# K-Means Algorithm to Identify the Elderly Psychological Stress Analysis Algorithm

Authors: Yan Gao
Journal: Advances in Multimedia
 (2022)

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## Abstract

In order to study the psychological anxiety of the elderly, a psychological stress recognition algorithm based on ECG signal acquisition and heart rate variability was proposed based on the K-means algorithm. By collecting ECG signals of the elderly, HRV information can be accurately obtained, and RFC can be used to identify the psychological changes of the elderly under different degrees of stress. The research results show that the LR and RFC models have a better recognition effect on psychological stress when comparing with the KNN model. When the psychological stress is high, the test accuracy of the KNN model is 84.51%. The accuracy of stress recognition was 93.45%, and the accuracy of RFC’s recognition of psychological stress was 93.88%.


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## Body

## 1. Introduction

As of June 2021, the number of elderly people aged 60 and above in my country has exceeded 250 million. In the face of the increasingly obvious problem of aging and the reality of the accelerating rate of aging, we must pay attention to the solution to the problem of the elderly [1]. For the elderly, with the increase of age and the decline of physical quality, the torment of illness and the inconvenience of life, coupled with the fear of some diseases, are bound to be mixed with many factors. It causes huge psychological pressure on the elderly. Therefore, it is not only necessary to timely understand the physical health status of the elderly, but, more importantly, also to timely assess their mental health status, to maximize the understanding of elderly group of psychological problem-related factors, through the identification of psychological pressure to appease the elderly, and to provide them with targeted psychological counseling [2]. For this reason, this research starts from the perspective of ECG signal acquisition and heart rate variability to better identify the psychological stress of the elderly and selects an algorithm model that is more suitable for psychological stress identification through experimental comparison, so as to better evaluate and deal with the possible psychological stress problems of the elderly.


### 1.1. Literature Review

Zhou et al. believed that the increasing pressure of human life has made the identification algorithm of psychological stress gradually valued (Figure1), and since the beginning of the 21st century, the use of physiological parameters to identify psychological stress has become the focus of attention of domestic and foreign researchers. At present, there are many methods and means for the identification and assessment of psychological stress at home and abroad [3]. For example, Chen et al. effectively assessed the driver’s psychological state by collecting the drivers’ ECG signals, EMG signals, and breathing signals, mainly recording the physiological signals of drivers driving on fixed roads in the city center, and demonstrated the feasibility of using physiological signals to identify stress [4]; Hammad et al. identified the characteristics of skin electrical reactions through LDA and SVM algorithms, and the recognition rate of LDA algorithms reached more than 80% and induced psychological stress in humans through games. At the same time, the myoelectric signals and respiratory signals in the two different states of low pressure and high pressure were collected as the research objects, and finally, the LDA and Fisher discriminant analysis results were obtained, and the average recognition rate exceeded 85% [5]. Sharma et al. established a psychological stress model with support vector machine as a classifier and proved through experiments that the support vector machine algorithm model is stable in identifying stress and has a higher recognition rate. Physiological signals are collected, two kinds of physiological signals with pressure and no pressure are collected, and then, the difference between pressure and nonpressure is identified by correcting the loss function of the support vector machine. Finally, different people are tested and trained by this method to get higher classification accuracy [6].Figure 1
Psychological stress distribution.In recent years, China has also begun to attach importance to the use of physiological signals to identify psychological stress and is constantly conducting research and exploration. Lu et al. used EEG signals to identify human stress and chose K-nearest neighbor classifier as the classification algorithm in the system. Finally, an online stress monitoring system based on EEG signals was developed [7]; He et al. studied the psychological stress of specific groups of EEG signals, taking the mothers of seven children with intellectual disabilities and the mothers of four normal children of the same age as the research object, and using their EEG data as the data source, of which the EEG data of the mothers of the mentally disabled children were used as the stress data, and the EEG data of the mothers of normal children were the stress-free data. First, the linear and nonlinear features extracted from the EEG signal were compared and then combined with the evaluation scale of PSQL and LZC complexity, alpha relative power, and other characteristics, and finally, the psychological stress state was more effectively evaluated; 36 groups of ECG signals, 18 groups of surface EMG signals, and 18 groups of finger pulse wave signals were collected from nine testers, using these signals as the raw data to identify psychological stress, and then, the DS evidence theory was combined with the SVM algorithm to build a stress recognition model. Achieving the recognition of psychological stress, it proves the effectiveness of this model in assessing psychological stress states [8]. Aiming at the individual differences in identifying psychological stress, the algorithm was improved and studied. Taking EMG signal as the sample parameter of the study, Chen et al. proposed an improved support vector machine (SVM) psychological stress identification algorithm. In order to reduce the training error, the loss function of the support vector machine is improved by the method of clustering the samples, and the clustered information is assigned to the loss function to realize the recognition of psychological stress. It is shown that the algorithm can effectively address the individual differences in assessing psychological stress [9].


## 1.1. Literature Review

Zhou et al. believed that the increasing pressure of human life has made the identification algorithm of psychological stress gradually valued (Figure1), and since the beginning of the 21st century, the use of physiological parameters to identify psychological stress has become the focus of attention of domestic and foreign researchers. At present, there are many methods and means for the identification and assessment of psychological stress at home and abroad [3]. For example, Chen et al. effectively assessed the driver’s psychological state by collecting the drivers’ ECG signals, EMG signals, and breathing signals, mainly recording the physiological signals of drivers driving on fixed roads in the city center, and demonstrated the feasibility of using physiological signals to identify stress [4]; Hammad et al. identified the characteristics of skin electrical reactions through LDA and SVM algorithms, and the recognition rate of LDA algorithms reached more than 80% and induced psychological stress in humans through games. At the same time, the myoelectric signals and respiratory signals in the two different states of low pressure and high pressure were collected as the research objects, and finally, the LDA and Fisher discriminant analysis results were obtained, and the average recognition rate exceeded 85% [5]. Sharma et al. established a psychological stress model with support vector machine as a classifier and proved through experiments that the support vector machine algorithm model is stable in identifying stress and has a higher recognition rate. Physiological signals are collected, two kinds of physiological signals with pressure and no pressure are collected, and then, the difference between pressure and nonpressure is identified by correcting the loss function of the support vector machine. Finally, different people are tested and trained by this method to get higher classification accuracy [6].Figure 1
Psychological stress distribution.In recent years, China has also begun to attach importance to the use of physiological signals to identify psychological stress and is constantly conducting research and exploration. Lu et al. used EEG signals to identify human stress and chose K-nearest neighbor classifier as the classification algorithm in the system. Finally, an online stress monitoring system based on EEG signals was developed [7]; He et al. studied the psychological stress of specific groups of EEG signals, taking the mothers of seven children with intellectual disabilities and the mothers of four normal children of the same age as the research object, and using their EEG data as the data source, of which the EEG data of the mothers of the mentally disabled children were used as the stress data, and the EEG data of the mothers of normal children were the stress-free data. First, the linear and nonlinear features extracted from the EEG signal were compared and then combined with the evaluation scale of PSQL and LZC complexity, alpha relative power, and other characteristics, and finally, the psychological stress state was more effectively evaluated; 36 groups of ECG signals, 18 groups of surface EMG signals, and 18 groups of finger pulse wave signals were collected from nine testers, using these signals as the raw data to identify psychological stress, and then, the DS evidence theory was combined with the SVM algorithm to build a stress recognition model. Achieving the recognition of psychological stress, it proves the effectiveness of this model in assessing psychological stress states [8]. Aiming at the individual differences in identifying psychological stress, the algorithm was improved and studied. Taking EMG signal as the sample parameter of the study, Chen et al. proposed an improved support vector machine (SVM) psychological stress identification algorithm. In order to reduce the training error, the loss function of the support vector machine is improved by the method of clustering the samples, and the clustered information is assigned to the loss function to realize the recognition of psychological stress. It is shown that the algorithm can effectively address the individual differences in assessing psychological stress [9].


## 2. Methods

### 2.1. K-Means Algorithm Process Introduction

The cluster method has three main components for data collection [10].


#### 2.1.1. Select the Distance according to the Sample Measurements

TheT k-search algorithm means that the cluster algorithm is limited to only one part of each partition. When there are few examples of similarities in each class, the k-language algorithm tends to achieve better results. However, if the sample is similar in the upper grades, the division of the groups will continue. Therefore, by combining the algorithms, it is possible to obtain local accuracy rather than the world’s lowest accuracy of the function score [11].


#### 2.1.2. Selection Criterion Function

k-means algorithm means that the cluster algorithm is influenced by similar measurement choices and uses the error-sum quadratic criterion function to improve cluster performance. Suppose X contains k cluster subsets: X1,X2,…,Xk; the number of samples in each cluster subset is n1,n2,…,nk, and the mean points of each cluster subset are as follows:(1)m1,m2,…,mk.The formula for the error function of the sum of the squares is as follows:(2)E=∑i=1k∑p∈Xip=mi2.①
The calculation of similarity is carried out according to the average value of the objects in a cluster.②
Randomly designatek cluster center.③
For each sampleXi, we allocated to the nearest class according to the principle of minimum distance.④
Move the group content style to the center [12].⑤
Repeat steps two and three until the average of the groups does not change.As a two-dimensional example of group analysis, the number of clusters required isk=2, and we choose(3)O10,2,O20,0.The above formula is the initial cluster center, namely:(4)M1=O10,2,M2=O20,0.Based on the distance between the remaining objects and each central cluster, they are classified as the closest cluster. We pairO3:(5)dM1,O3=O−1.52+2−02=2.5,dM2,O3=O−1.52+0−02=1.5.Obviously, the formula is as follows:(6)dM2,O2<dM1,O3.So, we assignO3 to C2.ForO4,(7)dm2,O4=O−52+2−02=29,dM2,O4=O−52+0−02=5.Due todM1,O5≤dM2,O5, we assign O5 to C1.We update to get the new cluster as follows:(8)C1=O1,O5,C2=O2,O3,O4.Calculating the squared error criterion, the individual variance is as follows:(9)E1=0−02+2−22+0−52+2−22=25,M1=O1=0,2,E2=27.25,M2=O2=0,0.The overall average contrast is as follows:(10)E=E1+E2=25+27.25=52.25.


#### 2.1.3. Calculate the Center of the New Cluster

We repeat (2) and (3) to get O1 assigned to C1, O2 assigned to O2, O3 assigned to C2, O4 assigned to C2, and O5 assigned to C1. Updating to get a new cluster, the center is as follows:(11)M1=2.5,2,M2=2.17,0.The individual variances are as follows:(12)E1=0−2.52+2−22+2.5−52+2−22=12.5,E2=13.15.The overall mean error is as follows:(13)E=E1+E2=12.5+13.15=25.65.After the first iteration, the average error was corrected relatively well. Since the mean of the groups did not change during the two changes, the iteration process was stopped and the algorithm was completed.


### 2.2. Psychological Stress Recognition Based on ECG Signal Acquisition

#### 2.2.1. Contents of Physiological Parameters

(1) ECG Signal. The various characteristic waveforms of ECG can produce corresponding differences with the change of emotion. Identifying the psychological stress state by identifying the changes of the characteristic waveform is a method to identify psychological stress based on ECG signals [13]. Not only does the amplitude and duration of each waveform of the ECG have a certain effect on the study of psychological stress, but some activities of the heart also have very sensitive reactions to the state and level of psychological stress, such as heart rate, heart rate variability (HRV), and electrical activity. Among them, HRV is a very effective psychological stress assessment parameter. HRV defines the R-wave interval parameters of an ECG waveform in microseconds, and information on heart activity can be obtained by analyzing HRV through mathematical theories such as fast Fourier transform and wavelet theory [14].(2) Surface EMG Signal. EMG can be collected anywhere corresponding to the muscles on the human surface. For example, the muscle groups in the upper back are typical, and these muscle groups can effectively reflect emotional states, especially tension and stress. However, during game task research and testing, it is usually to collect electrical signals from the facial muscles, and the activity of this facial muscle group is associated with a negative or positive emotional response, and the subject will express the feeling of stress or tension in the facial muscle group, and the electrode can be collected by placing the electrode on a specific facial muscle group [15].(3) Finger Pulse Wave Signal. Finger pulse wave signal (FPPG) is a general reflection of the electrical activity inside blood vessels or on the skin surface when nerve impulses are transmitted in the heart conduction system, so PPG contains very important physiological information such as reflecting the overall physiological state of the heart and blood vessels. PPG concentric electrical signals are similar to several characteristic waveform, mainly composed of main wave, tidal wave, heavy wave, and other parts. The main frequency of the normal finger pulse wave signal is in the range below 40 Hz, and almost all the energy is distributed below 10 Hz [16].


#### 2.2.2. Experimental Instruments and Measurement Methods

(1) Instrument Parameters. The ECG signals required for the test were collected by an ECG device that received the signal generated by this study, which could record 12 lead ECG signals, including standard I, II, III, and chest V1 ∼ V6 branches. In combination with VR, VF, and VL, many leader symbols can be selected and used for testing. At the same time, the acquisition of the hardware part of the ECG signal includes some preprocessing functions, such as amplification, filtering, and A/D conversion, which can transmit the output data directly to the computer through the serial port for subsequent analysis and processing. The acquisition equipment for surface EMG signals and finger pulse wave signals uses the equipment already in the laboratory—multiconduction physiological recorder MP150. The acquisition module of MP150 can synchronously acquire ECG signal, EMG signal, finger pulse wave signal, EEG signal, gastrointestinal electric signal, etc. Under the experimental conditions, it can assist the synchronous acquisition of other electrophysiological signals [17]. The ECG signal acquisition hardware circuit part designed by the system belongs to the standard 12-lead ECG acquisition system, with a gain of 250 times, and amplifies the actual ECG signal on the human body surface to the volt level; the parameters of the filter circuit are that the high frequency is 312 Hz, and the low frequency is 0.045 Hz, and the sampling frequency is 1k Hz. The ECG signal collected by the ECG signal acquisition circuit of the system is already a serial digital signal after preliminary amplification and filtering [18].(2) Measurement Method. The participants of the experiment were 9 graduates of Yanshan University. The students were healthy, deaf, and right-handed, without any confusion; did not change their minds before the examination; and were on paper approved. The data collection method is shown in Figure 2.Figure 2
Data collection method.(3) Data collection. The data collected in this experiment include ECG data collected by the circuit designed in this research, surface EMG data collected by MP150, and finger pulse wave data. The collected ECG signals of 8 channels are sent in the form of data packets [19]. The packet contains 6 octave headers, ECG data collected by 8 leads arranged in sequence, and standard 12-lead ECG signal data obtained according to the international standard 10-channel 12-lead ECG signal calculation method. The calculation method is shown in the following formula .(14)C1∼C6=V1∼V6I=III=IIIII=II−IaVR=12I+IIaVR=I−12IIaVR=II−12I.The ECG data collected by the experiment can be processed according to the batch data model to produce the data process, and the counting process can be viewed with MATLAB software. The counting process is data exchange, data isolation, grouping, and high—method of combining data, signal structure calculations, and wave images. The signal count is complete according to the standard (17). There are clear differences in the waveform of the ECG signal. Relatively speaking, the waveform of the standard lead is closer to the standard ECG signal, so this research will select the standard lead for the later algorithm to identify psychological stress [20].


## 2.1. K-Means Algorithm Process Introduction

The cluster method has three main components for data collection [10].


### 2.1.1. Select the Distance according to the Sample Measurements

TheT k-search algorithm means that the cluster algorithm is limited to only one part of each partition. When there are few examples of similarities in each class, the k-language algorithm tends to achieve better results. However, if the sample is similar in the upper grades, the division of the groups will continue. Therefore, by combining the algorithms, it is possible to obtain local accuracy rather than the world’s lowest accuracy of the function score [11].


### 2.1.2. Selection Criterion Function

k-means algorithm means that the cluster algorithm is influenced by similar measurement choices and uses the error-sum quadratic criterion function to improve cluster performance. Suppose X contains k cluster subsets: X1,X2,…,Xk; the number of samples in each cluster subset is n1,n2,…,nk, and the mean points of each cluster subset are as follows:(1)m1,m2,…,mk.The formula for the error function of the sum of the squares is as follows:(2)E=∑i=1k∑p∈Xip=mi2.①
The calculation of similarity is carried out according to the average value of the objects in a cluster.②
Randomly designatek cluster center.③
For each sampleXi, we allocated to the nearest class according to the principle of minimum distance.④
Move the group content style to the center [12].⑤
Repeat steps two and three until the average of the groups does not change.As a two-dimensional example of group analysis, the number of clusters required isk=2, and we choose(3)O10,2,O20,0.The above formula is the initial cluster center, namely:(4)M1=O10,2,M2=O20,0.Based on the distance between the remaining objects and each central cluster, they are classified as the closest cluster. We pairO3:(5)dM1,O3=O−1.52+2−02=2.5,dM2,O3=O−1.52+0−02=1.5.Obviously, the formula is as follows:(6)dM2,O2<dM1,O3.So, we assignO3 to C2.ForO4,(7)dm2,O4=O−52+2−02=29,dM2,O4=O−52+0−02=5.Due todM1,O5≤dM2,O5, we assign O5 to C1.We update to get the new cluster as follows:(8)C1=O1,O5,C2=O2,O3,O4.Calculating the squared error criterion, the individual variance is as follows:(9)E1=0−02+2−22+0−52+2−22=25,M1=O1=0,2,E2=27.25,M2=O2=0,0.The overall average contrast is as follows:(10)E=E1+E2=25+27.25=52.25.


### 2.1.3. Calculate the Center of the New Cluster

We repeat (2) and (3) to get O1 assigned to C1, O2 assigned to O2, O3 assigned to C2, O4 assigned to C2, and O5 assigned to C1. Updating to get a new cluster, the center is as follows:(11)M1=2.5,2,M2=2.17,0.The individual variances are as follows:(12)E1=0−2.52+2−22+2.5−52+2−22=12.5,E2=13.15.The overall mean error is as follows:(13)E=E1+E2=12.5+13.15=25.65.After the first iteration, the average error was corrected relatively well. Since the mean of the groups did not change during the two changes, the iteration process was stopped and the algorithm was completed.


## 2.1.1. Select the Distance according to the Sample Measurements

TheT k-search algorithm means that the cluster algorithm is limited to only one part of each partition. When there are few examples of similarities in each class, the k-language algorithm tends to achieve better results. However, if the sample is similar in the upper grades, the division of the groups will continue. Therefore, by combining the algorithms, it is possible to obtain local accuracy rather than the world’s lowest accuracy of the function score [11].


## 2.1.2. Selection Criterion Function

k-means algorithm means that the cluster algorithm is influenced by similar measurement choices and uses the error-sum quadratic criterion function to improve cluster performance. Suppose X contains k cluster subsets: X1,X2,…,Xk; the number of samples in each cluster subset is n1,n2,…,nk, and the mean points of each cluster subset are as follows:(1)m1,m2,…,mk.The formula for the error function of the sum of the squares is as follows:(2)E=∑i=1k∑p∈Xip=mi2.①
The calculation of similarity is carried out according to the average value of the objects in a cluster.②
Randomly designatek cluster center.③
For each sampleXi, we allocated to the nearest class according to the principle of minimum distance.④
Move the group content style to the center [12].⑤
Repeat steps two and three until the average of the groups does not change.As a two-dimensional example of group analysis, the number of clusters required isk=2, and we choose(3)O10,2,O20,0.The above formula is the initial cluster center, namely:(4)M1=O10,2,M2=O20,0.Based on the distance between the remaining objects and each central cluster, they are classified as the closest cluster. We pairO3:(5)dM1,O3=O−1.52+2−02=2.5,dM2,O3=O−1.52+0−02=1.5.Obviously, the formula is as follows:(6)dM2,O2<dM1,O3.So, we assignO3 to C2.ForO4,(7)dm2,O4=O−52+2−02=29,dM2,O4=O−52+0−02=5.Due todM1,O5≤dM2,O5, we assign O5 to C1.We update to get the new cluster as follows:(8)C1=O1,O5,C2=O2,O3,O4.Calculating the squared error criterion, the individual variance is as follows:(9)E1=0−02+2−22+0−52+2−22=25,M1=O1=0,2,E2=27.25,M2=O2=0,0.The overall average contrast is as follows:(10)E=E1+E2=25+27.25=52.25.


## 2.1.3. Calculate the Center of the New Cluster

We repeat (2) and (3) to get O1 assigned to C1, O2 assigned to O2, O3 assigned to C2, O4 assigned to C2, and O5 assigned to C1. Updating to get a new cluster, the center is as follows:(11)M1=2.5,2,M2=2.17,0.The individual variances are as follows:(12)E1=0−2.52+2−22+2.5−52+2−22=12.5,E2=13.15.The overall mean error is as follows:(13)E=E1+E2=12.5+13.15=25.65.After the first iteration, the average error was corrected relatively well. Since the mean of the groups did not change during the two changes, the iteration process was stopped and the algorithm was completed.


## 2.2. Psychological Stress Recognition Based on ECG Signal Acquisition

### 2.2.1. Contents of Physiological Parameters

(1) ECG Signal. The various characteristic waveforms of ECG can produce corresponding differences with the change of emotion. Identifying the psychological stress state by identifying the changes of the characteristic waveform is a method to identify psychological stress based on ECG signals [13]. Not only does the amplitude and duration of each waveform of the ECG have a certain effect on the study of psychological stress, but some activities of the heart also have very sensitive reactions to the state and level of psychological stress, such as heart rate, heart rate variability (HRV), and electrical activity. Among them, HRV is a very effective psychological stress assessment parameter. HRV defines the R-wave interval parameters of an ECG waveform in microseconds, and information on heart activity can be obtained by analyzing HRV through mathematical theories such as fast Fourier transform and wavelet theory [14].(2) Surface EMG Signal. EMG can be collected anywhere corresponding to the muscles on the human surface. For example, the muscle groups in the upper back are typical, and these muscle groups can effectively reflect emotional states, especially tension and stress. However, during game task research and testing, it is usually to collect electrical signals from the facial muscles, and the activity of this facial muscle group is associated with a negative or positive emotional response, and the subject will express the feeling of stress or tension in the facial muscle group, and the electrode can be collected by placing the electrode on a specific facial muscle group [15].(3) Finger Pulse Wave Signal. Finger pulse wave signal (FPPG) is a general reflection of the electrical activity inside blood vessels or on the skin surface when nerve impulses are transmitted in the heart conduction system, so PPG contains very important physiological information such as reflecting the overall physiological state of the heart and blood vessels. PPG concentric electrical signals are similar to several characteristic waveform, mainly composed of main wave, tidal wave, heavy wave, and other parts. The main frequency of the normal finger pulse wave signal is in the range below 40 Hz, and almost all the energy is distributed below 10 Hz [16].


### 2.2.2. Experimental Instruments and Measurement Methods

(1) Instrument Parameters. The ECG signals required for the test were collected by an ECG device that received the signal generated by this study, which could record 12 lead ECG signals, including standard I, II, III, and chest V1 ∼ V6 branches. In combination with VR, VF, and VL, many leader symbols can be selected and used for testing. At the same time, the acquisition of the hardware part of the ECG signal includes some preprocessing functions, such as amplification, filtering, and A/D conversion, which can transmit the output data directly to the computer through the serial port for subsequent analysis and processing. The acquisition equipment for surface EMG signals and finger pulse wave signals uses the equipment already in the laboratory—multiconduction physiological recorder MP150. The acquisition module of MP150 can synchronously acquire ECG signal, EMG signal, finger pulse wave signal, EEG signal, gastrointestinal electric signal, etc. Under the experimental conditions, it can assist the synchronous acquisition of other electrophysiological signals [17]. The ECG signal acquisition hardware circuit part designed by the system belongs to the standard 12-lead ECG acquisition system, with a gain of 250 times, and amplifies the actual ECG signal on the human body surface to the volt level; the parameters of the filter circuit are that the high frequency is 312 Hz, and the low frequency is 0.045 Hz, and the sampling frequency is 1k Hz. The ECG signal collected by the ECG signal acquisition circuit of the system is already a serial digital signal after preliminary amplification and filtering [18].(2) Measurement Method. The participants of the experiment were 9 graduates of Yanshan University. The students were healthy, deaf, and right-handed, without any confusion; did not change their minds before the examination; and were on paper approved. The data collection method is shown in Figure 2.Figure 2
Data collection method.(3) Data collection. The data collected in this experiment include ECG data collected by the circuit designed in this research, surface EMG data collected by MP150, and finger pulse wave data. The collected ECG signals of 8 channels are sent in the form of data packets [19]. The packet contains 6 octave headers, ECG data collected by 8 leads arranged in sequence, and standard 12-lead ECG signal data obtained according to the international standard 10-channel 12-lead ECG signal calculation method. The calculation method is shown in the following formula .(14)C1∼C6=V1∼V6I=III=IIIII=II−IaVR=12I+IIaVR=I−12IIaVR=II−12I.The ECG data collected by the experiment can be processed according to the batch data model to produce the data process, and the counting process can be viewed with MATLAB software. The counting process is data exchange, data isolation, grouping, and high—method of combining data, signal structure calculations, and wave images. The signal count is complete according to the standard (17). There are clear differences in the waveform of the ECG signal. Relatively speaking, the waveform of the standard lead is closer to the standard ECG signal, so this research will select the standard lead for the later algorithm to identify psychological stress [20].


## 2.2.1. Contents of Physiological Parameters

(1) ECG Signal. The various characteristic waveforms of ECG can produce corresponding differences with the change of emotion. Identifying the psychological stress state by identifying the changes of the characteristic waveform is a method to identify psychological stress based on ECG signals [13]. Not only does the amplitude and duration of each waveform of the ECG have a certain effect on the study of psychological stress, but some activities of the heart also have very sensitive reactions to the state and level of psychological stress, such as heart rate, heart rate variability (HRV), and electrical activity. Among them, HRV is a very effective psychological stress assessment parameter. HRV defines the R-wave interval parameters of an ECG waveform in microseconds, and information on heart activity can be obtained by analyzing HRV through mathematical theories such as fast Fourier transform and wavelet theory [14].(2) Surface EMG Signal. EMG can be collected anywhere corresponding to the muscles on the human surface. For example, the muscle groups in the upper back are typical, and these muscle groups can effectively reflect emotional states, especially tension and stress. However, during game task research and testing, it is usually to collect electrical signals from the facial muscles, and the activity of this facial muscle group is associated with a negative or positive emotional response, and the subject will express the feeling of stress or tension in the facial muscle group, and the electrode can be collected by placing the electrode on a specific facial muscle group [15].(3) Finger Pulse Wave Signal. Finger pulse wave signal (FPPG) is a general reflection of the electrical activity inside blood vessels or on the skin surface when nerve impulses are transmitted in the heart conduction system, so PPG contains very important physiological information such as reflecting the overall physiological state of the heart and blood vessels. PPG concentric electrical signals are similar to several characteristic waveform, mainly composed of main wave, tidal wave, heavy wave, and other parts. The main frequency of the normal finger pulse wave signal is in the range below 40 Hz, and almost all the energy is distributed below 10 Hz [16].


## 2.2.2. Experimental Instruments and Measurement Methods

(1) Instrument Parameters. The ECG signals required for the test were collected by an ECG device that received the signal generated by this study, which could record 12 lead ECG signals, including standard I, II, III, and chest V1 ∼ V6 branches. In combination with VR, VF, and VL, many leader symbols can be selected and used for testing. At the same time, the acquisition of the hardware part of the ECG signal includes some preprocessing functions, such as amplification, filtering, and A/D conversion, which can transmit the output data directly to the computer through the serial port for subsequent analysis and processing. The acquisition equipment for surface EMG signals and finger pulse wave signals uses the equipment already in the laboratory—multiconduction physiological recorder MP150. The acquisition module of MP150 can synchronously acquire ECG signal, EMG signal, finger pulse wave signal, EEG signal, gastrointestinal electric signal, etc. Under the experimental conditions, it can assist the synchronous acquisition of other electrophysiological signals [17]. The ECG signal acquisition hardware circuit part designed by the system belongs to the standard 12-lead ECG acquisition system, with a gain of 250 times, and amplifies the actual ECG signal on the human body surface to the volt level; the parameters of the filter circuit are that the high frequency is 312 Hz, and the low frequency is 0.045 Hz, and the sampling frequency is 1k Hz. The ECG signal collected by the ECG signal acquisition circuit of the system is already a serial digital signal after preliminary amplification and filtering [18].(2) Measurement Method. The participants of the experiment were 9 graduates of Yanshan University. The students were healthy, deaf, and right-handed, without any confusion; did not change their minds before the examination; and were on paper approved. The data collection method is shown in Figure 2.Figure 2
Data collection method.(3) Data collection. The data collected in this experiment include ECG data collected by the circuit designed in this research, surface EMG data collected by MP150, and finger pulse wave data. The collected ECG signals of 8 channels are sent in the form of data packets [19]. The packet contains 6 octave headers, ECG data collected by 8 leads arranged in sequence, and standard 12-lead ECG signal data obtained according to the international standard 10-channel 12-lead ECG signal calculation method. The calculation method is shown in the following formula .(14)C1∼C6=V1∼V6I=III=IIIII=II−IaVR=12I+IIaVR=I−12IIaVR=II−12I.The ECG data collected by the experiment can be processed according to the batch data model to produce the data process, and the counting process can be viewed with MATLAB software. The counting process is data exchange, data isolation, grouping, and high—method of combining data, signal structure calculations, and wave images. The signal count is complete according to the standard (17). There are clear differences in the waveform of the ECG signal. Relatively speaking, the waveform of the standard lead is closer to the standard ECG signal, so this research will select the standard lead for the later algorithm to identify psychological stress [20].


## 3. Experimental Analysis

### 3.1. Psychological Stress Recognition Algorithm Based on Heart Rate Variability

#### 3.1.1. ECG Signal Acquisition

The data collection place is selected in a quiet, closed room; before the experiment, the participants first attached the electrodes of the ECG signal acquisition device to the chest through the V5 lead, and then sat in front of the computer equipped with the data acquisition platform, and filled in the basic personal information in the login interface of the data acquisition platform. The acquisition process of the experiment is divided into 4 stages (relaxation, low level, intermediate level, and high level), as shown in Figure3.Figure 3
Experimental processes.In the experiment, each participant collected 5 sets of ECG data; each group contained four different states of relaxation, low-level pressure, intermediate pressure, and high-level pressure; and a total of 200 groups of ECG data containing different stress states were collected [21]. Using digital signal processing technology, high-precision and high-reliability filters can be designed. In different environments, only a few parameters need to be modified in the software, and it also has strong versatility. The design of the traditional digital filter for ECG signal noise is mainly for the spectral range of different noises, using a digital filtering method with linear phase, respectively, to filter out the power frequency interference, baseline drift, and EMG interference in the ECG signal, but the traditional digital filtering method is based on Fourier changes, using a global transformation, which cannot express the local characteristics of the time and frequency of the signal. We need to make the subsignal frequency of a certain scale, which reaches this frequency band after decomposing the signal [22]. The sampling frequency of the ECG signal in this research is 250 Hz. According to the above principle, the 7-layer wavelet decomposition can meet the basic requirements of ECG signal denoising. The frequency and noise distribution of each layer after decomposition are shown in Table 1.Table 1
Frequency and noise distribution of wavelet decomposition.
Low-frequency componentsFrequency rangeNoiseHigh-frequency componentsFrequency rangeNoiseA00–125—D0105–240A10–62.5—D160.5–10.5EMG interferenceA20–31.3—D230.3–52.5Power frequency interference—————EMG interferenceA30–15.6—D314.6–30.3EMG interferenceA40–7.8—D46.8–15.6EMG interferenceA50–3.9—D52.8–7.8EMG interferenceA60–1.9—D61.8–3.9A70–0.9Baseline driftD70.8–1.9As shown in the table above, the original ECG signal through 7 layers of wavelet decomposition is to obtain the low-frequency component and high-frequency component of the signal at each scale, because the signal frequency of the ECG signal causing baseline drift is less than 1 Hz, and the frequency range of A7 is close, and it can be considered that A7 contains the information of baseline drift, the same as the frequency of the power frequency interference is 50 Hz, all distributed in D2, the MYO interference frequency range is 5Hz-2000 Hz, and it is completely distributed on the 5 high-frequency components of D1 to D5. At the same time, its signal is mainly concentrated in the frequency range of D1 and D2. It can be seen that different noise energies of the ECG signal are distributed to different frequency intervals after wavelet decomposition, and the noise can be filtered or suppressed by setting an appropriate threshold function in this different interval.


### 3.2. Extraction of HRV Eigenvalues

#### 3.2.1. Extraction of Time-Domain Eigenvalues

Time domain analysis is the earliest used analytical method for HRV, which studies the extent to which a stimulus causes a transient change in HRV by performing a statistically discrete trend analysis of a sequence of RR intervals. Time domain analysis for HRV is divided into two main methods: statistical analysis and geometric analysis. The geometric figure method is not sensitive to abnormal heart rate in HRV analysis, but generally requires long-term acquisition of ECG signal data to draw, which is suitable for long-term ECG signal analysis. The statistical analysis method is simple and fast to calculate, and both long- and short-range ECG signals can be selected and used according to the index characteristics. In this research, because the short-range HRV signal is analyzed, the statistical analysis method is used to extract the eigenvalues from the RR interval sequence.


#### 3.2.2. Extraction of Frequency-Domain Eigenvalues

Modern spectral calculations have been developed to solve the problem of low accuracy and large differences in classical spectral calculations [23]. From the spectral evaluation method, modern spectral evaluation can be divided into two types: parametric modeling and nonparametric modeling, of which parametric modeling is the basic model of modern spectral evaluation, AR model, MA model, and ARMA model. The idea of the parametric model method is to build a similar model of the actual signal based on the prior knowledge of the process, and then use the known limited observations or the estimation of its limited autocorrelation function to estimate the parameters of the model, and finally calculate the power spectrum of the model. The parametric model spectral estimation method has no windowing process, which avoids the problems caused by windowing in the classical spectral estimation, and has better frequency resolution and stability, but it also has some problems, such as the difficulty of determining the order of the AR model and poor trough tracking.The LS periodogram is based on the periodogram method of classical spectrum estimation. It cannot directly analyze the spectrum of nonuniformly sampled signals. The degree of fitting is such that the Fourier transform can be equivalently applied to signals that are sampled at unequal intervals. In this research, the LS periodogram is used to obtain the power spectrum of HRV, and the frequency domain features of HRV are extracted. The power density spectrum is shown in Figure4.Figure 4
HRV power density spectrum of Lomb–Scargle method.Physiological studies have found that the power spectral line of HRV in normal people’s calm state is mainly at 0–0.4 Hz, mainly including three spectral components, high-frequency component (HF, spectral peak around 0.25 Hz), low-frequency component (LF, spectral peak around 0.1 Hz), and the “1/f component” where the power spectral density increases with decreasing frequency extending to very low frequencies [24].


### 3.3. Pressure Recognition Model for HRV

The human brain is very complex and usually consists of two segments: the central nervous system and the peripheral nervous system. The peripheral nervous system includes the autonomic nervous system (ANS) and the somatic nervous system, and ANS is particularly associated with negative emotions such as stress, anxiety, and depression. The activity of ANS is related to the body’s immune system: blood pressure, respiration, heart rate, body temperature, digestive, and endocrine systems. ANS itself consists of two segments, the sympathetic nervous system and the parasympathetic nervous system, which are responsible for developing a stress and relaxation response, as shown in Figure5.Figure 5
Hierarchical structure of the brain.


#### 3.3.1. Pressure Identification Weight Analysis of HRV Eigenvalues

A total of 11 different functions of the features of HRV used to create high-quality models in this study are 5 time domains such as SDNN, RMSSD, SDSD, NN50, and PNN50; 4 hour domains such as VLF, LF, HF, and LF/HF; and 2 blast points for analysis such as VAI and VLI for nonlinear quantization properties. We will use random memory significance measurements to better understand the relationship between HRV characteristics and severity to determine the severity of HRV variables in psychiatric disorders. For the HRV training model, this study provides a measure of the value of the forest in the previous section and a stress-level measure of the model for calculating the weight of each HRV specialization in recreation and stress according to the report. In Figure6, the sum values of all the properties are up to 1.Figure 6
HRV feature weight in stress recognition.From the figure above, it can be seen from the HRV characteristics obtained in this study that LF and HF are more supportive of altitude detection. LF and HF are measures of human brain function. It can be seen that the human mind is affected by the autonomic nervous system. From the point of view of HRV analysis, frequency monitoring works best in the analytical corner of our article, and LF feature is the most important indicator of HRV to determine the characteristics of brain stress, observation time, and nonlinear distribution analysis. Closely, its nonlinear nature suggests that the VLI, which ranks second after frequency measurements, excludes the Poincare scatterplot, a measure of how much VLI is used in this document that can determine stress in the brain [25].


#### 3.3.2. Model Recognition Effect Evaluation

In this study, the K-En yakın neighbor (KNN), logistics regression (LR) model, and random forest classification (RFC) model are used in most comparative studies to study the effect of random forest modeling on determining HRV stress status. The design features were modified 5 times according to the validation; that is, the data were randomly divided into 5 parts: 4 parts were taken according to the training, and 1 part was backed up according to the test set to experiment. We use the model to determine stress and low stress, stress and moderate states, and stress and anxiety states, each of which determines the accuracy of our model through ROC curves and 20 cross-validation tests based on performance measurements and standards. The ROC curves and AUC values of the three stress difference models are shown in Figure7, and the diagonal dashed line shows the results of the assumptions. Assuming, the AUC is 0.5.Figure 7
ROC curves of models KNN, LR, and RFC to identify relaxation and low-stress states.The closer the ROC curve is to the upper left, the greater the space at its lower point, the better the structural performance, the closer the dashed diagonal, and the closer the AUC is to the standard performance. In the analysis of the rest and low-pressure conditions from Figure8, the AUCs of KNN, LR, and RFC were 0.62, 075, and 0.78, respectively, and the performance of the LR and RFC models was similar, while the performance of KNN was also high. All the benefits of our model are negative, which is poor. In AUC, the AUCs of KNN, LR, and RFC are 0.72, 0.90, and 095, respectively, to determine the average voltage. Meanwhile, RFC is better recognized, LR is slightly reduced, and KNN’s performance recognition remains poor. Figure 9. In the analysis of relaxation and stress conditions, the AUCs of KNN, LR, and RFC were 0.88, 0.96, and 0.96, respectively. During this time, all three models gained excellent experience. As the level increases, the performance of our model increases in the sense that it is higher. RFC and LR are more effective than KNN.Figure 8
ROC curves of models KNN, LR, and RFC to identify relaxation and moderate stress states.Figure 9
ROC curves of models KNN, LR, and RFC to identify relaxation and high-stress states.Table2 describes the weaknesses and accuracy of our model for determining stress and low stress states, stress and moderate states, and stress states and levels.Table 2
Classification results of three classifiers in relaxation and different stress states.
StateClassifierMain parameterAccuracyRelaxed/low-pressure stateKNNK = 759.38LRpenalty = ′12′, tol = 0.000174.43RFCTree_nums = 1000, Mtry = 472.35Relaxed/medium-pressure stateKNNK = 763.46LRPenalty = ′12′, tol = 0.000188.94RFCTree_nums = 1000, Mtry = 490.03Relaxed/high-pressure stateKNNK = 778.51LRPenalty = ′12′, tol = 0.000192.45RFCTree_nums = 1000, Mtry = 489.88In Table2, the exceptions of the three models were corrected by cross-validation five times. K in KNN represents the number of closest people, the LR penalty represents the use of the l2 restriction, and tol = 0.0001 is an exception in the case of dropout. The parameter Tree_nums = 1000 in RFC represents the number of metaclassifiers in the random memory, and Mtry = 4 represents the number of subset of functions selected at random. Figure 10 compares our class acceptance factor (ACC) for rest and stress fluctuations.Figure 10
Comparison of classification accuracy of three classifiers under relaxation and different stress states.Figure10 shows that the recognition accuracy of the three models in identifying relaxation and different stress states is consistent with the ROC curve and AUC performance. When in a lower stress state, the recognition accuracy of the three models is lower. Model LR and RFC identification are only good when the pressure state reaches medium-intensity pressure and above. Comparing the recognition accuracy of the three models at the same time, it is found that KNN has a lower accuracy than the other two models in identifying relaxation and different psychological pressures, while the accuracy of LR and RFC is close, and RFC is slightly better than LR.Aiming at the stress identification problem of HRV, this research adopts the random forest classification algorithm to establish a stress identification model based on random forest and discusses the construction process of the HRV stress model and the calculation method of the HRV feature weight in the identification model in detail. Experimental results show that changes in psychological stress state can be identified by HRV, and the LF and HF extracted by frequency domain analysis are the main characteristics of HRV to identify psychological stress, and the characteristic value of HRV is more sensitive when the pressure is larger. At the same time, through the comparative experiment of three classifiers, it is found that when the HRV is used to identify psychological stress states, RFC and LR have better recognition effects than KNN, and the recognition effect is similar. When the degree of stress is high, the random forest model has a better recognition performance as a whole, reaching a recognition rate of about 90%.Because psychological stress is closely related to individual’s physical and mental health and quality of life, research on automatic identification of psychological stress is of great significance. Biosignal HRV is a common assessment for detecting and identifying psychological stress, it is able to react to the state of psychological stress without subjective consciousness, and current physiological mechanisms and studies of HRV to identify psychological stress have shown that HRV is associated with psychological stress. The purpose of this research is to automatically identify different levels of psychological stress by biological signal HRV and use video games to induce relaxation and low, medium, and high psychological stress. HRV is obtained by collecting ECG signals, and time domain and frequency domain are extracted from HRV.


## 3.1. Psychological Stress Recognition Algorithm Based on Heart Rate Variability

### 3.1.1. ECG Signal Acquisition

The data collection place is selected in a quiet, closed room; before the experiment, the participants first attached the electrodes of the ECG signal acquisition device to the chest through the V5 lead, and then sat in front of the computer equipped with the data acquisition platform, and filled in the basic personal information in the login interface of the data acquisition platform. The acquisition process of the experiment is divided into 4 stages (relaxation, low level, intermediate level, and high level), as shown in Figure3.Figure 3
Experimental processes.In the experiment, each participant collected 5 sets of ECG data; each group contained four different states of relaxation, low-level pressure, intermediate pressure, and high-level pressure; and a total of 200 groups of ECG data containing different stress states were collected [21]. Using digital signal processing technology, high-precision and high-reliability filters can be designed. In different environments, only a few parameters need to be modified in the software, and it also has strong versatility. The design of the traditional digital filter for ECG signal noise is mainly for the spectral range of different noises, using a digital filtering method with linear phase, respectively, to filter out the power frequency interference, baseline drift, and EMG interference in the ECG signal, but the traditional digital filtering method is based on Fourier changes, using a global transformation, which cannot express the local characteristics of the time and frequency of the signal. We need to make the subsignal frequency of a certain scale, which reaches this frequency band after decomposing the signal [22]. The sampling frequency of the ECG signal in this research is 250 Hz. According to the above principle, the 7-layer wavelet decomposition can meet the basic requirements of ECG signal denoising. The frequency and noise distribution of each layer after decomposition are shown in Table 1.Table 1
Frequency and noise distribution of wavelet decomposition.
Low-frequency componentsFrequency rangeNoiseHigh-frequency componentsFrequency rangeNoiseA00–125—D0105–240A10–62.5—D160.5–10.5EMG interferenceA20–31.3—D230.3–52.5Power frequency interference—————EMG interferenceA30–15.6—D314.6–30.3EMG interferenceA40–7.8—D46.8–15.6EMG interferenceA50–3.9—D52.8–7.8EMG interferenceA60–1.9—D61.8–3.9A70–0.9Baseline driftD70.8–1.9As shown in the table above, the original ECG signal through 7 layers of wavelet decomposition is to obtain the low-frequency component and high-frequency component of the signal at each scale, because the signal frequency of the ECG signal causing baseline drift is less than 1 Hz, and the frequency range of A7 is close, and it can be considered that A7 contains the information of baseline drift, the same as the frequency of the power frequency interference is 50 Hz, all distributed in D2, the MYO interference frequency range is 5Hz-2000 Hz, and it is completely distributed on the 5 high-frequency components of D1 to D5. At the same time, its signal is mainly concentrated in the frequency range of D1 and D2. It can be seen that different noise energies of the ECG signal are distributed to different frequency intervals after wavelet decomposition, and the noise can be filtered or suppressed by setting an appropriate threshold function in this different interval.


## 3.1.1. ECG Signal Acquisition

The data collection place is selected in a quiet, closed room; before the experiment, the participants first attached the electrodes of the ECG signal acquisition device to the chest through the V5 lead, and then sat in front of the computer equipped with the data acquisition platform, and filled in the basic personal information in the login interface of the data acquisition platform. The acquisition process of the experiment is divided into 4 stages (relaxation, low level, intermediate level, and high level), as shown in Figure3.Figure 3
Experimental processes.In the experiment, each participant collected 5 sets of ECG data; each group contained four different states of relaxation, low-level pressure, intermediate pressure, and high-level pressure; and a total of 200 groups of ECG data containing different stress states were collected [21]. Using digital signal processing technology, high-precision and high-reliability filters can be designed. In different environments, only a few parameters need to be modified in the software, and it also has strong versatility. The design of the traditional digital filter for ECG signal noise is mainly for the spectral range of different noises, using a digital filtering method with linear phase, respectively, to filter out the power frequency interference, baseline drift, and EMG interference in the ECG signal, but the traditional digital filtering method is based on Fourier changes, using a global transformation, which cannot express the local characteristics of the time and frequency of the signal. We need to make the subsignal frequency of a certain scale, which reaches this frequency band after decomposing the signal [22]. The sampling frequency of the ECG signal in this research is 250 Hz. According to the above principle, the 7-layer wavelet decomposition can meet the basic requirements of ECG signal denoising. The frequency and noise distribution of each layer after decomposition are shown in Table 1.Table 1
Frequency and noise distribution of wavelet decomposition.
Low-frequency componentsFrequency rangeNoiseHigh-frequency componentsFrequency rangeNoiseA00–125—D0105–240A10–62.5—D160.5–10.5EMG interferenceA20–31.3—D230.3–52.5Power frequency interference—————EMG interferenceA30–15.6—D314.6–30.3EMG interferenceA40–7.8—D46.8–15.6EMG interferenceA50–3.9—D52.8–7.8EMG interferenceA60–1.9—D61.8–3.9A70–0.9Baseline driftD70.8–1.9As shown in the table above, the original ECG signal through 7 layers of wavelet decomposition is to obtain the low-frequency component and high-frequency component of the signal at each scale, because the signal frequency of the ECG signal causing baseline drift is less than 1 Hz, and the frequency range of A7 is close, and it can be considered that A7 contains the information of baseline drift, the same as the frequency of the power frequency interference is 50 Hz, all distributed in D2, the MYO interference frequency range is 5Hz-2000 Hz, and it is completely distributed on the 5 high-frequency components of D1 to D5. At the same time, its signal is mainly concentrated in the frequency range of D1 and D2. It can be seen that different noise energies of the ECG signal are distributed to different frequency intervals after wavelet decomposition, and the noise can be filtered or suppressed by setting an appropriate threshold function in this different interval.


## 3.2. Extraction of HRV Eigenvalues

### 3.2.1. Extraction of Time-Domain Eigenvalues

Time domain analysis is the earliest used analytical method for HRV, which studies the extent to which a stimulus causes a transient change in HRV by performing a statistically discrete trend analysis of a sequence of RR intervals. Time domain analysis for HRV is divided into two main methods: statistical analysis and geometric analysis. The geometric figure method is not sensitive to abnormal heart rate in HRV analysis, but generally requires long-term acquisition of ECG signal data to draw, which is suitable for long-term ECG signal analysis. The statistical analysis method is simple and fast to calculate, and both long- and short-range ECG signals can be selected and used according to the index characteristics. In this research, because the short-range HRV signal is analyzed, the statistical analysis method is used to extract the eigenvalues from the RR interval sequence.


### 3.2.2. Extraction of Frequency-Domain Eigenvalues

Modern spectral calculations have been developed to solve the problem of low accuracy and large differences in classical spectral calculations [23]. From the spectral evaluation method, modern spectral evaluation can be divided into two types: parametric modeling and nonparametric modeling, of which parametric modeling is the basic model of modern spectral evaluation, AR model, MA model, and ARMA model. The idea of the parametric model method is to build a similar model of the actual signal based on the prior knowledge of the process, and then use the known limited observations or the estimation of its limited autocorrelation function to estimate the parameters of the model, and finally calculate the power spectrum of the model. The parametric model spectral estimation method has no windowing process, which avoids the problems caused by windowing in the classical spectral estimation, and has better frequency resolution and stability, but it also has some problems, such as the difficulty of determining the order of the AR model and poor trough tracking.The LS periodogram is based on the periodogram method of classical spectrum estimation. It cannot directly analyze the spectrum of nonuniformly sampled signals. The degree of fitting is such that the Fourier transform can be equivalently applied to signals that are sampled at unequal intervals. In this research, the LS periodogram is used to obtain the power spectrum of HRV, and the frequency domain features of HRV are extracted. The power density spectrum is shown in Figure4.Figure 4
HRV power density spectrum of Lomb–Scargle method.Physiological studies have found that the power spectral line of HRV in normal people’s calm state is mainly at 0–0.4 Hz, mainly including three spectral components, high-frequency component (HF, spectral peak around 0.25 Hz), low-frequency component (LF, spectral peak around 0.1 Hz), and the “1/f component” where the power spectral density increases with decreasing frequency extending to very low frequencies [24].


## 3.2.1. Extraction of Time-Domain Eigenvalues

Time domain analysis is the earliest used analytical method for HRV, which studies the extent to which a stimulus causes a transient change in HRV by performing a statistically discrete trend analysis of a sequence of RR intervals. Time domain analysis for HRV is divided into two main methods: statistical analysis and geometric analysis. The geometric figure method is not sensitive to abnormal heart rate in HRV analysis, but generally requires long-term acquisition of ECG signal data to draw, which is suitable for long-term ECG signal analysis. The statistical analysis method is simple and fast to calculate, and both long- and short-range ECG signals can be selected and used according to the index characteristics. In this research, because the short-range HRV signal is analyzed, the statistical analysis method is used to extract the eigenvalues from the RR interval sequence.


## 3.2.2. Extraction of Frequency-Domain Eigenvalues

Modern spectral calculations have been developed to solve the problem of low accuracy and large differences in classical spectral calculations [23]. From the spectral evaluation method, modern spectral evaluation can be divided into two types: parametric modeling and nonparametric modeling, of which parametric modeling is the basic model of modern spectral evaluation, AR model, MA model, and ARMA model. The idea of the parametric model method is to build a similar model of the actual signal based on the prior knowledge of the process, and then use the known limited observations or the estimation of its limited autocorrelation function to estimate the parameters of the model, and finally calculate the power spectrum of the model. The parametric model spectral estimation method has no windowing process, which avoids the problems caused by windowing in the classical spectral estimation, and has better frequency resolution and stability, but it also has some problems, such as the difficulty of determining the order of the AR model and poor trough tracking.The LS periodogram is based on the periodogram method of classical spectrum estimation. It cannot directly analyze the spectrum of nonuniformly sampled signals. The degree of fitting is such that the Fourier transform can be equivalently applied to signals that are sampled at unequal intervals. In this research, the LS periodogram is used to obtain the power spectrum of HRV, and the frequency domain features of HRV are extracted. The power density spectrum is shown in Figure4.Figure 4
HRV power density spectrum of Lomb–Scargle method.Physiological studies have found that the power spectral line of HRV in normal people’s calm state is mainly at 0–0.4 Hz, mainly including three spectral components, high-frequency component (HF, spectral peak around 0.25 Hz), low-frequency component (LF, spectral peak around 0.1 Hz), and the “1/f component” where the power spectral density increases with decreasing frequency extending to very low frequencies [24].


## 3.3. Pressure Recognition Model for HRV

The human brain is very complex and usually consists of two segments: the central nervous system and the peripheral nervous system. The peripheral nervous system includes the autonomic nervous system (ANS) and the somatic nervous system, and ANS is particularly associated with negative emotions such as stress, anxiety, and depression. The activity of ANS is related to the body’s immune system: blood pressure, respiration, heart rate, body temperature, digestive, and endocrine systems. ANS itself consists of two segments, the sympathetic nervous system and the parasympathetic nervous system, which are responsible for developing a stress and relaxation response, as shown in Figure5.Figure 5
Hierarchical structure of the brain.


### 3.3.1. Pressure Identification Weight Analysis of HRV Eigenvalues

A total of 11 different functions of the features of HRV used to create high-quality models in this study are 5 time domains such as SDNN, RMSSD, SDSD, NN50, and PNN50; 4 hour domains such as VLF, LF, HF, and LF/HF; and 2 blast points for analysis such as VAI and VLI for nonlinear quantization properties. We will use random memory significance measurements to better understand the relationship between HRV characteristics and severity to determine the severity of HRV variables in psychiatric disorders. For the HRV training model, this study provides a measure of the value of the forest in the previous section and a stress-level measure of the model for calculating the weight of each HRV specialization in recreation and stress according to the report. In Figure6, the sum values of all the properties are up to 1.Figure 6
HRV feature weight in stress recognition.From the figure above, it can be seen from the HRV characteristics obtained in this study that LF and HF are more supportive of altitude detection. LF and HF are measures of human brain function. It can be seen that the human mind is affected by the autonomic nervous system. From the point of view of HRV analysis, frequency monitoring works best in the analytical corner of our article, and LF feature is the most important indicator of HRV to determine the characteristics of brain stress, observation time, and nonlinear distribution analysis. Closely, its nonlinear nature suggests that the VLI, which ranks second after frequency measurements, excludes the Poincare scatterplot, a measure of how much VLI is used in this document that can determine stress in the brain [25].


### 3.3.2. Model Recognition Effect Evaluation

In this study, the K-En yakın neighbor (KNN), logistics regression (LR) model, and random forest classification (RFC) model are used in most comparative studies to study the effect of random forest modeling on determining HRV stress status. The design features were modified 5 times according to the validation; that is, the data were randomly divided into 5 parts: 4 parts were taken according to the training, and 1 part was backed up according to the test set to experiment. We use the model to determine stress and low stress, stress and moderate states, and stress and anxiety states, each of which determines the accuracy of our model through ROC curves and 20 cross-validation tests based on performance measurements and standards. The ROC curves and AUC values of the three stress difference models are shown in Figure7, and the diagonal dashed line shows the results of the assumptions. Assuming, the AUC is 0.5.Figure 7
ROC curves of models KNN, LR, and RFC to identify relaxation and low-stress states.The closer the ROC curve is to the upper left, the greater the space at its lower point, the better the structural performance, the closer the dashed diagonal, and the closer the AUC is to the standard performance. In the analysis of the rest and low-pressure conditions from Figure8, the AUCs of KNN, LR, and RFC were 0.62, 075, and 0.78, respectively, and the performance of the LR and RFC models was similar, while the performance of KNN was also high. All the benefits of our model are negative, which is poor. In AUC, the AUCs of KNN, LR, and RFC are 0.72, 0.90, and 095, respectively, to determine the average voltage. Meanwhile, RFC is better recognized, LR is slightly reduced, and KNN’s performance recognition remains poor. Figure 9. In the analysis of relaxation and stress conditions, the AUCs of KNN, LR, and RFC were 0.88, 0.96, and 0.96, respectively. During this time, all three models gained excellent experience. As the level increases, the performance of our model increases in the sense that it is higher. RFC and LR are more effective than KNN.Figure 8
ROC curves of models KNN, LR, and RFC to identify relaxation and moderate stress states.Figure 9
ROC curves of models KNN, LR, and RFC to identify relaxation and high-stress states.Table2 describes the weaknesses and accuracy of our model for determining stress and low stress states, stress and moderate states, and stress states and levels.Table 2
Classification results of three classifiers in relaxation and different stress states.
StateClassifierMain parameterAccuracyRelaxed/low-pressure stateKNNK = 759.38LRpenalty = ′12′, tol = 0.000174.43RFCTree_nums = 1000, Mtry = 472.35Relaxed/medium-pressure stateKNNK = 763.46LRPenalty = ′12′, tol = 0.000188.94RFCTree_nums = 1000, Mtry = 490.03Relaxed/high-pressure stateKNNK = 778.51LRPenalty = ′12′, tol = 0.000192.45RFCTree_nums = 1000, Mtry = 489.88In Table2, the exceptions of the three models were corrected by cross-validation five times. K in KNN represents the number of closest people, the LR penalty represents the use of the l2 restriction, and tol = 0.0001 is an exception in the case of dropout. The parameter Tree_nums = 1000 in RFC represents the number of metaclassifiers in the random memory, and Mtry = 4 represents the number of subset of functions selected at random. Figure 10 compares our class acceptance factor (ACC) for rest and stress fluctuations.Figure 10
Comparison of classification accuracy of three classifiers under relaxation and different stress states.Figure10 shows that the recognition accuracy of the three models in identifying relaxation and different stress states is consistent with the ROC curve and AUC performance. When in a lower stress state, the recognition accuracy of the three models is lower. Model LR and RFC identification are only good when the pressure state reaches medium-intensity pressure and above. Comparing the recognition accuracy of the three models at the same time, it is found that KNN has a lower accuracy than the other two models in identifying relaxation and different psychological pressures, while the accuracy of LR and RFC is close, and RFC is slightly better than LR.Aiming at the stress identification problem of HRV, this research adopts the random forest classification algorithm to establish a stress identification model based on random forest and discusses the construction process of the HRV stress model and the calculation method of the HRV feature weight in the identification model in detail. Experimental results show that changes in psychological stress state can be identified by HRV, and the LF and HF extracted by frequency domain analysis are the main characteristics of HRV to identify psychological stress, and the characteristic value of HRV is more sensitive when the pressure is larger. At the same time, through the comparative experiment of three classifiers, it is found that when the HRV is used to identify psychological stress states, RFC and LR have better recognition effects than KNN, and the recognition effect is similar. When the degree of stress is high, the random forest model has a better recognition performance as a whole, reaching a recognition rate of about 90%.Because psychological stress is closely related to individual’s physical and mental health and quality of life, research on automatic identification of psychological stress is of great significance. Biosignal HRV is a common assessment for detecting and identifying psychological stress, it is able to react to the state of psychological stress without subjective consciousness, and current physiological mechanisms and studies of HRV to identify psychological stress have shown that HRV is associated with psychological stress. The purpose of this research is to automatically identify different levels of psychological stress by biological signal HRV and use video games to induce relaxation and low, medium, and high psychological stress. HRV is obtained by collecting ECG signals, and time domain and frequency domain are extracted from HRV.


## 3.3.1. Pressure Identification Weight Analysis of HRV Eigenvalues

A total of 11 different functions of the features of HRV used to create high-quality models in this study are 5 time domains such as SDNN, RMSSD, SDSD, NN50, and PNN50; 4 hour domains such as VLF, LF, HF, and LF/HF; and 2 blast points for analysis such as VAI and VLI for nonlinear quantization properties. We will use random memory significance measurements to better understand the relationship between HRV characteristics and severity to determine the severity of HRV variables in psychiatric disorders. For the HRV training model, this study provides a measure of the value of the forest in the previous section and a stress-level measure of the model for calculating the weight of each HRV specialization in recreation and stress according to the report. In Figure6, the sum values of all the properties are up to 1.Figure 6
HRV feature weight in stress recognition.From the figure above, it can be seen from the HRV characteristics obtained in this study that LF and HF are more supportive of altitude detection. LF and HF are measures of human brain function. It can be seen that the human mind is affected by the autonomic nervous system. From the point of view of HRV analysis, frequency monitoring works best in the analytical corner of our article, and LF feature is the most important indicator of HRV to determine the characteristics of brain stress, observation time, and nonlinear distribution analysis. Closely, its nonlinear nature suggests that the VLI, which ranks second after frequency measurements, excludes the Poincare scatterplot, a measure of how much VLI is used in this document that can determine stress in the brain [25].


## 3.3.2. Model Recognition Effect Evaluation

In this study, the K-En yakın neighbor (KNN), logistics regression (LR) model, and random forest classification (RFC) model are used in most comparative studies to study the effect of random forest modeling on determining HRV stress status. The design features were modified 5 times according to the validation; that is, the data were randomly divided into 5 parts: 4 parts were taken according to the training, and 1 part was backed up according to the test set to experiment. We use the model to determine stress and low stress, stress and moderate states, and stress and anxiety states, each of which determines the accuracy of our model through ROC curves and 20 cross-validation tests based on performance measurements and standards. The ROC curves and AUC values of the three stress difference models are shown in Figure7, and the diagonal dashed line shows the results of the assumptions. Assuming, the AUC is 0.5.Figure 7
ROC curves of models KNN, LR, and RFC to identify relaxation and low-stress states.The closer the ROC curve is to the upper left, the greater the space at its lower point, the better the structural performance, the closer the dashed diagonal, and the closer the AUC is to the standard performance. In the analysis of the rest and low-pressure conditions from Figure8, the AUCs of KNN, LR, and RFC were 0.62, 075, and 0.78, respectively, and the performance of the LR and RFC models was similar, while the performance of KNN was also high. All the benefits of our model are negative, which is poor. In AUC, the AUCs of KNN, LR, and RFC are 0.72, 0.90, and 095, respectively, to determine the average voltage. Meanwhile, RFC is better recognized, LR is slightly reduced, and KNN’s performance recognition remains poor. Figure 9. In the analysis of relaxation and stress conditions, the AUCs of KNN, LR, and RFC were 0.88, 0.96, and 0.96, respectively. During this time, all three models gained excellent experience. As the level increases, the performance of our model increases in the sense that it is higher. RFC and LR are more effective than KNN.Figure 8
ROC curves of models KNN, LR, and RFC to identify relaxation and moderate stress states.Figure 9
ROC curves of models KNN, LR, and RFC to identify relaxation and high-stress states.Table2 describes the weaknesses and accuracy of our model for determining stress and low stress states, stress and moderate states, and stress states and levels.Table 2
Classification results of three classifiers in relaxation and different stress states.
StateClassifierMain parameterAccuracyRelaxed/low-pressure stateKNNK = 759.38LRpenalty = ′12′, tol = 0.000174.43RFCTree_nums = 1000, Mtry = 472.35Relaxed/medium-pressure stateKNNK = 763.46LRPenalty = ′12′, tol = 0.000188.94RFCTree_nums = 1000, Mtry = 490.03Relaxed/high-pressure stateKNNK = 778.51LRPenalty = ′12′, tol = 0.000192.45RFCTree_nums = 1000, Mtry = 489.88In Table2, the exceptions of the three models were corrected by cross-validation five times. K in KNN represents the number of closest people, the LR penalty represents the use of the l2 restriction, and tol = 0.0001 is an exception in the case of dropout. The parameter Tree_nums = 1000 in RFC represents the number of metaclassifiers in the random memory, and Mtry = 4 represents the number of subset of functions selected at random. Figure 10 compares our class acceptance factor (ACC) for rest and stress fluctuations.Figure 10
Comparison of classification accuracy of three classifiers under relaxation and different stress states.Figure10 shows that the recognition accuracy of the three models in identifying relaxation and different stress states is consistent with the ROC curve and AUC performance. When in a lower stress state, the recognition accuracy of the three models is lower. Model LR and RFC identification are only good when the pressure state reaches medium-intensity pressure and above. Comparing the recognition accuracy of the three models at the same time, it is found that KNN has a lower accuracy than the other two models in identifying relaxation and different psychological pressures, while the accuracy of LR and RFC is close, and RFC is slightly better than LR.Aiming at the stress identification problem of HRV, this research adopts the random forest classification algorithm to establish a stress identification model based on random forest and discusses the construction process of the HRV stress model and the calculation method of the HRV feature weight in the identification model in detail. Experimental results show that changes in psychological stress state can be identified by HRV, and the LF and HF extracted by frequency domain analysis are the main characteristics of HRV to identify psychological stress, and the characteristic value of HRV is more sensitive when the pressure is larger. At the same time, through the comparative experiment of three classifiers, it is found that when the HRV is used to identify psychological stress states, RFC and LR have better recognition effects than KNN, and the recognition effect is similar. When the degree of stress is high, the random forest model has a better recognition performance as a whole, reaching a recognition rate of about 90%.Because psychological stress is closely related to individual’s physical and mental health and quality of life, research on automatic identification of psychological stress is of great significance. Biosignal HRV is a common assessment for detecting and identifying psychological stress, it is able to react to the state of psychological stress without subjective consciousness, and current physiological mechanisms and studies of HRV to identify psychological stress have shown that HRV is associated with psychological stress. The purpose of this research is to automatically identify different levels of psychological stress by biological signal HRV and use video games to induce relaxation and low, medium, and high psychological stress. HRV is obtained by collecting ECG signals, and time domain and frequency domain are extracted from HRV.


## 4. Conclusion

The RFC was used to identify the relaxation and different degrees of pressure and to evaluate the recognition effect of the model and the KNN and LR models. Through the experiments in this research, we get the following conclusions:(1)
The classification model of psychological stress can be established by using HRV signal to identify psychological stress, and the recognition effect is positively correlated with the degree of stress induction from the overall perspective of the identification results of KNN, LR, and RFC, and the sensitivity is high when the pressure is large.(2)
The LF and HF of the frequency domain analysis play a major role in the stress identification of HRV, while the Poincare scatter plot in the nonlinear analysis shows regular changes with the psychological pressure to a certain extent. When the psychological pressure changes from a relaxed to a high-pressure state, the Poincare scatter plot shows a trend from loose to aggregated.In the comparative test of the three models of KNN, LR, and RFC, we found that LR and RFC have better recognition performance than KNN model, and the identification results of LR and RFC are close, and the accuracy of RFC recognition is about 90% when the pressure is high.How to reliably and conveniently detect and identify the psychological stress of individuals in daily life has received more and more researchers’ attention, and it can be seen from the experimental conclusions of this paper that HRV can be used to identify psychological stress states and has obvious effects when identifying high-stress states. In real life, the early warning of high-stress states of the human body through HRV also has good feasibility and significant application value, so future research work will further focus on automatic and efficient identification of high stress states in daily life, mainly including the following points:Furthermore, we expand the training samples and improve the ECG signal database for psychological stress recognition. Expanding the training sample mainly starts from two aspects, one is to increase the overall number of samples, and the other is to increase the number of participants. The increase in the number of samples helps the classification model learn the data better, reduces overfitting, and reduces the generalization error of the model. Increasing the number of subjects is helpful for further analysis of individual differences in stress recognition due to differences in physiology and experience.



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*Source: 9993589-2022-07-14.xml*