技术领域technical field
本发明涉及心电技术领域，尤其是涉及一种心电信号识别方法、系统和心电监测设备。The invention relates to the technical field of electrocardiogram, in particular to an electrocardiographic signal identification method, system and electrocardiographic monitoring equipment.
背景技术Background technique
当下心电监测技术的发展十分迅速，产生了很多面向非专业人员使用的动态心电监测设备，然而，在做心电图的过程中，存在如肌肉颤抖、仪器受到电磁干扰等情况会产生误差，使得计算机自动分析算法发生错误判断，给出错误的心电分析结果，对用户形成误导。所以，准确识别心电波形伪差，是动态心电监测设备亟需解决的问题之一。At present, the development of ECG monitoring technology is very rapid, and many dynamic ECG monitoring equipment for non-professionals have been produced. However, in the process of doing ECG, there will be errors such as muscle tremors and electromagnetic interference to the instrument, which makes The computer automatic analysis algorithm makes wrong judgments and gives wrong ECG analysis results, which misleads users. Therefore, accurate identification of ECG waveform artifacts is one of the problems that Holter monitoring equipment needs to solve urgently.
关于心电图中伪差的识别方法，主要是为实时心电分析的方法。实时心电分析指，用户采集信号的过程中每采集一小段信号分析一次，从而给用户一种即时分析的感觉。然而，现有的实时伪差识别方法，对于伪差的类别判断不全，判断粗略，在实时心电分析时的应用有限。若不依赖于识别算法，由人工识别伪差波形，则需要用户需要一定的心电专业知识，这也降低了应用的实用性。Regarding the identification method of the artifact in the ECG, it is mainly a method for real-time ECG analysis. Real-time ECG analysis refers to the analysis of each small section of signal collected by the user during the signal collection process, thus giving the user a feeling of instant analysis. However, the existing real-time artifact recognition methods are incomplete and rough in judging the types of artifacts, and their application in real-time ECG analysis is limited. If the artifact waveform is manually identified without relying on the identification algorithm, the user needs certain ECG expertise, which also reduces the practicability of the application.
发明内容Contents of the invention
有鉴于此，本发明的目的在于提供心电信号识别方法、系统和心电监测设备，可以对心电信号进行更加细致的判断，从而可以为后期信号处理提供了精确的数据，同时本发明的判断建立在一个采集周期采集的心电信号，可以达到实时分析的需求，适用于实时心电监测。In view of this, the object of the present invention is to provide an ECG signal recognition method, system and ECG monitoring equipment, which can make a more detailed judgment on the ECG signal, thereby providing accurate data for later signal processing. Judgment based on ECG signals collected in one acquisition cycle can meet the needs of real-time analysis and is suitable for real-time ECG monitoring.
第一方面，本发明实施例提供了一种心电信号识别方法，包括：获取一个采集周期采集的心电信号；根据所述心电信号，计算心电信号的标准差、子段标准差数组；根据所述标准差和所述子段标准差数组，识别所述心电信号是否存在大幅干扰；如果所述心电信号不存在大幅干扰，则根据所述标准差和子段标准差数组，计算心电信号的平均波峰孤立度和波峰孤立度数组；根据所述平均波峰孤立度和所述波峰孤立度数组，识别所述心电信号是否存在小幅干扰。In the first aspect, the embodiment of the present invention provides a method for identifying ECG signals, including: acquiring ECG signals acquired in one acquisition cycle; calculating the standard deviation of the ECG signals and the array of sub-segment standard deviations according to the ECG signals ; According to the standard deviation and the sub-segment standard deviation array, identify whether there is a large amount of interference in the ECG signal; if there is no large-scale interference in the ECG signal, then calculate according to the standard deviation and the sub-segment standard deviation array The average peak isolation of the ECG signal and an array of peak isolations; according to the average peak isolation and the array of peak isolations, identify whether there is a small interference in the ECG signal.
结合第一方面，本发明实施例提供了第一方面的第一种可能的实施方式，其中，所述根据所述心电信号，计算心电信号的标准差、子段标准差数组，包括：根据心电信号，计算心电信号的标准差；将所述心电信号按周期等分为多个心电波形片段；根据所述多个心电波形片段，获得每个心电波形片段的信号幅值；根据所述每个心电波形片段的信号幅值，计算每个心电波形片段的子段标准差，组成子段标准差数组。In combination with the first aspect, the embodiment of the present invention provides a first possible implementation manner of the first aspect, wherein the calculation of the standard deviation of the ECG signal and the sub-segment standard deviation array according to the ECG signal includes: According to the ECG signal, calculate the standard deviation of the ECG signal; divide the ECG signal into a plurality of ECG waveform segments according to the cycle; obtain the signal of each ECG waveform segment according to the plurality of ECG waveform segments Amplitude: according to the signal amplitude of each ECG waveform segment, calculate the sub-segment standard deviation of each ECG waveform segment to form an array of sub-segment standard deviations.
结合第一方面，本发明实施例提供了第一方面的第二种可能的实施方式，其中，所述根据所述标准差和所述子段标准差数组，识别所述心电信号是否存在大幅干扰，包括：判断所述标准差是否大于第一阈值；如果大于，则判定所述心电信号幅值序列的伪差类型为大幅干扰；如果不大于，则判断所有子段标准差是否存在大于所述第一阈值的子段标准差；如果是，则获取存在大于所述第一阈值的子段标准差的个数；判断所述大于所述第一阈值的子段标准差的个数是否大于第二阈值；如果是，则判定所述心电信号幅值序列的伪差类型为部分大幅干扰。In combination with the first aspect, the embodiment of the present invention provides a second possible implementation manner of the first aspect, wherein, according to the standard deviation and the array of sub-segment standard deviations, it is identified whether there is a large Interference, including: judging whether the standard deviation is greater than a first threshold; if greater, then judging that the artifact type of the ECG signal amplitude sequence is large interference; if not greater, judging whether all sub-segment standard deviations are greater than The sub-section standard deviation of the first threshold; if yes, obtain the number of sub-section standard deviations greater than the first threshold; determine whether the number of sub-section standard deviations greater than the first threshold is is greater than the second threshold; if yes, it is determined that the artifact type of the ECG signal amplitude sequence is partial large-scale interference.
结合第一方面，本发明实施例提供了第一方面的第三种可能的实施方式，其中，所述根据所述标准差和所述子段标准差数组，计算心电信号的平均波峰孤立度和波峰孤立度数组，包括：计算每个所述心电波形片段的信号幅值的欧式距离之和；从多个心电波形片段的信号幅值的欧式距离之和中选取最小值，并确定与所述最小值对应的基准信号幅值；从多个心电波形片段的信号幅值中，选取大于所述基准信号幅值的信号幅值；计算所有大于所述基准信号幅值的信号幅值的波峰孤立度；根据所述波峰孤立度，组建波峰孤立度数组；根据所述波峰孤立度数组，得到平均波峰孤立度。In combination with the first aspect, the embodiment of the present invention provides a third possible implementation manner of the first aspect, wherein the average peak isolation of the ECG signal is calculated according to the standard deviation and the array of sub-segment standard deviations and the peak isolation array, including: calculating the sum of the Euclidean distances of the signal amplitudes of each of the ECG waveform segments; selecting the minimum value from the sum of the Euclidean distances of the signal amplitudes of a plurality of ECG waveform segments, and determining A reference signal amplitude corresponding to the minimum value; from the signal amplitudes of a plurality of ECG waveform segments, select a signal amplitude greater than the reference signal amplitude; calculate all signal amplitudes greater than the reference signal amplitude The peak isolation of the value; according to the peak isolation, an array of peak isolation is established; according to the array of peak isolation, the average peak isolation is obtained.
结合第一方面，本发明实施例提供了第一方面的第四种可能的实施方式，其中，所述根据所述平均波峰孤立度和所述波峰孤立度数组，识别所述心电信号是否存在小幅干扰，包括：判断所述平均波峰孤立度是否大于第三阈值；如果大于，则判定所述心电信号幅值序列的伪差类型为小幅干扰；如果不大于，再判断所述波峰孤立度数组中的元素个数是否大于第四阈值；如果是，则判断所述心电信号幅值序列的伪差类型为部分小幅干扰。In combination with the first aspect, the embodiment of the present invention provides a fourth possible implementation manner of the first aspect, wherein, according to the average peak isolation and the peak isolation array, identifying whether the ECG signal exists Small interference, including: judging whether the average peak isolation is greater than a third threshold; if greater, then determining that the artifact type of the ECG signal amplitude sequence is small interference; if not greater, then judging the peak isolation Whether the number of elements in the array is greater than the fourth threshold; if so, it is judged that the artifact type of the ECG signal amplitude sequence is partial small-amplitude interference.
第二方面，本发明实施例还提供一种心电信号识别系统，包括：获取模块，用于获取一个采集周期采集的心电信号；计算模块，用于根据所述心电信号，计算心电信号的标准差、子段标准差数组，如果所述心电信号不存在大幅干扰，则根据所述标准差和子段标准差数组，计算心电信号的平均波峰孤立度和波峰孤立度数组；第一识别模块，用于根据所述标准差和所述子段标准差数组，识别所述心电信号是否存在大幅干扰；第二识别模块，用于根据所述平均波峰孤立度和所述波峰孤立度数组，识别所述心电信号是否存在小幅干扰。In the second aspect, the embodiment of the present invention also provides an ECG signal recognition system, including: an acquisition module, used to acquire an ECG signal collected in one collection period; a calculation module, used to calculate the ECG signal according to the ECG signal The standard deviation of the signal, the sub-section standard deviation array, if there is no significant interference in the electrocardiographic signal, then calculate the average peak isolation and the peak isolation array of the electrocardiographic signal according to the standard deviation and the sub-section standard deviation array; An identification module, used to identify whether there is a large amount of interference in the ECG signal according to the standard deviation and the sub-segment standard deviation array; a second identification module, used to identify the average peak isolation degree and the peak isolation The degree array is used to identify whether there is a small interference in the ECG signal.
结合第二方面，本发明实施例提供了第二方面的第一种可能的实施方式，其中，所述计算模块，用于：根据所述心电信号，计算心电信号的标准差，将所述心电信号按周期等分为多个心电波形片段，根据所述多个心电波形片段，获得每个心电波形片段的信号幅值，根据所述每个心电波形片段的信号幅值，计算每个心电波形片段的子段标准差，组成子段标准差数组。In combination with the second aspect, the embodiment of the present invention provides a first possible implementation manner of the second aspect, wherein the calculation module is configured to: calculate the standard deviation of the ECG signal according to the ECG signal, and calculate the The electrocardiographic signal is divided into a plurality of electrocardiographic waveform segments by cycle, and the signal amplitude of each electrocardiographic waveform segment is obtained according to the plurality of electrocardiographic waveform segments, and the signal amplitude of each electrocardiographic waveform segment is obtained according to the signal amplitude of each electrocardiographic waveform segment. value, calculate the sub-segment standard deviation of each ECG waveform segment, and form an array of sub-segment standard deviations.
结合第二方面，本发明实施例提供了第二方面的第二种可能的实施方式，其中，所述第一识别模块，用于：判断所述标准差是否大于第一阈值，如果大于，则判定所述心电信号幅值序列的伪差类型为大幅干扰，如果不大于，则判断所有子段标准差是否存在大于所述第一阈值的子段标准差，如果是，则获取存在大于所述第一阈值的子段标准差的个数，判断所述大于所述第一阈值的子段标准差的个数是否大于第二阈值，如果是，则判定所述心电信号幅值序列的伪差类型为部分大幅干扰。In combination with the second aspect, an embodiment of the present invention provides a second possible implementation manner of the second aspect, wherein the first identification module is configured to: determine whether the standard deviation is greater than a first threshold, and if greater, then Judging that the artifact type of the ECG signal amplitude sequence is large interference, if not greater than, then judging whether there is a subsection standard deviation greater than the first threshold in all subsection standard deviations, if yes, obtaining The number of the sub-section standard deviations of the first threshold value, judge whether the number of the sub-section standard deviations greater than the first threshold value is greater than the second threshold value, if yes, determine the number of the electrocardiographic signal amplitude value sequence The type of artifact is partially large interference.
结合第二方面，本发明实施例提供了第二方面的第三种可能的实施方式，其中，所述计算模块，用于：计算每个所述心电波形片段的信号幅值的欧式距离之和；从多个心电波形片段的信号幅值的欧式距离之和中选取最小值，并确定与所述最小值对应的基准信号幅值；从多个心电波形片段的信号幅值中，选取大于所述基准信号幅值的信号幅值；计算所有大于所述基准信号幅值的信号幅值的波峰孤立度；根据所述波峰孤立度，组建波峰孤立度数组；根据所述波峰孤立度数据数组，得到平均波峰孤立度。In combination with the second aspect, the embodiment of the present invention provides a third possible implementation manner of the second aspect, wherein the calculation module is configured to: calculate the Euclidean distance between the signal amplitudes of each of the ECG waveform segments and; choose the minimum value from the sum of the Euclidean distances of the signal amplitudes of multiple ECG waveform segments, and determine the reference signal amplitude corresponding to the minimum value; from the signal amplitudes of multiple ECG waveform segments, Selecting a signal amplitude greater than the reference signal amplitude; calculating the peak isolation of all signal amplitudes greater than the reference signal amplitude; according to the peak isolation, forming a peak isolation array; according to the peak isolation Data array, get the average peak isolation.
结合第二方面，本发明实施例提供了第二方面的第四种可能的实施方式，其中，所述第二识别模块，包括：判断所述平均波峰孤立度是否大于第三阈值；如果大于，则判定所述心电信号幅值序列的伪差类型为小幅干扰，如果不大于，再判断所述波峰孤立度数组中的元素个数是否大于第四阈值，如果是，则判定所述心电信号幅值序列的伪差类型为部分小幅干扰。In combination with the second aspect, an embodiment of the present invention provides a fourth possible implementation manner of the second aspect, wherein the second identification module includes: judging whether the average peak isolation is greater than a third threshold; if greater, Then it is determined that the artifact type of the ECG signal amplitude sequence is a small interference, if not greater than, then determine whether the number of elements in the peak isolation array is greater than the fourth threshold, if so, determine that the ECG The artifact type of the signal amplitude sequence is partial small-amplitude interference.
第三方面，本发明实施例还提供一种心电监测设备，包括处理器，与所述处理器连接的存储器；其中，所述存储器用于存储一条或多条计算机指令，所述处理器被配置成执行所述存储器中的计算机指令，以通过上述实施例中任一项所述的方法识别采集的心电信号是否存在干扰。In the third aspect, the embodiment of the present invention also provides an electrocardiogram monitoring device, including a processor and a memory connected to the processor; wherein, the memory is used to store one or more computer instructions, and the processor is controlled by It is configured to execute the computer instructions in the memory, so as to identify whether there is interference in the collected electrocardiographic signal through the method described in any one of the above embodiments.
本发明实施例带来了以下有益效果：可以通过心电信号的标准差、子段标准差数组判断采集到的心电信号是否存在大幅干扰，如果不存在，则再根据平均波峰孤立度和波峰孤立度数组，判断采集到的心电信号是否存在小幅干扰，本发明可以对心电信号进行更加细致的判断，从而可以为后期信号处理提供了精确的数据，同时本发明的判断建立在一个采集周期采集的心电信号，可以达到实时分析的需求，适用于实时心电监测。The embodiment of the present invention brings the following beneficial effects: it can be judged whether there is a large amount of interference in the collected ECG signal through the standard deviation of the ECG signal and the array of sub-segment standard deviations, if not, then according to the average peak isolation and the peak The isolation array is used to judge whether there is a small interference in the collected ECG signal. The present invention can make a more detailed judgment on the ECG signal, thereby providing accurate data for later signal processing. At the same time, the judgment of the present invention is based on a collection The periodically collected ECG signals can meet the requirements of real-time analysis and are suitable for real-time ECG monitoring.
本发明的其他特征和优点将在随后的说明书中阐述，并且，部分地从说明书中变得显而易见，或者通过实施本发明而了解。本发明的目的和其他优点在说明书、权利要求书以及附图中所特别指出的结构来实现和获得。Additional features and advantages of the invention will be set forth in the description which follows, and in part will be apparent from the description, or may be learned by practice of the invention. The objectives and other advantages of the invention will be realized and attained by the structure particularly pointed out in the written description and claims hereof as well as the appended drawings.
为使本发明的上述目的、特征和优点能更明显易懂，下文特举较佳实施例，并配合所附附图，作详细说明如下。In order to make the above-mentioned objects, features and advantages of the present invention more comprehensible, preferred embodiments will be described in detail below together with the accompanying drawings.
附图说明Description of drawings
为了更清楚地说明本发明具体实施方式或现有技术中的技术方案，下面将对具体实施方式或现有技术描述中所需要使用的附图作简单地介绍，显而易见地，下面描述中的附图是本发明的一些实施方式，对于本领域普通技术人员来讲，在不付出创造性劳动的前提下，还可以根据这些附图获得其他的附图。In order to more clearly illustrate the specific implementation of the present invention or the technical solutions in the prior art, the following will briefly introduce the accompanying drawings that need to be used in the specific implementation or description of the prior art. Obviously, the accompanying drawings in the following description The drawings show some implementations of the present invention, and those skilled in the art can obtain other drawings based on these drawings without any creative work.
图1为本发明实施例提供的心电信号识别方法的流程图；Fig. 1 is the flow chart of the ECG signal recognition method that the embodiment of the present invention provides;
图2为心电信号的示意图；Fig. 2 is the schematic diagram of electrocardiogram;
图3为一个周期内的心电信号的示意图；Fig. 3 is a schematic diagram of an electrocardiographic signal in one cycle;
图4为本发明实施例提供的判断大幅干扰的方法的流程图；FIG. 4 is a flowchart of a method for judging large interference provided by an embodiment of the present invention;
图5为本发明实施例提供的判断小幅干扰的方法的流程图；FIG. 5 is a flowchart of a method for judging small interference provided by an embodiment of the present invention;
图6为本发明实施例提供的心电信号识别系统的结构图；6 is a structural diagram of an ECG signal recognition system provided by an embodiment of the present invention;
图7为本发明实施例提供的心电监测设备的结构图。Fig. 7 is a structural diagram of an electrocardiogram monitoring device provided by an embodiment of the present invention.
图标：icon:
200-心电信号识别系统；210-获取模块；220-计算模块；230-第一识别模块；240-第二识别模块；300-心电监测设备；310-处理器；320-存储器；330-总线；340-通信接口。200-ECG signal identification system; 210-acquisition module; 220-calculation module; 230-first identification module; 240-second identification module; 300-ECG monitoring equipment; 310-processor; 320-memory; 330- bus; 340-communication interface.
具体实施方式Detailed ways
为使本发明实施例的目的、技术方案和优点更加清楚，下面将结合附图对本发明的技术方案进行清楚、完整地描述，显然，所描述的实施例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做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。In order to make the purpose, technical solutions and advantages of the embodiments of the present invention clearer, the technical solutions of the present invention will be clearly and completely described below in conjunction with the accompanying drawings. Obviously, the described embodiments are part of the embodiments of the present invention, not all of them. the embodiment. Based on the embodiments of the present invention, all other embodiments obtained by persons of ordinary skill in the art without making creative efforts belong to the protection scope of the present invention.
在心电监测中，得到的心电图可能会存在伪差，这是由于在做心电图的过程中存在干扰，例如肌肉颤动、仪器收到电磁干扰等情况，在存在干扰的情况下出现的误差为伪差。目前，实时分析的方法为用户采集信号的过程中每采集一小段信号分析一次，从而给用户一种即时分析的感觉。然而，现有的实时伪差识别方法，对于伪差的类别判断不全，判断粗略，在实时心电分析时的应用有限。若不依赖于识别算法，由人工识别伪差波形，则需要用户需要一定的心电专业知识，这也降低了应用的实用性。基于此，本发明实施例提供的一种心电信号识别方法、系统和心电监测设备，可以通过心电信号的标准差、子段标准差数组判断采集到的心电信号是否存在大幅干扰，如果不存在，则再根据平均波峰孤立度和波峰孤立度数组，判断采集到的心电信号是否存在小幅干扰，本发明可以对心电信号进行更加细致的判断，从而可以为后期信号处理提供精确的数据，同时本发明采用一次采集周期的心电信号进行伪差的判断，可以更接近实时的完成心电伪差判断，延迟的时间为进行分析的周期，而周期的设定是任意的，当周期较短时，就可以达到近乎实时的效果。进一步说，本发明不需要对大量的数据进行复杂的统计分析，每次仅需对一个短周期的心电信号幅值序列进行统计分析，运行速度快，可以满足实时分析的需求，而不是经过一段时间才能达到较好的效果。In ECG monitoring, there may be artifacts in the obtained ECG. This is because there is interference in the process of doing ECG, such as muscle tremors, electromagnetic interference received by the instrument, etc. The error that occurs in the presence of interference is artifacts. . At present, the method of real-time analysis is to analyze each small segment of signal collected by the user during the signal collection process, so as to give the user a sense of instant analysis. However, the existing real-time artifact recognition methods are incomplete and rough in judging the types of artifacts, and their application in real-time ECG analysis is limited. If the artifact waveform is manually identified without relying on the identification algorithm, the user needs certain ECG expertise, which also reduces the practicability of the application. Based on this, an ECG signal recognition method, system and ECG monitoring device provided in the embodiments of the present invention can judge whether there is a large amount of interference in the collected ECG signal through the standard deviation of the ECG signal and the array of sub-segment standard deviations, If it does not exist, then according to the average peak isolation and the array of peak isolation, it is judged whether there is a small interference in the collected ECG signal. At the same time, the present invention uses the electrocardiographic signal of one acquisition cycle to judge the artifact, which can be closer to real-time completion of the electrocardiographic artifact judgment. The delayed time is the cycle of analysis, and the setting of the cycle is arbitrary. When the period is short, near real-time effects can be achieved. Furthermore, the present invention does not need to perform complex statistical analysis on a large amount of data, and only needs to perform statistical analysis on a short-period ECG signal amplitude sequence at a time. It takes a while to achieve better results.
为便于对本实施例进行理解，首先对本发明实施例所公开的一种心电信号识别方法进行详细介绍，参见图1所示，包括：In order to facilitate the understanding of this embodiment, a method for identifying an ECG signal disclosed in an embodiment of the present invention is firstly introduced in detail, as shown in FIG. 1 , including:
S110：获取一个采集周期采集的心电信号。S110: Obtain ECG signals collected in one collection period.
结合图2所示，为获取的心电信号。用户可以使用动态心电监测设备进行心电采集，并获取一次采集周期采集的心电信号，其中，采集到的心电信号实际上是信号幅值序列，以横坐标为时间、纵坐标为电压的心电图曲线记录的。Combined with Figure 2, it is the acquired ECG signal. Users can use dynamic ECG monitoring equipment to collect ECG and obtain ECG signals collected in one acquisition cycle. The collected ECG signals are actually a sequence of signal amplitudes, with time on the abscissa and voltage on the ordinate ECG curve records.
S120：根据心电信号，计算心电信号的标准差、子段标准差数组。S120: Calculate the standard deviation of the ECG signal and an array of sub-segment standard deviations according to the ECG signal.
作为一个示例，步骤S120包括：根据心电信号，计算心电信号的标准差；将心电信号按周期等分为多个心电波形片段；根据多个心电波形片段，获得每个心电波形片段的信号幅值；根据每个心电波形片段的信号幅值，计算每个心电波形片段的子段标准差，组成子段标准差数组。As an example, step S120 includes: calculating the standard deviation of the ECG signal according to the ECG signal; dividing the ECG signal into multiple ECG waveform segments by cycle; The signal amplitude of the waveform segment; according to the signal amplitude of each ECG waveform segment, the sub-segment standard deviation of each ECG waveform segment is calculated to form an array of sub-segment standard deviations.
其中，将心电信号按周期等分为多个心电波形片段中的按周期的意思是按照一次跳动计为一个周期，结合图3所示，一个跳动的时间包括P-R间期、Q-T间期和U波的时间。一次周期采集的心电信号包括多个一次跳动，将这些一次跳动分割出来分成心电波形片段。Among them, dividing the ECG signal into multiple ECG waveform segments by cycle means that one beat is counted as one cycle. As shown in Figure 3, the time of one beat includes the P-R interval and the Q-T interval. and U wave time. The electrocardiographic signal collected in one cycle includes multiple one-time beats, and these one-time beats are divided into electrocardiographic waveform segments.
在一些实施例中，在步骤S120之前，还可以包括：对获取到的心电信号进行数据预处理，以过滤基线漂移干扰和高频噪声，得到预处理后的心电波形数据。In some embodiments, before step S120, it may further include: performing data preprocessing on the acquired ECG signal to filter baseline drift interference and high-frequency noise to obtain preprocessed ECG waveform data.
S130：根据标准差和子段标准差数组，识别心电信号是否存在大幅干扰。S130: According to the standard deviation and the array of sub-segment standard deviations, identify whether there is significant interference in the ECG signal.
在一些实施例中，结合图4所示，步骤S130具体包括：In some embodiments, as shown in FIG. 4 , step S130 specifically includes:
S131：判断标准差是否大于第一阈值。S131: Determine whether the standard deviation is greater than a first threshold.
其中，第一阈值通过多次已知的数据进行测试得到。即，第一阈值是当计算出来的标准差大于这个临界阈值时，可以知道采集到的心电信号幅值序列收到了大幅干扰。如果大于，则进行步骤S132；如果不大于，则进行步骤S133。Wherein, the first threshold is obtained by performing tests on known data multiple times. That is, the first threshold is that when the calculated standard deviation is greater than the critical threshold, it can be known that the collected ECG signal amplitude sequence has received significant interference. If it is greater, go to step S132; if not, go to step S133.
S132：判定心电信号幅值序列的伪差类型为大幅干扰。S132: Determine that the type of artifact of the ECG signal amplitude sequence is large interference.
其中，大幅干扰的意思为心电波形的周期性很混乱，分不清楚心电波形的P波、QRS波、T波、U波。举例来说，结合图3所示，为没有干扰下的心电波形图，在这个心电波形图中，P波、T波、U波的幅值明显小于R波的幅值，而在判断采集的心电信号幅值序列的伪差类型为大幅干扰时，所呈现出来的心电图分不清楚心电波形的P波、QRS波、T波、U波，采集到的各个幅值变化混乱。Among them, a large amount of interference means that the periodicity of the ECG waveform is very chaotic, and the P wave, QRS wave, T wave, and U wave of the ECG waveform cannot be clearly distinguished. For example, as shown in Figure 3, it is an electrocardiographic waveform without interference. In this electrocardiographic waveform, the amplitudes of P waves, T waves, and U waves are significantly smaller than the amplitudes of R waves. When the artifact type of the collected ECG signal amplitude sequence is large interference, the presented ECG cannot clearly distinguish the P wave, QRS wave, T wave, and U wave of the ECG waveform, and the amplitude changes of each collected are chaotic.
S133：判断子段标准差是否存在大于第一阈值的子段标准差。如果存在，则进行步骤S134和步骤S135。S133: Determine whether the sub-segment standard deviation has a sub-segment standard deviation greater than the first threshold. If yes, proceed to step S134 and step S135.
其中，步骤S135：判断大于第一阈值的子段标准差的个数是否大于第二阈值中的第二阈值为自然数，第二阈值是指大于第一阈值的子段标准差的个数与这个临界值进行比较，判断是否部分大幅干扰。其中，这个第二阈值根据一个周期内采集的心电信号而定。举例来说，当一个采集周期内采集到20个一次跳动的心电波形片段，当20个心电波形片段中有10个心电波形片段的标准差大于第一阈值，也就是，10个心电波形片段的伪差类型为大幅干扰，这个10就是第二阈值。当然第二阈值的值可以根据一个采集周期内采集到的心电波形片段的个数而定。如果大于，则进行步骤S136，如果不大于，则进行步骤S140。Wherein, step S135: judging whether the number of subsection standard deviations greater than the first threshold is greater than the second threshold in the second threshold is a natural number, and the second threshold refers to the number of subsection standard deviations greater than the first threshold and this The critical value is compared to determine whether the part interferes substantially. Wherein, the second threshold is determined according to the ECG signals collected in one cycle. For example, when 20 one-beat ECG waveform segments are collected in one acquisition cycle, when the standard deviation of 10 ECG waveform segments among the 20 ECG waveform segments is greater than the first threshold, that is, 10 ECG waveform segments The artifact type of the electrical waveform segment is large interference, and this 10 is the second threshold. Of course, the value of the second threshold may be determined according to the number of ECG waveform segments collected in one collection period. If it is greater, proceed to step S136, and if not, proceed to step S140.
S136：判定心电信号幅值序列的伪差类型为部分大幅干扰。S136: Determine that the artifact type of the ECG signal amplitude sequence is partial large interference.
其中，部分大幅干扰的意思是在一次采集周期内的具有部分心电波形片段的心电波形的周期性很混乱，分不清楚心电波形的P波、QRS波、T波、U波。Among them, part of the large interference means that the periodicity of the ECG waveform with some ECG waveform segments in one acquisition cycle is very chaotic, and the P wave, QRS wave, T wave, and U wave of the ECG waveform cannot be clearly distinguished.
在一些实施例中，在步骤S130之前还包括：组建多个心电波形片段的信号幅值的数组，判断数组的长度为0时，判定当前获取的心电信号为无信号状态。即，没有采集到信号。In some embodiments, before step S130, it further includes: constructing an array of signal amplitudes of multiple ECG waveform segments, and judging that the currently acquired ECG signal is in a no-signal state when the length of the array is determined to be 0. That is, no signal is acquired.
S140：如果心电信号不存在大幅干扰，则根据标准差和子段标准差数组，计算心电信号的平均波峰孤立度和波峰孤立度数组。S140: If there is no significant interference in the electrocardiographic signal, calculate the average peak isolation and the array of peak isolation of the electrocardiographic signal according to the standard deviation and the array of sub-segment standard deviations.
在一些实施例中，根据标准差和子段标准差数组，计算心电信号的平均波峰孤立度和波峰孤立度数组，包括：计算每个心电波形片段的信号幅值的欧式距离之和；从多个心电波形片段的信号幅值的欧式距离之和中选取最小值，并确定与最小值对应的基准信号幅值；从多个心电波形片段的信号幅值中，选取大于基准信号幅值的信号幅值；计算所有大于基准信号幅值的信号幅值的波峰孤立度；根据波峰孤立度，组建波峰孤立度数组；根据波峰孤立度数组，得到平均波峰孤立度。In some embodiments, according to the standard deviation and the sub-segment standard deviation array, calculating the average peak isolation and the peak isolation array of the ECG signal includes: calculating the sum of the Euclidean distances of the signal amplitudes of each ECG waveform segment; Select the minimum value from the sum of the Euclidean distances of the signal amplitudes of multiple ECG waveform segments, and determine the reference signal amplitude corresponding to the minimum value; from the signal amplitudes of multiple ECG waveform segments, select value of the signal amplitude; calculate the peak isolation of all signal amplitudes greater than the reference signal amplitude; according to the peak isolation, set up the peak isolation array; according to the peak isolation array, get the average peak isolation.
举例来说，当获取的一次采集周期的心电波形片段为20个时，存在20个信号幅值，计算每一个信号幅值与其他信号幅值之间的欧式距离，得到欧式距离后，计算一个信号幅值的欧式距离之和，即20个心电波形片段对应20个欧氏距离之和，比较20个欧式距离之和的大小，选取20个欧式距离之和中的最小值，确定与最小值对应的信号幅值为基准信号幅值。For example, when there are 20 ECG waveform segments acquired in one acquisition cycle, there are 20 signal amplitudes, and the Euclidean distance between each signal amplitude and other signal amplitudes is calculated. After obtaining the Euclidean distance, calculate The sum of the Euclidean distances of a signal amplitude, that is, the sum of 20 Euclidean distances corresponding to 20 ECG waveform segments, compare the sum of the 20 Euclidean distances, select the minimum value among the 20 Euclidean distances, and determine the The signal amplitude corresponding to the minimum value is the reference signal amplitude.
其中，这个基准信号幅值的作用为：心电主波，即R波的幅值的阈值。再得到阈值后，将这个阈值与20个心电波形片段的信号幅值进行比较，选取大于这个阈值的信号幅值，并确定这个信号幅值在这个获取的心电信号中的位置。特别的，因为心电信号以横坐标为时间、纵坐标为电压的形式记录的，则具体的位置信息可以用时间来表示。Wherein, the function of the reference signal amplitude is: the main ECG wave, that is, the threshold of the amplitude of the R wave. After the threshold is obtained, compare the threshold with the signal amplitudes of 20 ECG waveform segments, select the signal amplitude greater than the threshold, and determine the position of the signal amplitude in the acquired ECG signal. In particular, since the electrocardiographic signal is recorded in the form of time on the abscissa and voltage on the ordinate, specific location information can be represented by time.
当得到这些位置信息后，计算该信号幅值的波峰孤立度。波峰孤立度是指一个波峰在以其自身为中心的一定范围内的满足条件的波峰个数。举例，结合图2所示，如果第三个信号幅值为待计算波峰孤立度的信号幅值，则以第三个信号幅值的位置为中心，在向左一定范围内和向右同等的范围内中找满足条件的波峰个数。这里所说的满足条件的波峰是指，该波峰值的大小为待计算波峰孤立度的信号幅值的一定比例，这个一定比例的范围为[0.5,0.9]。特别的，如果在以待计算波峰孤立度的信号幅值的位置为中心的一定范围内存在波峰值的大小大于待计算波峰孤立度的信号幅值，则待计算波峰孤立度的信号幅值的波峰孤立度为0。After obtaining these position information, calculate the peak isolation of the signal amplitude. Peak isolation refers to the number of peaks that meet the conditions within a certain range centered on itself. For example, as shown in Figure 2, if the third signal amplitude is the signal amplitude of the peak isolation to be calculated, then the position of the third signal amplitude is the center, within a certain range to the left and to the right Find the number of peaks that meet the conditions within the range. The peak satisfying the conditions mentioned here means that the magnitude of the peak is a certain proportion of the signal amplitude to be calculated for the peak isolation, and the range of this certain proportion is [0.5,0.9]. In particular, if within a certain range centered on the position of the signal amplitude of the peak isolation to be calculated, the magnitude of the peak value is greater than the signal amplitude of the peak isolation to be calculated, then the signal amplitude of the peak isolation to be calculated The peak isolation is 0.
其中，平均波峰孤立度为波峰孤立度数组的算术平均值。Among them, the average peak isolation is the arithmetic mean of the array of peak isolation.
S150：根据平均波峰孤立度和波峰孤立度数组，识别心电信号是否存在小幅干扰。S150: According to the average peak isolation and the array of peak isolation, identify whether there is a small disturbance in the electrocardiographic signal.
结合图5所示，根据平均波峰孤立度和波峰孤立度数组，识别心电信号是否存在小幅干扰，包括：Combined with Figure 5, according to the average peak isolation and the array of peak isolation, identify whether there is small interference in the ECG signal, including:
S151：判断平均波峰孤立度是否大于第三阈值。S151: Determine whether the average peak isolation is greater than a third threshold.
具体来说，第三阈值是根据已知的正常的心电数据和具有小幅干扰情况的心电数据，判定两种数据的临界值。如果大于，则进行步骤S152；如果不大于，则进行步骤S153。Specifically, the third threshold is based on the known normal ECG data and the ECG data with a small disturbance, and determines the critical value of the two data. If it is greater, proceed to step S152; if not, proceed to step S153.
S152：判定心电信号幅值序列的伪差类型为小幅干扰。S152: Determine that the type of artifact of the ECG signal amplitude sequence is small amplitude interference.
其中，结合图2和图3所示，在没有干扰的心电信号幅值大小中，P波、T波、U波的幅值明显小于R波的幅值，小幅干扰是指P波、T波、U波其中的至少一个信号幅值与R波的幅值大小相当，或者为R波的幅值大小的一定比例，其中，一定比例的范围可以为[0.5，0.9]，我们将这种干扰定义为小幅干扰。小幅干扰可以确定P波、R波、T波、U波，但是P波、T波、U波与R波之间的幅值对比不明显。Among them, as shown in Figure 2 and Figure 3, in the magnitude of the ECG signal amplitude without interference, the amplitudes of P wave, T wave, and U wave are significantly smaller than the amplitude of R wave, and small interference refers to the amplitude of P wave, T wave, and T wave. The signal amplitude of at least one of the wave and U wave is equivalent to the amplitude of the R wave, or is a certain proportion of the amplitude of the R wave. Among them, the range of a certain proportion can be [0.5, 0.9]. We will use this Disturbances are defined as small disturbances. Small interference can determine P wave, R wave, T wave, U wave, but the amplitude contrast between P wave, T wave, U wave and R wave is not obvious.
S153：判断波峰孤立度数组中的元素个数是否大于第四阈值。如果大于，则进行步骤S154；如果不大于，则进行步骤S155。S153: Determine whether the number of elements in the peak isolation array is greater than the fourth threshold. If greater, proceed to step S154; if not greater, proceed to step S155.
S154：判定心电信号幅值序列的伪差类型为部分小幅干扰。S154: Determine that the artifact type of the ECG signal amplitude sequence is partial small-amplitude interference.
部分小幅干扰的意思是在一次采集周期内的具有部分心电波形片段的具有上述所说的小幅干扰的情况。Partial small-amplitude interference refers to the above-mentioned small-amplitude interference with part of ECG waveform segments within one acquisition period.
S155：判定该信号没有收到干扰。S155: Determine that the signal does not receive interference.
结合图6所示，心电信号识别系统200，包括：获取模块210、计算模块220、第一识别模块230和第二识别模块240。As shown in FIG. 6 , the ECG signal recognition system 200 includes: an acquisition module 210 , a calculation module 220 , a first recognition module 230 and a second recognition module 240 .
其中，获取模块210用于获取一个采集周期采集的心电信号。计算模块220与获取模块210相连，用于根据心电信号，计算心电信号的标准差、子段标准差数组，如果心电信号不存在严重干扰现象，则根据标准差和子段标准差数组，计算心电信号的平均波峰孤立度和波峰孤立度数组。第一识别模块230与计算模块220相连，用于根据标准差和子段标准差数组，识别心电信号是否存在大幅干扰。第二识别模块240与计算模块220，用于根据平均波峰孤立度和所述波峰孤立度数组，识别心电信号是否存在小幅干扰。Wherein, the obtaining module 210 is used to obtain the electrocardiographic signal collected in one collection period. The calculation module 220 is connected with the acquisition module 210, and is used to calculate the standard deviation of the ECG signal and the sub-section standard deviation array according to the ECG signal. If there is no serious interference phenomenon in the ECG signal, then according to the standard deviation and the sub-section standard deviation array, Calculate the average peak isolation and the array of peak isolation of the ECG signal. The first identification module 230 is connected with the calculation module 220, and is used to identify whether there is a large amount of interference in the ECG signal according to the standard deviation and the array of sub-segment standard deviations. The second identification module 240 and the calculation module 220 are configured to identify whether there is small interference in the ECG signal according to the average peak isolation and the array of peak isolation.
在一些实施例中，计算模块220用于：根据心电信号，计算心电信号的标准差，将心电信号按周期等分为多个心电波形片段，根据多个心电波形片段，获得每个心电波形片段的信号幅值，根据每个心电波形片段的信号幅值，计算每个心电波形片段的子段标准差，组成子段标准差数组。In some embodiments, the calculation module 220 is configured to: calculate the standard deviation of the ECG signal according to the ECG signal, divide the ECG signal into a plurality of ECG waveform segments equally by cycle, and obtain According to the signal amplitude of each ECG waveform segment, the sub-segment standard deviation of each ECG waveform segment is calculated to form an array of sub-segment standard deviations.
在一些实施例中，第一识别模块230，用于：判断标准差是否大于第一阈值，如果大于，则判断心电信号幅值序列的伪差类型为大幅干扰，如果不大于，则判断所有子段标准差是否存在大于第一阈值的子段标准差，如果存在，则获取存在大于第一阈值的子段标准差的个数，判断大于第一阈值的子段标准差的个数是否大于第二阈值，如果大于，则判断心电信号幅值序列的伪差类型为部分大幅干扰。In some embodiments, the first identification module 230 is used to: determine whether the standard deviation is greater than the first threshold, if greater, then determine that the artifact type of the ECG signal amplitude sequence is large interference, and if not greater, then determine all Whether the sub-section standard deviation has a sub-section standard deviation greater than the first threshold, if it exists, obtain the number of sub-section standard deviations greater than the first threshold, and determine whether the number of sub-section standard deviations greater than the first threshold is greater than If the second threshold is greater than, it is judged that the artifact type of the ECG signal amplitude sequence is partial large-scale interference.
在一些实施例中，计算模块220，用于：计算每个心电波形片段的信号幅值的欧式距离之和；从多个心电波形片段的信号幅值的欧式距离之和中选取最小值，并确定与最小值对应的基准信号幅值；从多个心电波形片段的信号幅值中，选取大于基准信号幅值的信号幅值；计算所有大于基准信号幅值的信号幅值的波峰孤立度；根据波峰孤立度，组建波峰孤立度数组；根据波峰孤立度数据数组，得到平均波峰孤立度。In some embodiments, the calculation module 220 is configured to: calculate the sum of the Euclidean distances of the signal amplitudes of each ECG waveform segment; select the minimum value from the sum of the Euclidean distances of the signal amplitudes of multiple ECG waveform segments , and determine the reference signal amplitude corresponding to the minimum value; from the signal amplitudes of multiple ECG waveform segments, select the signal amplitude greater than the reference signal amplitude; calculate the peaks of all signal amplitudes greater than the reference signal amplitude Isolation; according to the peak isolation, an array of peak isolation is established; according to the peak isolation data array, the average peak isolation is obtained.
在一些实施例中，第二识别模块240，包括：判断平均波峰孤立度是否大于第三阈值；如果大于，则判断心电信号幅值序列的伪差类型为幅值过小，如果不大于，再判断波峰孤立度数组中的元素个数是否大于第四阈值，如果大于，则判断心电信号幅值序列的伪差类型为少量扰动。In some embodiments, the second identification module 240 includes: judging whether the average peak isolation is greater than the third threshold; if it is greater, then judging that the artifact type of the amplitude sequence of the ECG signal is too small in amplitude, if not greater, It is then judged whether the number of elements in the wave peak isolation array is greater than the fourth threshold, and if so, it is judged that the artifact type of the ECG signal amplitude sequence is a small amount of disturbance.
本发明实施例所提供的系统，其实现原理及产生的技术效果和前述方法实施例相同，为简要描述，系统实施例部分未提及之处，可参考前述方法实施例中相应内容。The implementation principles and technical effects of the system provided by the embodiments of the present invention are the same as those of the foregoing method embodiments. For brief description, for the parts not mentioned in the system embodiments, reference may be made to the corresponding content in the foregoing method embodiments.
参见图7所示，心电监测设备300，其特征在于，包括处理器310，与处理器310连接的存储器320；其中，存储器320用于存储一条或多条计算机指令，处理器310被配置成执行存储器320中的计算机指令，以通过上述实施例任一项所述的方法识别采集的心电信号是否存在干扰。Referring to Fig. 7, the ECG monitoring device 300 is characterized in that it includes a processor 310 and a memory 320 connected to the processor 310; wherein the memory 320 is used to store one or more computer instructions, and the processor 310 is configured to Execute the computer instructions in the memory 320 to identify whether there is interference in the collected electrocardiographic signal through the method described in any one of the above embodiments.
再参见图7，还包括：总线330和通信接口340，所述处理器310、通信接口340和存储器320通过总线330连接。Referring to FIG. 7 again, it further includes: a bus 330 and a communication interface 340 , the processor 310 , the communication interface 340 and the memory 320 are connected through the bus 330 .
其中，存储器320可能包含高速随机存取存储器(RAM，Random Access Memory)，也可能还包括非不稳定的存储器(non-volatile memory)，例如至少一个磁盘存储器。通过至少一个通信接口340(可以是有线或者无线)实现该系统网元与至少一个其他网元之间的通信连接，可以使用互联网，广域网，本地网，城域网等。Wherein, the memory 320 may include a high-speed random access memory (RAM, Random Access Memory), and may also include a non-volatile memory (non-volatile memory), such as at least one disk memory. The communication connection between the system network element and at least one other network element is realized through at least one communication interface 340 (which may be wired or wireless), and the Internet, wide area network, local network, metropolitan area network, etc. can be used.
总线330可以是ISA总线、PCI总线或EISA总线等。所述总线可以分为地址总线、数据总线、控制总线等。为便于表示，图7中仅用一个双向箭头表示，但并不表示仅有一根总线或一种类型的总线。The bus 330 may be an ISA bus, a PCI bus, or an EISA bus, etc. The bus can be divided into address bus, data bus, control bus and so on. For ease of representation, only one double-headed arrow is used in FIG. 7 , but it does not mean that there is only one bus or one type of bus.
其中，存储器320用于存储程序，所述处理器310在接收到执行指令后，执行所述程序401，前述本发明实施例任一实施例揭示的流过程定义的装置所执行的方法可以应用于处理器310中，或者由处理器310实现。Wherein, the memory 320 is used to store the program, and the processor 310 executes the program 401 after receiving the execution instruction, and the method performed by the device for stream process definition disclosed in any embodiment of the foregoing embodiments of the present invention can be applied to In the processor 310, or implemented by the processor 310.
处理器310可能是一种集成电路芯片，具有信号的处理能力。在实现过程中，上述方法的各步骤可以通过处理器310中的硬件的集成逻辑电路或者软件形式的指令完成。上述的处理器310可以是通用处理器，包括中央处理器(Central Processing Unit，简称CPU)、网络处理器(Network Processor，简称NP)等；还可以是数字信号处理器(DigitalSignal Processing，简称DSP)、专用集成电路(Application Specific IntegratedCircuit，简称ASIC)、现成可编程门阵列(Field-Programmable Gate Array，简称FPGA)或者其他可编程逻辑器件、分立门或者晶体管逻辑器件、分立硬件组件。可以实现或者执行本发明实施例中的公开的各方法、步骤及逻辑框图。通用处理器可以是微处理器或者该处理器也可以是任何常规的处理器等。结合本发明实施例所公开的方法的步骤可以直接体现为硬件译码处理器执行完成，或者用译码处理器中的硬件及软件模块组合执行完成。软件模块可以位于随机存储器，闪存、只读存储器，可编程只读存储器或者电可擦写可编程存储器、寄存器等本领域成熟的存储介质中。该存储介质位于存储器320，处理器310读取存储器320中的信息，结合其硬件完成上述方法的步骤。The processor 310 may be an integrated circuit chip and has a signal processing capability. In the implementation process, each step of the above method may be implemented by an integrated logic circuit of hardware in the processor 310 or instructions in the form of software. The above-mentioned processor 310 can be a general-purpose processor, including a central processing unit (Central Processing Unit, referred to as CPU), a network processor (Network Processor, referred to as NP), etc.; it can also be a digital signal processor (Digital Signal Processing, referred to as DSP) , Application Specific Integrated Circuit (ASIC for short), off-the-shelf programmable gate array (Field-Programmable Gate Array, FPGA for short) or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components. Various methods, steps and logic block diagrams disclosed in the embodiments of the present invention may be implemented or executed. A general-purpose processor may be a microprocessor, or the processor may be any conventional processor, or the like. The steps of the methods disclosed in the embodiments of the present invention may be directly implemented by a hardware decoding processor, or implemented by a combination of hardware and software modules in the decoding processor. The software module can be located in a mature storage medium in the field such as random access memory, flash memory, read-only memory, programmable read-only memory or electrically erasable programmable memory, register. The storage medium is located in the memory 320, and the processor 310 reads the information in the memory 320, and completes the steps of the above method in combination with its hardware.
除非另外具体说明，否则在这些实施例中阐述的部件和步骤的相对步骤、数字表达式和数值并不限制本发明的范围。Relative steps, numerical expressions and numerical values of components and steps set forth in these embodiments do not limit the scope of the present invention unless specifically stated otherwise.
在这里示出和描述的所有示例中，任何具体值应被解释为仅仅是示例性的，而不是作为限制，因此，示例性实施例的其他示例可以具有不同的值。In all examples shown and described herein, any specific values should be construed as merely exemplary and not limiting, and thus other examples of the exemplary embodiments may have different values.
应注意到：相似的标号和字母在下面的附图中表示类似项，因此，一旦某一项在一个附图中被定义，则在随后的附图中不需要对其进行进一步定义和解释。It should be noted that like numerals and letters denote similar items in the following figures, therefore, once an item is defined in one figure, it does not require further definition and explanation in subsequent figures.
附图中的流程图和框图显示了根据本发明的多个实施例的系统、方法和计算机程序产品的可能实现的体系架构、功能和操作。在这点上，流程图或框图中的每个方框可以代表一个模块、程序段或代码的一部分，所述模块、程序段或代码的一部分包含一个或多个用于实现规定的逻辑功能的可执行指令。也应当注意，在有些作为替换的实现中，方框中所标注的功能也可以以不同于附图中所标注的顺序发生。例如，两个连续的方框实际上可以基本并行地执行，它们有时也可以按相反的顺序执行，这依所涉及的功能而定。也要注意的是，框图和/或流程图中的每个方框、以及框图和/或流程图中的方框的组合，可以用执行规定的功能或动作的专用的基于硬件的系统来实现，或者可以用专用硬件与计算机指令的组合来实现。The flowchart and block diagrams in the figures illustrate the architecture, functionality, and operation of possible implementations of systems, methods and computer program products according to various embodiments of the present invention. In this regard, each block in a flowchart or block diagram may represent a module, program segment, or part of code that includes one or more Executable instructions. It should also be noted that, in some alternative implementations, the functions noted in the block may occur out of the order noted in the figures. For example, two blocks in succession may, in fact, be executed substantially concurrently, or they may sometimes be executed in the reverse order, depending upon the functionality involved. It should also be noted that each block of the block diagrams and/or flowchart illustrations, and combinations of blocks in the block diagrams and/or flowchart illustrations, can be implemented by a dedicated hardware-based system that performs the specified function or action , or may be implemented by a combination of dedicated hardware and computer instructions.
另外，在本发明实施例的描述中，除非另有明确的规定和限定，术语“相连”应做广义理解，例如，可以是固定连接，也可以是可拆卸连接，或一体地连接；可以是机械连接，也可以是电连接；可以是直接相连，也可以通过中间媒介间接相连，可以是两个元件内部的连通。对于本领域的普通技术人员而言，可以具体情况理解上述术语在本发明中的具体含义。In addition, in the description of the embodiments of the present invention, unless otherwise clearly stipulated and limited, the term "connected" should be understood in a broad sense, for example, it can be a fixed connection, a detachable connection, or an integral connection; it can be A mechanical connection can also be an electrical connection; it can be a direct connection or an indirect connection through an intermediary, and it can be the internal communication of two components. Those of ordinary skill in the art can understand the specific meanings of the above terms in the present invention in specific situations.
在本发明的描述中，需要说明的是，术语“中心”、“上”、“下”、“左”、“右”、“内”等指示的方位或位置关系为基于附图所示的方位或位置关系，仅是为了便于描述本发明和简化描述，而不是指示或暗示所指的装置或元件必须具有特定的方位、以特定的方位构造和操作，因此不能理解为对本发明的限制。此外，术语“第一”、“第二”、“第三”仅用于描述目的，而不能理解为指示或暗示相对重要性。In the description of the present invention, it should be noted that the orientation or positional relationship indicated by the terms "center", "upper", "lower", "left", "right", "inside" etc. are based on the Orientation or positional relationship is only for the convenience of describing the present invention and simplifying the description, and does not indicate or imply that the referred device or element must have a specific orientation, be constructed and operated in a specific orientation, and thus should not be construed as a limitation of the present invention. In addition, the terms "first", "second", and "third" are used for descriptive purposes only, and should not be construed as indicating or implying relative importance.
在本申请所提供的几个实施例中，应该理解到，所揭露的系统和方法，可以通过其它的方式实现。以上所描述的系统实施例仅仅是示意性的，例如，所述单元的划分，仅仅为一种逻辑功能划分，实际实现时可以有另外的划分方式，又例如，多个单元或组件可以结合或者可以集成到另一个系统，或一些特征可以忽略，或不执行。另一点，所显示或讨论的相互之间的耦合或直接耦合或通信连接可以是通过一些通信接口，单元的间接耦合或通信连接，可以是电性，机械或其它的形式。In the several embodiments provided in this application, it should be understood that the disclosed system and method can be implemented in other ways. The system embodiments described above are only illustrative. For example, the division of the units is only a logical function division. In actual implementation, there may be other division methods. For example, multiple units or components can be combined or May be integrated into another system, or some features may be ignored, or not implemented. In another point, the mutual coupling or direct coupling or communication connection shown or discussed may be through some communication interfaces, and the indirect coupling or communication connection of units may be in electrical, mechanical or other forms.
所述作为分离部件说明的单元可以是或者也可以不是物理上分开的，作为单元显示的部件可以是或者也可以不是物理单元，即可以位于一个地方，或者也可以分布到多个网络单元上。可以根据实际的需要选择其中的部分或者全部单元来实现本实施例方案的目的。The units described as separate components may or may not be physically separated, and the components shown as units may or may not be physical units, that is, they may be located in one place, or may be distributed to multiple network units. Part or all of the units can be selected according to actual needs to achieve the purpose of the solution of this embodiment.
另外，在本发明各个实施例中的各功能单元可以集成在一个处理单元中，也可以是各个单元单独物理存在，也可以两个或两个以上单元集成在一个单元中。In addition, each functional unit in each embodiment of the present invention may be integrated into one processing unit, each unit may exist separately physically, or two or more units may be integrated into one unit.
所述功能如果以软件功能单元的形式实现并作为独立的产品销售或使用时，可以存储在一个处理器可执行的非易失的计算机可读取存储介质中。基于这样的理解，本发明的技术方案本质上或者说对现有技术做出贡献的部分或者该技术方案的部分可以以软件产品的形式体现出来，该计算机软件产品存储在一个存储介质中，包括若干指令用以使得一台计算机设备(可以是个人计算机，服务器，或者网络设备等)执行本发明各个实施例所述方法的全部或部分步骤。而前述的存储介质包括：U盘、移动硬盘、只读存储器(ROM，Read-Only Memory)、随机存取存储器(RAM，Random Access Memory)、磁碟或者光盘等各种可以存储程序代码的介质。If the functions are realized in the form of software function units and sold or used as independent products, they can be stored in a non-volatile computer-readable storage medium executable by a processor. Based on this understanding, the essence of the technical solution of the present invention or the part that contributes to the prior art or the part of the technical solution can be embodied in the form of a software product, and the computer software product is stored in a storage medium, including Several instructions are used to make a computer device (which may be a personal computer, a server, or a network device, etc.) execute all or part of the steps of the methods described in various embodiments of the present invention. The aforementioned storage medium includes: U disk, mobile hard disk, read-only memory (ROM, Read-Only Memory), random access memory (RAM, Random Access Memory), magnetic disk or optical disk and other media that can store program codes. .
最后应说明的是：以上所述实施例，仅为本发明的具体实施方式，用以说明本发明的技术方案，而非对其限制，本发明的保护范围并不局限于此，尽管参照前述实施例对本发明进行了详细的说明，本领域的普通技术人员应当理解：任何熟悉本技术领域的技术人员在本发明揭露的技术范围内，其依然可以对前述实施例所记载的技术方案进行修改或可轻易想到变化，或者对其中部分技术特征进行等同替换；而这些修改、变化或者替换，并不使相应技术方案的本质脱离本发明实施例技术方案的精神和范围，都应涵盖在本发明的保护范围之内。因此，本发明的保护范围应所述以权利要求的保护范围为准。Finally, it should be noted that: the above-described embodiments are only specific implementations of the present invention, used to illustrate the technical solutions of the present invention, rather than limiting them, and the scope of protection of the present invention is not limited thereto, although referring to the foregoing The embodiment has described the present invention in detail, and those skilled in the art should understand that any person familiar with the technical field can still modify the technical solutions described in the foregoing embodiments within the technical scope disclosed in the present invention Changes can be easily thought of, or equivalent replacements are made to some of the technical features; and these modifications, changes or replacements do not make the essence of the corresponding technical solutions deviate from the spirit and scope of the technical solutions of the embodiments of the present invention, and should be included in the scope of the present invention within the scope of protection. Therefore, the protection scope of the present invention should be based on the protection scope of the claims.
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| CN201711429249.4ACN108324271B (en) | 2017-12-25 | 2017-12-25 | ECG signal identification method, system and ECG monitoring equipment |
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| CN201711429249.4ACN108324271B (en) | 2017-12-25 | 2017-12-25 | ECG signal identification method, system and ECG monitoring equipment |
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