并将差分序列均值最小的分解信号作为有效脉搏信号；
    根据所述有效脉搏信号计算用户的血压。
  2. 如权利要求1所述的血压测量方法，其特征在于，所述将所述脉搏信号分解为N个预设频率范围内的分解信号，具体包括：
    采用小波变换算法，将所述脉搏信号分解为N个预设频率范围内的分解信号；
    或者，采用带通滤波器，将所述脉搏信号分解为N个预设频率范围内的分解信号。
  3. 如权利要求1所述的血压测量方法，其特征在于，所述计算每个分解信号中的脉搏极大值序列的差分序列均值，并将差分序列均值最小的分解信号作为有效脉搏信号，具体包括：
    逐一获取每个分解信号中的脉搏极大值序列；
    根据所述脉搏极大值序列，计算获得所述分解信号的一阶差分值序列；
    根据所述一阶差分值序列，计算获得所述分解信号的二阶差分值序列；
    对所述二阶差分值序列进行归一化处理，获得所述分解信号的差分序列均值；
    比较所有分解信号的差分序列均值，将差分序列均值最小的分解信号作为有效脉搏信号。
  4. 如权利要求3所述的血压测量方法，其特征在于，所述对所述二阶差分值序列进行归一化处理，获得所述分解信号的差分序列均值，具体包括：
    求取所述二阶差分值序列的均值；
    求取所述脉搏极大值序列的均值；
    根据所述二阶差分值序列的均值和所述脉搏极大值序列的均值，计算获得所述分解信号的差分序列均值。
  5. 如权利要求3或4所述的血压测量方法，其特征在于，所述脉搏极大值序列为邻域内最大信号幅值的序列；所述一阶差分值序列为相邻两个脉搏极大值的差值的序列；所述二阶差分值序列为相邻两个一阶差分值的差值的序列。
  6. 一种血压测量装置，其特征在于，包括：
    信号检测模块，用于检测用户的脉搏信号；
    信号分解模块，用于将所述脉搏信号分解为N个预设频率范围内的分解信号；其中，N≥1；
    有效脉搏信号获取模块，用于计算每个分解信号中的脉搏极大值序列的差分序列均值，并将差分序列均值最小的分解信号作为有效脉搏信号；以及，
    血压计算模块，用于根据所述有效脉搏信号计算用户的血压。
  7. 如权利要求6所述的血压测量装置，其特征在于，所述信号分解模块具体用于采用小波变换算法，将所述脉搏信号分解为N个预设频率范围内的分解信号；
    或者，采用带通滤波器，将所述脉搏信号分解为N个预设频率范围内的分解信号。
  8. 如权利要求6所述的血压测量装置，其特征在于，所述有效脉搏信号获取模块具体包括：
    获取单元，用于逐一获取每个分解信号中的脉搏极大值序列；
    第一计算单元，用于根据所述脉搏极大值序列，计算获得所述分解信号的一阶差分值序列；
    第二计算单元，用于根据所述一阶差分值序列，计算获得所述分解信号的二阶差分值序列；
    处理单元，用于对所述二阶差分值序列进行归一化处理，获得所述分解信号的差分序列均值；以及，
    比较单元，用于比较所有分解信号的差分序列均值，将差分序列均值最小的分解信号作为有效脉搏信号。
  9. 如权利要求8所述的血压测量装置，其特征在于，所述处理单元具体包括：
    第一求取子单元，用于求取所述二阶差分值序列的均值；
    第二求取子单元，用于求取所述脉搏极大值序列的均值；以及，
    计算子单元，用于根据所述二阶差分值序列的均值和所述脉搏极大值序列的均值，计算获得所述分解信号的差分序列均值。
  10. 如权利要求8或9所述的血压测量装置，其特征在于，所述脉搏极大值序列为邻域内最大信号幅值的序列；所述一阶差分值序列为相邻两个脉搏极大值的差值的序列；所述二 阶差分值序列为相邻两个一阶差分值的差值的序列。
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