CN112155514A - Non-contact intraocular pressure measuring method based on pulse bioelectricity detection - Google Patents

Non-contact intraocular pressure measuring method based on pulse bioelectricity detection Download PDF

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CN112155514A
CN112155514A CN202011098516.6A CN202011098516A CN112155514A CN 112155514 A CN112155514 A CN 112155514A CN 202011098516 A CN202011098516 A CN 202011098516A CN 112155514 A CN112155514 A CN 112155514A
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pulse
intraocular pressure
information
wave
follows
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康爱国
李广
姚紫娟
陈松
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Taiyuan University of Technology
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Taiyuan University of Technology
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/16—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for measuring intraocular pressure, e.g. tonometers
    • A61B3/165—Non-contacting tonometers
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/0205—Simultaneously evaluating both cardiovascular conditions and different types of body conditions, e.g. heart and respiratory condition
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7235—Details of waveform analysis
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B7/00—Instruments for auscultation
    • A61B7/02—Stethoscopes
    • A61B7/04—Electric stethoscopes
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06F—ELECTRIC DIGITAL DATA PROCESSING
    • G06F17/00—Digital computing or data processing equipment or methods, specially adapted for specific functions
    • G06F17/10—Complex mathematical operations

Abstract

The invention relates to a non-contact intraocular pressure measuring method based on pulse bioelectricity detection, belonging to the technical field of non-contact intraocular pressure measurement; the technical problem to be solved is as follows: an improvement of a non-contact tonometry method based on detecting pulse bioelectrical information is provided; the technical scheme for solving the technical problem is as follows: amplifying, filtering and carrying out analog-to-digital conversion on the acquired pulse, heart sound and electrocardio signals by using a pulse sensor, a heart sound sensor and an electrocardio sensor in the intraocular pressure measuring system, and transmitting the signals to an upper computer by Bluetooth to display waveforms; calculating corresponding pulse information and intraocular pressure information by using pulse information data processing algorithm program built in the upper computer, and using intraocular pressure measuring systemThe system measures and collects pulse information; establishing a multi-pulse information intraocular pressure model; measurement of actual intraocular pressure, IOP, by applanation tonometertModeling intraocular pressure data by combining pulse information measured by an intraocular pressure measuring system; the invention is applied to non-contact intraocular pressure measurement.

Description

Non-contact intraocular pressure measuring method based on pulse bioelectricity detection
Technical Field
The invention discloses a non-contact intraocular pressure measuring method based on pulse bioelectricity detection, and belongs to the technical field of non-contact intraocular pressure measurement.
Background
Intraocular pressure is an important parameter for diagnosing eye diseases and cardiovascular diseases, the traditional contact type intraocular pressure measurement is easy to cause problems of cross infection, corneal accidental injury and the like, and non-contact type intraocular pressure measurement has become a hot spot of research in the field in recent years; at present, the TX-20 tonometer developed by a Japan Canon company, the iCare HOME hand-held rebound tonometer developed by a Finland Aike company and the Soviet SW-500 tonometer developed in China are used for measurement, the tonometer does not need to be anesthetized by eyes and does not need to contact with the eyeball during measurement, but the tonometer needs to be placed at the eye position during measurement, the measurement is carried out in a manual control mode, the continuous measurement cannot be carried out, the measurement error is more than 3mmHg, and the measurement mode and the measurement precision are required to be improved.
Disclosure of Invention
In order to overcome the defects in the prior art, the invention aims to solve the technical problems that: an improvement of a non-contact tonometric measurement method based on detecting pulse bioelectrical information is provided.
In order to solve the technical problems, the invention adopts the technical scheme that: a non-contact intraocular pressure measuring method based on pulse bioelectricity detection comprises the following steps:
the method comprises the following steps: amplifying, filtering and carrying out analog-to-digital conversion on the acquired pulse, heart sound and electrocardio signals by using a pulse sensor, a heart sound sensor and an electrocardio sensor in the intraocular pressure measuring system, and transmitting the signals to an upper computer by Bluetooth to display waveforms;
step two: calculating corresponding pulse information and intraocular pressure information by using a pulse information data processing algorithm program built in the upper computer, and measuring and collecting the pulse information by using an intraocular pressure measuring system;
the pulse information measured and collected comprises pulse wave transmission time PTT, stroke volume Z, height h of main wave crest, height h of descending channel1And the height h of the heavy pulse wave2Relative height h of the descending gorges1/h, relative height of counterpulsation wave h2H, pulse wave waveform characteristic quantity K, pulse rate R and systolic wave area K1Diastolic waveform area K2Characteristic ratio of systolic and diastolic phases k1/k2The information parameters are obtained by calculation according to the characteristic points of the pulse waveform and each parameter;
the pulse wave transmission time PTT comprises PTTECGAnd PTTPCGThe PTTECGIs the time from the peak point of the L wave of the electrocardiogram signal (ECG) to the characteristic point of the corresponding periodic pulse, the PTTPCGIs a heart sound signal (PCG) S1The method for selecting the pulse characteristic point comprises the point P with the maximum slope of the main wave rising edge1Main wave median point P2And the maximum point P of the main wave crest3Wherein the main wave median point P2The calculated pulse wave transmission time PTT standard deviation as the pulse wave feature point is minimum, and the result is most stable;
the stroke volume Z represents the ejection volume of each beat of the heart, and influences the intraocular pressure by influencing the systolic pressure, and the calculation formula of the stroke volume Z is as follows:
Z＝h*[t1/(T-t1)+1]；
wherein h is the height of the main wave crest of the pulse, and the unit is mmHg, t1Is the systolic time, T is the pulse period, in seconds;
the pulse waveform characteristic quantity K represents the elasticity of arterial blood vessels, peripheral resistance and blood viscosity, and the calculation formula of the pulse waveform characteristic quantity K is as follows:
K＝(Pm-Pd)/(Ps-Pd)；
in the formula PsAnd PdRespectively systolic and diastolic blood pressure in mmHg, PmMean arterial pressure;
the mean arterial pressure PmThe calculation formula of (2) is as follows:
Figure BDA0002724546640000021
wherein P (t) represents a function of the pulse with respect to t;
the systolic wave-shaped area K1The calculation formula of (2) is as follows:
K1＝(Pm1-Pd)/(Ps-Pd)；
in the formula Pm1Mean arterial pressure during systole;
the systolic mean arterial pressure Pm1The calculation formula of (2) is as follows:
Figure BDA0002724546640000022
in the formula t1The contraction period time is in seconds;
the diastolic waveform area K2The calculation formula of (2) is as follows:
K2＝(Pm2-Pd)/(Ps-Pd)；
in the formula Pm2Mean arterial pressure in diastole;
the diastolic mean arterial pressure Pm2The calculation formula of (2) is as follows:
Figure BDA0002724546640000023
in the formula t2Diastolic time in seconds;
the characteristic ratio k1/k2The calculation formula of (2) is as follows:
K1/K2＝(Pm1-Pd)/(Pm2-Pd)；
the pulse rate R is used for measuring the influence of the peripheral condition of the human body on the intraocular pressure, the ocular pressure is low when the pulse rate is small, the ocular pressure is high when the pulse rate is large, and the calculation formula of the pulse rate R is as follows:
R＝1/T；
wherein T is the pulse period;
step three: establishing a multi-pulse information intraocular pressure model;
the actual IOP of a plurality of testers standing and lying at different time intervals in one day is respectively measured by using a flattening tonometer and a tonometry systemtAnd pulse information, actual intraocular pressure (IOP)tMeasuring by a flattening tonometer, and modeling intraocular pressure data by combining pulse information measured by an intraocular pressure measuring system;
the pulse transmission time is calculated with heart sound signal as reference, multiple pulse wave information is measured by intraocular pressure measuring system, and actual intraocular pressure IOP at the same time is measured by tonometertFor multiple pulse wave information and IOPtAnd performing multiple regression analysis on the values to obtain a multiple pulse information intraocular pressure model.
In the process of establishing the multi-pulse information intraocular pressure model in the third step, calculating the correlation between the pulse information and the intraocular pressure through the pearson correlation coefficient in the measured pulse information, and extracting the pulse information with strong correlation with the intraocular pressure;
the calculation formula of the Pearson correlation coefficient r is as follows:
Figure BDA0002724546640000031
in the formula
Figure BDA0002724546640000032
In the formula, r represents a correlation coefficient between x and y, the value range is [ -1,1], the absolute value of the correlation coefficient is taken, and the closer to 1, the better the correlation is;
defining that the value range of more than or equal to | r | <0.7 is significant correlation, and more than or equal to | r | <1 of 0.7 is high correlation;
defining intraocular pressure, IOP, of each test subjecttIs y;
defining pulse wave transit time PTT of each testerPCGZ stroke volume, H/H stroke channel relative height, g/H pulse wave relative height, K pulse wave waveform characteristic quantity, R pulse rate, and K systolic waveform area1Diastolic waveform area k2Characteristic ratio k1/k2Is x;
substituting the above values into a calculation formula of the Pearson correlation coefficient r to obtain the IOPtThe value and the correlation coefficient of each pulse wave information, and the pulse wave information with strong correlation with the IOP is determined to be the pulse wave transmission time PTT according to the calculation resultPCGThe pulse output Z, the pulse wave waveform characteristic quantity K and the pulse rate R, wherein K and R are dimensionless;
then, an intraocular pressure model of the multi-pulse information is established according to the correlation characteristics of the multi-pulse electrical information and the intraocular pressure, the multi-element linear regression model selects the pulse information and the intraocular pressure with strong correlation calculated by the Pearson correlation coefficient as an independent variable and a dependent variable, and the calculation formula is as follows:
Y＝A+B1X1+B2X2+…+BKXK；
wherein Y is a dependent variable, X1，X2，…XKIs an independent variable, A is a constant term, B1，B2…BKIs a regression equation coefficient; IOP is represented by Yt，X1，X2，…XKRepresenting multiple pulse wave information, and determining IOP of each grouptThe value and the pulse information are respectively substituted into the above formula to calculate A and B1，B3…BKAnd finally obtaining the intraocular pressure model based on the multi-pulse information.
The pulse sensor type used in the intraocular pressure measuring system is HK2000B, the heart sound sensor type is HKY-06C, and the electrocardio sensor type is HKD-10L.
Compared with the prior art, the invention has the beneficial effects that: the invention provides an improved intraocular pressure non-contact measurement method, which adopts an intraocular pressure measurement system of pulse bioelectricity information, and calculates the average error of intraocular pressure to reach 1.3mmHg by establishing a multi-pulse information intraocular pressure model, so that the accuracy is higher compared with the existing detection instrument and detection method, and the intraocular pressure non-contact measurement method accords with the medical measurement standard; the detection model obtained by the method is applied to the system, non-contact measurement of intraocular pressure can be realized, the accuracy is high, the operation is simple, the repeatability is good, and intraocular pressure data can be continuously measured.
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The invention is further described below with reference to the accompanying drawings:
FIG. 1 is a diagram of a human body pulse waveform measured by an tonometry system according to the present invention;
FIG. 2 is a schematic diagram illustrating the calculation of the pulse wave transmission time PTT according to the present invention;
fig. 3 is a schematic diagram of the tonometric measurement system of the present invention.
Detailed Description
The invention utilizes the characteristics that pulse bioelectricity information can indirectly detect human physiological indexes and can be applied to intelligent medical equipment, establishes an intraocular pressure model based on pulse information, and provides a method for indirectly measuring intraocular pressure by means of the pulse information; in the measurement process, due to the fact that pulse information is numerous, the adopted calculation methods are different, the established intraocular pressure models are different, and difficulty is brought to accurate measurement of intraocular pressure, so that the establishment of the appropriate pulse information intraocular pressure model is of great significance to design of an accurate intraocular pressure measurement system.
The invention adopts a corresponding intraocular pressure measuring system to measure, obtains corresponding data of pulse information such as Pulse Transmission Time (PTT), stroke volume, pulse characteristic value, pulse rate and the like of people of different ages at different moments, performs fitting processing on the data, obtains a multi-pulse information intraocular pressure model, is applied to the system, and provides a new reliable method for intraocular pressure non-contact measurement.
The invention firstly measures and collects the pulse information, the pulse information comprises pulse wave transmission time PTT, stroke volume Z and relative height of the descending channel (h)1/h) and the relative height of the dicrotic wave (h)2H), pulse wave waveform characteristic quantity K, pulse rate R and systolic waveform area K1Diastolic waveform area k2Characteristic ratio k1/k2And the pulse waveform is obtained by calculation according to the characteristic points and various parameters of the pulse waveform. Using self-developed intraocular pressureThe waveform of the human body pulse measured by the measuring system is shown in fig. 1, wherein b is the starting point of the pulse wave; c is the main wave crest; d is the wave crest of the wave before the dicrotic pulse; e is the left ventricular diastolic starting point; f is the origin of the dicrotic wave; g is the maximum pressure point of the dicrotic wave; h. h is1、h2The wave crest height of the main wave, the height of the descending channel and the height of the dicrotic wave are respectively, and the quantities can directly participate in calculation in an upper computer.
The calculation method of each pulse information comprises the following steps:
pulse transit time PTT including PTTECGAnd PTTPCGTwo kinds. PTTECGIs the time from the peak point of the L wave of the electrocardio signal (ECG) to the characteristic point of the corresponding periodic pulse. PTTPCGIs a heart sound signal (PCG) S1To the corresponding periodic pulse feature point. The pulse characteristic point selection method comprises the point P with the maximum main wave rising edge slope1Main wave median point P2And the maximum point P of the main wave crest3. A large number of studies have shown that the median point P is2The calculated arrival pulse wave transmission time PTT standard deviation as the pulse wave feature point is the smallest and the result is the most stable, and the calculation schematic diagram is shown in FIG. 2.
Stroke volume Z represents the ejection volume of each beat of the heart, which affects the intraocular pressure by affecting the systolic pressure. The calculation formula is as follows:
Z＝h*[t1/(T-t1)+1] (2)
wherein h is the height of the main wave crest of the pulse, and the unit is mmHg. t is t1The systolic time, T, is the pulse period in seconds.
The pulse waveform characteristic quantity K represents elasticity of arterial blood vessels, peripheral resistance and blood viscosity, and is closely related to the level of intraocular pressure. The K value is calculated as:
K＝(Pm-Pd)/(Ps-Pd) (3)
wherein the mean arterial pressure is calculated by the formula:
Figure BDA0002724546640000051
p in formula (3)sAnd PdRespectively systolic pressure and diastolic pressure, which are expressed in mmHg and can be directly read from the ordinate of the pulse waveform.
In equation (4), P (t) represents the function of the pulse with respect to t.
Systolic wave area K1Diastolic waveform area K2And a characteristic ratio k1/k2The calculation formula of (a) is as follows,
K1＝(Pm1-Pd)/(Ps-Pd) (5)
wherein systolic mean arterial pressure:
Figure BDA0002724546640000052
t in equation (6)1The systolic time is given in seconds.
K2＝(Pm2-Pd)/(Ps-Pd) (7)
Mean arterial pressure in diastole
Figure BDA0002724546640000053
T in equation (8)2Diastolic time in seconds.
K1/K2＝(Pm1-Pd)/(Pm2-Pd) (9)
The pulse rate can measure the influence of the peripheral condition of the human body on the intraocular pressure, and the pulse rate is low when the pulse rate is small and high when the pulse rate is large, and the calculation formula is as follows:
R＝1/T (10)
the intraocular pressure measuring system used by the invention consists of an HK2000B pulse sensor, an HKY-06C heart sound sensor, an HKD-10L electrocardio sensor, a hardware circuit and upper computer software.
The hardware circuit comprises an amplifying and filtering circuit, an A/D conversion circuit, an STM32 minimum system, a Bluetooth module, a data storage chip, a key and a power supply circuit, and the upper computer software is compiled by LabVIEW. The connection structure block diagram of the system is shown in FIG. 3;
intraocular pressure measurement system workflow: the pulse, electrocardio and heart sound signals collected by the pulse, electrocardio and heart sound sensors are amplified, filtered and subjected to analog-to-digital conversion, then the signals are transmitted to an upper computer by Bluetooth to display waveforms, and pulse information and intraocular pressure are calculated in the upper computer by using a pulse information calculation formula and an intraocular pressure model formula written in the upper computer.
The upper computer of the system comprises a waveform display window and a pulse information and intraocular pressure display window, and data can be directly read from the waveform display window and the pulse information and intraocular pressure display window.
In the embodiment of the invention, when a multi-pulse information intraocular pressure model is established, 40 testers, half of men and women, which are 20-40 years old, 10 of the testers have higher blood pressure and 10 of the testers have lower blood pressure, and the actual intraocular pressure IOP (intraocular pressure) of each tester standing and lying at 5, 7, 10, 14 and 18 times in one day is measured by using a flattening tonometer and a tonometry systemtAnd pulse information. Actual intraocular pressure (IOP)tMeasured by a Goldmann applanation tonometer, modeled with the pulse information measured by the system.
The Goldmann applanation tonometer used in the invention carries out indirect intraocular pressure measurement by applanating the cornea with a pressure measuring head, the diameter is 3.06mm, the instrument structure is stable, the measurement value is reliable, the error of the tonometer is only +/-0.5 mmHg, and the measurement standard is high.
The pulse transmission time is calculated by taking the heart sound signal as reference, multiple pulse wave information is measured by an intraocular pressure measuring system, and the actual intraocular pressure IOP at the same moment is measured by a Goldmann tonometertFor multiple pulse wave information and IOPtAnd performing multiple regression analysis to obtain a multiple pulse information intraocular pressure model.
And establishing a multi-pulse information intraocular pressure model, and extracting pulse information with strong correlation with intraocular pressure from the measured pulse information. The correlation between the pulse information and the intraocular pressure is calculated through the Pearson correlation coefficient.
The calculation formula of the Pearson correlation coefficient r is as follows:
Figure BDA0002724546640000061
in the formula
Figure BDA0002724546640000062
Wherein r represents the correlation coefficient between x and y, and has a value range of [ -1,1 [)]The correlation coefficient is taken as an absolute value, and the closer to 1, the better the correlation. Normally having a value in the range of 0.4 ≦ r<0.7 is significant correlation, and | r ≦ 0.7 is non-counting<1 is highly correlated. At intraocular pressure IOP of each test subjecttY, pulse wave transit time PTTPCGZ stroke volume, H/H stroke channel relative height, g/H pulse wave relative height, K pulse wave waveform characteristic quantity, R pulse rate, and K systolic waveform area1Diastolic waveform area k2Characteristic ratio k1/k2To IOP of x, substituting into equation (13)tAnd a correlation coefficient of each pulse wave information. The pulse wave information which is proved to have strong correlation with the IOP by the calculation result is the pulse wave transmission time PTTPCGThe pulse wave waveform characteristic quantity K and the pulse rate R, wherein K and R are dimensionless. The correlation coefficients were 0.901, 0.806, 0.881, 0.84, respectively. Measuring multi-pulse information and IOPtAs shown in table 1:
Figure BDA0002724546640000071
TABLE 1 Multi-pulse information and actual intraocular pressure value (IOP)t)
And establishing an intraocular pressure model of the multi-pulse information according to the relevant characteristics of the multi-pulse electrical information and intraocular pressure. The multivariate linear regression model selects pulse information and intraocular pressure with strong correlation calculated by the correlation coefficient of the Pearson as independent variable and dependent variable, and the calculation formula is as follows:
Y＝A+B1X1+B2X2+…+BKXK (15)
wherein Y is a dependent variable, X1，X2，…XKIs an independent variable, A is a constant term, B1，B2…BKFor regression equation coefficients, IOP is expressed in terms of Yt，X1，X2，…XKRepresenting multiple pulse wave information, and determining IOP of each grouptSubstituting the pulse information into the formula (15), calculating A and B1，B3…BKAnd obtaining an intraocular pressure model based on the multi-pulse information as follows:
IOPt＝103.317-121.977×PTTPCG-0.427×Z-70.832×K+5.193×R (16)
in order to verify the validity of the obtained intraocular pressure model and obtain the intraocular pressure model with the highest measurement accuracy, the three intraocular pressure models of the multi-pulse information intraocular pressure model are input into an upper computer, the intraocular pressure IOP and the pulse bioelectricity information of the 40 testers are measured again by using a measurement system, and the actual intraocular pressure IOP at the same moment is measured by using a Goldmann tonometert. And the error is calculated and analyzed, and the calculation error data is shown in table 2:
Figure BDA0002724546640000081
TABLE 2 error between measured intraocular pressure and actual intraocular pressure
It should be noted that, regarding the specific structure of the present invention, the connection relationship between the modules adopted in the present invention is determined and can be realized, except for the specific description in the embodiment, the specific connection relationship can bring the corresponding technical effect, and the technical problem proposed by the present invention is solved on the premise of not depending on the execution of the corresponding software program.
Finally, it should be noted that: the above embodiments are only used to illustrate the technical solution of the present invention, and not to limit the same; while the invention has been described in detail and with reference to the foregoing embodiments, it will be understood by those skilled in the art that: the technical solutions described in the foregoing embodiments may still be modified, or some or all of the technical features may be equivalently replaced; and the modifications or the substitutions do not make the essence of the corresponding technical solutions depart from the scope of the technical solutions of the embodiments of the present invention.

Claims (3)

1. A non-contact intraocular pressure measuring method based on pulse bioelectricity detection is characterized in that: the method comprises the following steps:
the method comprises the following steps: amplifying, filtering and carrying out analog-to-digital conversion on the acquired pulse, heart sound and electrocardio signals by using a pulse sensor, a heart sound sensor and an electrocardio sensor in the intraocular pressure measuring system, and transmitting the signals to an upper computer by Bluetooth to display waveforms;
step two: calculating corresponding pulse information and intraocular pressure information by using a pulse information data processing algorithm program built in the upper computer, and measuring and collecting the pulse information by using an intraocular pressure measuring system;
the pulse information measured and collected comprises pulse wave transmission time PTT, stroke volume Z, height h of main wave crest, height h of descending channel1And the height h of the heavy pulse wave2Relative height h of the descending gorges1/h, relative height of counterpulsation wave h2H, pulse wave waveform characteristic quantity K, pulse rate R and systolic wave area K1Diastolic waveform area K2Characteristic ratio of systolic and diastolic phases k1/k2The information parameters are obtained by calculation according to the characteristic points of the pulse waveform and each parameter;
the pulse wave transmission time PTT comprises PTTECGAnd PTTPCGThe PTTECGIs the time from the peak point of the L wave of the electrocardiogram signal (ECG) to the characteristic point of the corresponding periodic pulse, the PTTPCGIs a heart sound signal (PCG) S1The method for selecting the pulse characteristic point comprises the point P with the maximum slope of the main wave rising edge1Main wave median point P2And the most dominant wave peakLarge value point P3Wherein the main wave median point P2The calculated pulse wave transmission time PTT standard deviation as the pulse wave feature point is minimum, and the result is most stable;
the stroke volume Z represents the ejection volume of each beat of the heart, and influences the intraocular pressure by influencing the systolic pressure, and the calculation formula of the stroke volume Z is as follows:
Z＝h*[t1/(T-t1)+1]；
wherein h is the height of the main wave crest of the pulse, and the unit is mmHg, t1Is the systolic time, T is the pulse period, in seconds; the pulse waveform characteristic quantity K represents the elasticity of arterial blood vessels, peripheral resistance and blood viscosity, and the calculation formula of the pulse waveform characteristic quantity K is as follows:
K＝(Pm-Pd)/(Ps-Pd)；
in the formula PsAnd PdRespectively systolic and diastolic blood pressure in mmHg, PmMean arterial pressure;
the mean arterial pressure PmThe calculation formula of (2) is as follows:
Figure FDA0002724546630000011
wherein P (t) represents a function of the pulse with respect to t;
the systolic wave-shaped area K1The calculation formula of (2) is as follows:
K1＝(Pm1-Pd)/(Ps-Pd)；
in the formula Pm1Mean arterial pressure during systole;
the systolic mean arterial pressure Pm1The calculation formula of (2) is as follows:
Figure FDA0002724546630000021
in the formula t1The contraction period time is in seconds;
the diastolic waveform area K2The calculation formula of (2) is as follows:
K2＝(Pm2-Pd)/(Ps-Pd)；
in the formula Pm2Mean arterial pressure in diastole;
the diastolic mean arterial pressure Pm2The calculation formula of (2) is as follows:
Figure FDA0002724546630000022
in the formula t2Diastolic time in seconds;
the characteristic ratio k1/k2The calculation formula of (2) is as follows:
K1/K2＝(Pm1-Pd)/(Pm2-Pd)；
the pulse rate R is used for measuring the influence of the peripheral condition of the human body on the intraocular pressure, the ocular pressure is low when the pulse rate is small, the ocular pressure is high when the pulse rate is large, and the calculation formula of the pulse rate R is as follows:
R＝1/T；
wherein T is the pulse period;
step three: establishing a multi-pulse information intraocular pressure model;
the actual IOP of a plurality of testers standing and lying at different time intervals in one day is respectively measured by using a flattening tonometer and a tonometry systemtAnd pulse information, actual intraocular pressure (IOP)tMeasuring by a flattening tonometer, and modeling intraocular pressure data by combining pulse information measured by an intraocular pressure measuring system;
the pulse transmission time is calculated with heart sound signal as reference, multiple pulse wave information is measured by intraocular pressure measuring system, and actual intraocular pressure IOP at the same time is measured by tonometertFor multiple pulse wave information and IOPtAnd performing multiple regression analysis on the values to obtain a multiple pulse information intraocular pressure model.
2. The non-contact tonometric measurement method based on detecting pulse bioelectrical information according to claim 1, characterized in that: in the process of establishing the multi-pulse information intraocular pressure model in the third step, calculating the correlation between the pulse information and the intraocular pressure through the pearson correlation coefficient in the measured pulse information, and extracting the pulse information with strong correlation with the intraocular pressure;
the calculation formula of the Pearson correlation coefficient r is as follows:
Figure FDA0002724546630000023
in the formula
Figure FDA0002724546630000031
In the formula, r represents a correlation coefficient between x and y, the value range is [ -1,1], the absolute value of the correlation coefficient is taken, and the closer to 1, the better the correlation is;
defining that the value range of more than or equal to | r | <0.7 is significant correlation, and more than or equal to | r | <1 of 0.7 is high correlation;
defining intraocular pressure, IOP, of each test subjecttIs y;
defining pulse wave transit time PTT of each testerPCGZ stroke volume, H/H stroke channel relative height, g/H pulse wave relative height, K pulse wave waveform characteristic quantity, R pulse rate, and K systolic waveform area1Diastolic waveform area k2Characteristic ratio k1/k2Is x;
substituting the above values into a calculation formula of the Pearson correlation coefficient r to obtain the IOPtThe value and the correlation coefficient of each pulse wave information, and the pulse wave information with strong correlation with the IOP is determined to be the pulse wave transmission time PTT according to the calculation resultPCGThe pulse output Z, the pulse wave waveform characteristic quantity K and the pulse rate R, wherein K and R are dimensionless;
then, an intraocular pressure model of the multi-pulse information is established according to the correlation characteristics of the multi-pulse electrical information and the intraocular pressure, the multi-element linear regression model selects the pulse information and the intraocular pressure with strong correlation calculated by the Pearson correlation coefficient as an independent variable and a dependent variable, and the calculation formula is as follows:
Y＝A+B1X1+B2X2+…+BKXK；
wherein Y is a dependent variable, X1，X2，…XKIs an independent variable, A is a constant term, B1，B2…BKIs a regression equation coefficient; IOP is represented by Yt，X1，X2，…XKRepresenting multiple pulse wave information, and determining IOP of each grouptThe value and the pulse information are respectively substituted into the above formula to calculate A and B1，B3…BKAnd finally obtaining the intraocular pressure model based on the multi-pulse information.
3. The non-contact tonometric measurement method based on detecting pulse bioelectrical information according to claim 2, characterized in that: the pulse sensor type used in the intraocular pressure measuring system is HK2000B, the heart sound sensor type is HKY-06C, and the electrocardio sensor type is HKD-10L.
CN202011098516.6A 2020-10-14 2020-10-14 Non-contact intraocular pressure measuring method based on pulse bioelectricity detection Pending CN112155514A (en)

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