Disclosure of Invention
This section is intended to outline some aspects of embodiments of the application and to briefly introduce some preferred embodiments. Some simplifications or omissions may be made in this section as well as in the description of the application and in the title of the application, which may not be used to limit the scope of the application.
The present invention has been made in view of the above-mentioned problems with existing electrocardiograph alarm systems.
Therefore, the invention solves the technical problems that the existing electrocardiograph monitor alarm system cannot adapt to the personalized requirements of different patients and different conditions and the alarm accuracy is to be improved.
The quick alarm method for the electrocardiograph monitor comprises the following steps of S1, acquiring electrocardiograph signals of a patient through the electrocardiograph monitor to form an electrocardiograph signal diagram, S2, acquiring time domain features, amplitude features and waveform features in the electrocardiograph signal diagram, S3, constructing a waveform state display model based on the feature data acquired in S2, inputting all feature values, outputting waveform state display values, S4, acquiring the electrocardiograph signal diagram at uniform intervals in rated time to acquire a waveform state display curve in the rated time, S5, performing feature extraction on the waveform state display curve, constructing a waveform state alarm model, acquiring waveform state alarm values, and comparing set threshold values to finish electrocardiograph signal alarm.
The invention relates to a rapid alarm method of an electrocardiograph monitor, which is a preferable scheme, wherein the step S1 of collecting electrocardiograph signals further comprises preprocessing the collected electrocardiograph signals, and the preprocessing step specifically comprises denoising, normalization, cutting and segmentation, histogram equalization and feature extraction.
As a preferable scheme of the rapid alarm method of the electrocardiograph monitor, the time domain characteristics obtained in the S2 comprise RR intervals, QRS complex widths, P wave widths, T wave widths and QT intervals, the amplitude characteristics obtained in the S2 comprise R wave amplitudes, P wave amplitudes and T wave amplitudes, and the waveform characteristics obtained in the S2 comprise waveform slopes, areas of QRS complexes, areas of P waves and areas of T waves.
As a preferable scheme of the rapid alarm method of the electrocardiograph monitor, the invention comprises the following steps of:
Wherein δ is a waveform state display value, a is an RR interval, c is a QRS complex width, f is a QT interval, d is a P-wave width, g is a T-wave width, b is an R-wave amplitude, e is a P-wave amplitude, h is a T-wave amplitude, k is a waveform slope, SQRS is an area of QRS complex, SP is an area of P-wave, ST is an area of T-wave, 1.354, 3.91, -1.407, 2.6, -1.39, 2.573, and-1.43 are adjustment constants, and dx is integral operation.
The method for quickly alarming the electrocardiograph monitor comprises the following steps of obtaining waveform state display values in rated time, obtaining reference points by taking time sequence as an abscissa in a two-dimensional coordinate system and taking the waveform state display values as an ordinate in the two-dimensional coordinate system, and sequentially connecting the reference points by a smooth curve to form the waveform state display curve.
The characteristic extracted from the waveform state display curve specifically comprises a maximum slope of the curve, a minimum slope of the curve, a maximum value of the curve, a minimum value of the curve, a coordinate value of a contrast at the maximum slope of the curve and a coordinate value of a contrast at the minimum slope of the curve;
the built waveform state alarm model specifically comprises the following steps:
Wherein η is a waveform state alarm value, Kmin is a minimum slope of a curve, Kmax is a maximum slope of a curve, Ymax is a maximum value of a curve, Ymin is a minimum value of a curve, YKmin is a coordinate value of a contrast at the minimum slope of a curve, YKmax is a coordinate value of a contrast at the maximum slope of a curve, 1.01 and-0.58 are adjustment constants, and dx is an integral operation.
As a preferable scheme of the rapid alarm method of the electrocardiograph monitor, when the waveform state alarm value is higher than the threshold value, the current electrocardiograph signal is defined to be abnormal, and alarm is carried out.
As a preferable scheme of the rapid alarm method of the electrocardiograph monitor, the threshold value is optimally set to 0.86 or 0.864.
The invention has the beneficial effects that the quick alarm method of the electrocardiograph monitor has the advantages that the time domain characteristics, the amplitude characteristics and the waveform characteristics in an electrocardiograph image are acquired after electrocardiograph signals are acquired, a waveform state display model is constructed, after waveform state display values are output, a waveform state display curve in rated time is acquired, characteristic analysis is carried out on the curve, a waveform state alarm model is constructed, the waveform state alarm values are acquired, and the electrocardiograph signal alarm is completed by comparing the set threshold values. Compared with the traditional electrocardiograph alarm mode, the data processing method is higher in applicability, the obtained alarm is higher in accuracy, the applicability model adjustment can be carried out according to the conditions of different patients, and the problems that the existing electrocardiograph monitor alarm system cannot adapt to personalized requirements of different patients and under different conditions and the alarm accuracy is to be improved are solved.
Detailed Description
So that the manner in which the above recited objects, features and advantages of the present invention can be understood in detail, a more particular description of the invention, briefly summarized above, may be had by reference to the embodiments, some of which are illustrated in the appended drawings. All other embodiments, which can be made by one of ordinary skill in the art based on the embodiments of the present invention without making any inventive effort, shall fall within the scope of the present invention.
The alarm system of the existing electrocardiograph monitor is generally based on fixed threshold values and simple rules, cannot adapt to individual requirements of different patients and different conditions, and the alarm accuracy needs to be improved.
Therefore, referring to fig. 1, the present invention provides a rapid alarm method for an electrocardiograph monitor, which includes the following steps:
S1, electrocardiosignal acquisition, namely acquiring electrocardiosignals of a patient through an electrocardiograph monitor to form an electrocardiosignal graph;
s2, acquiring time domain features, amplitude features and waveform features in an electrocardiosignal graph;
S3, constructing a waveform state display model based on the characteristic data acquired in the S2, inputting each characteristic value and outputting a waveform state display value;
S4, uniformly and intermittently acquiring electrocardiosignal images in rated time to acquire a waveform state display curve in the rated time;
and S5, extracting characteristics of the waveform state display curve, constructing a waveform state alarm model, acquiring a waveform state alarm value, and comparing the waveform state alarm value with a set threshold value to finish electrocardiosignal alarm.
Specifically, the step S1 of preprocessing the collected electrocardiosignals after collecting the electrocardiosignals;
the preprocessing step comprises denoising, normalization, cutting and segmentation, histogram equalization and feature extraction.
It should be noted that the pretreatment steps are specifically as follows:
1. Denoising:
Filtering, namely removing high-frequency noise and low-frequency interference in the electrocardiosignal by using various filters (such as low-pass filtering, high-pass filtering and band-pass filtering).
Median filtering, which is particularly suitable for removing salt and pepper noise.
And (3) adaptive filtering, namely dynamically adjusting filtering parameters according to signal characteristics.
Specific:
low pass filtering Hlow（f）=1/（1+jf/fc);
high pass filtering Hhigh（f）=（jf/fc）/（1+jf/fc);
band-pass filtering, namely combining low-pass filtering and high-pass filtering, and only allowing signals in a specific frequency range to pass through;
2. Normalization:
the amplitude of the electrocardiographic signal is normalized to a certain fixed range to eliminate differences between different individuals.
Specific:
Linear normalization xnorm=（x-xmin）/（xmax-xmin), where xmin and xmax are the minimum and maximum of the signal, respectively;
3. cutting and segmenting:
the electrocardiographic signals are cut into individual heart cycles to facilitate subsequent feature extraction and analysis.
The starting point of the heart cycle is typically determined based on R-wave detection, and then the signal is cut according to RR intervals;
4. Histogram equalization:
enhancing the contrast of the signal by adjusting the histogram distribution of the electrocardiograph signal so that features are more prominent, such as adjusting the histogram with a Cumulative Distribution Function (CDF);
5. Feature extraction:
Key features such as R-wave position, QRS complex width, T-wave width, etc. are extracted from the preprocessed electrocardiograph signals.
And R wave detection, namely detecting the position of R waves in the electrocardiosignal.
QRS width calculation the width of the QRS complex is calculated, typically from the starting point of the R wave to the lowest point of the S wave.
And detecting the T wave, namely detecting the starting point and the end point of the T wave, and calculating the width of the T wave.
Further, the time domain features obtained in S2 specifically include RR interval, QRS complex width, P wave width, T wave width and QT interval;
the amplitude characteristics obtained in the step S2 specifically comprise R wave amplitude, P wave amplitude and T wave amplitude;
the waveform characteristics obtained in the step S2 specifically comprise waveform slope, the area of the QRS complex, the area of the P wave and the area of the T wave.
Specific:
Time domain features:
RR interval-the time interval between two consecutive R waves, reflects the rhythm of the heart beat.
QRS complex width, the time interval from the start of the Q wave to the end of the S wave, reflects the rate of ventricular depolarization.
P-wave width, the duration of the P-wave, reflects the rate of atrial depolarization.
T-wave width, the duration of the T-wave, reflects the velocity of ventricular repolarization.
The QT interval, the time interval from the start of the QRS complex to the end of the T wave, is the total time of ventricular depolarization and repolarization.
Amplitude characteristics:
R wave amplitude: the maximum amplitude of R wave.
P-wave amplitude, the maximum amplitude of P-wave.
T wave amplitude: maximum amplitude of T wave.
Waveform characteristics:
Waveform slope, which is the slope of the rising or falling of the waveform, can reflect the dynamic change of electrocardiosignals.
The waveform area is the area of the QRS complex, the P wave and the T wave, and can reflect the energy of electrocardiosignals.
Further, the constructed waveform state display model specifically comprises the following steps:
Wherein δ is a waveform state display value, a is an RR interval, c is a QRS complex width, f is a QT interval, d is a P-wave width, g is a T-wave width, b is an R-wave amplitude, e is a P-wave amplitude, h is a T-wave amplitude, k is a waveform slope, SQRS is an area of QRS complex, SP is an area of P-wave, ST is an area of T-wave, 1.354, 3.91, -1.407, 2.6, -1.39, 2.573, and-1.43 are adjustment constants, and dx is integral operation.
Still further, referring to fig. 2, the step of obtaining a waveform state display curve within a rated time specifically includes the following steps:
h1, acquiring each waveform state display value in rated time;
H2, in the two-dimensional coordinate system, taking time sequence as an abscissa and a waveform state display value as an ordinate, and acquiring each reference point;
and H3, sequentially connecting all the reference points by using a smooth curve to form a waveform state display curve.
Specifically, the characteristics extracted from the waveform state display curve comprise a maximum slope of the curve, a minimum slope of the curve, a maximum value of the curve, a minimum value of the curve, a coordinate value of a contrast at the maximum slope of the curve and a coordinate value of a contrast at the minimum slope of the curve;
the built waveform state alarm model specifically comprises the following steps:
Wherein η is a waveform state alarm value, Kmin is a minimum slope of a curve, Kmax is a maximum slope of a curve, Ymax is a maximum value of a curve, Ymin is a minimum value of a curve, YKmin is a coordinate value of a contrast at the minimum slope of a curve, YKmax is a coordinate value of a contrast at the maximum slope of a curve, 1.01 and-0.58 are adjustment constants, and dx is an integral operation.
Specifically, when the waveform state alarm value is higher than the threshold value, the current electrocardiosignal is defined to be abnormal, and alarm is carried out.
Further, the threshold optimization is set at 0.86 or 0.864.
In order to verify the technical effect of the present invention, the following simulation test was performed:
1. test preparation
A certain number of electrocardiographic monitors are selected as the test equipment.
Real electrocardiosignal data of patients with different ages and different health conditions are collected.
And determining the standard of the normal electrocardiosignals and the abnormal electrocardiosignals for subsequent data comparison.
2. Data acquisition
And an electrocardiograph monitor is used for collecting electrocardiograph signals of each patient in a quiet state, so that the accuracy and consistency of data are ensured.
Personal information, electrocardiosignal characteristics and known health conditions of each patient are recorded.
3. Data processing
According to the method of the invention, the characteristic extraction is carried out on the collected electrocardiosignal, which comprises the time domain characteristic, the amplitude characteristic and the waveform characteristic.
And outputting a waveform state display value by using the constructed waveform state display model.
And acquiring a waveform state display curve within a certain time, and performing characteristic analysis.
4. Alarm model construction
And constructing a waveform state alarm model according to the characteristic analysis result, and outputting a waveform state alarm value.
And setting a proper alarm threshold value.
5. Data analysis
And comparing the alarm value output by the alarm model with the actual health condition to evaluate the alarm accuracy.
And analyzing false alarm and missing alarm conditions.
6. Results recording
Recording test results, including alarm accuracy under normal and abnormal conditions.
Data validation table:
| Patient ID | Age of | Sex (sex) | Health condition | Characteristic value of electrocardiosignal | Alarm threshold | Actual condition | Alarm model output value | Alarm result | False alarm/missing alarm | Remarks |
| 1 | 45 | Man's body | Normal state | RR interval 800ms, QRS width 90 ms. | 0.86 | Normal state | 0.376 | Alarm is not given | No-missing report | / |
| 2 | 30 | Female | Coronary heart disease | RR interval 600ms, QRS width 110 ms. | 0.86 | Abnormality of | 0.910 | Alarm device | No-missing report | / |
| 3 | 55 | Female | Arrhythmia of heart | RR interval 620ms, QRS width 100 ms. | 0.86 | Abnormality of | 1.65 | Alarm device | No-missing report | / |
| 4 | 70 | Man's body | Hypertension of the type | RR interval 720ms, QRS width 95 ms. | 0.86 | Abnormality of | 1.033 | Alarm device | No-missing report | / |
Wherein RR interval (ms), QRS width (ms), P-wave width (ms), T-wave width (ms), QT interval (ms), R-wave amplitude (mV), P-wave amplitude (mV), T-wave amplitude (mV), waveform slope, QRS complex area (mv·ms), P-wave area (mv·ms), T-wave area (mv·ms).
Note that this column may contain any additional observations or special instructions, such as signal quality, patient position changes, drug effects, etc.
Description:
the "electrocardiosignal characteristic value" column in the table contains the electrocardiosignal key characteristic data of each patient.
The alarm model output value is an alarm value processed by the method and is used for being compared with an alarm threshold value to determine whether to trigger an alarm.
The "alarm results" column indicates whether the electrocardiograph has triggered an alarm correctly based on the model output values.
The "false alarm/missing alarm" column records the false alarm or missing alarm conditions occurring in the test, which is critical to the accuracy of the evaluation system.
The invention provides a rapid alarm method of an electrocardiograph monitor, which comprises the steps of acquiring time domain features, amplitude features and waveform features in an electrocardiograph image after acquiring electrocardiograph signals, constructing a waveform state display model, acquiring a waveform state display curve in rated time after outputting a waveform state display value, carrying out feature analysis on the curve, constructing a waveform state alarm model, acquiring a waveform state alarm value, comparing a set threshold value, and completing electrocardiograph signal alarm. Compared with the traditional electrocardiograph alarm mode, the data processing method is higher in applicability, the obtained alarm is higher in accuracy, the applicability model adjustment can be carried out according to the conditions of different patients, and the problems that the existing electrocardiograph monitor alarm system cannot adapt to personalized requirements of different patients and under different conditions and the alarm accuracy is to be improved are solved.
It should be noted that the above embodiments are only for illustrating the technical solution of the present invention and not for limiting the same, and although the present invention has been described in detail with reference to the preferred embodiments, it should be understood by those skilled in the art that the technical solution of the present invention may be modified or substituted without departing from the spirit and scope of the technical solution of the present invention, which is intended to be covered in the scope of the claims of the present invention.