CN100413464C - Method and apparatus for continuously measuring blood pressure - Google Patents
Method and apparatus for continuously measuring blood pressure Download PDFInfo
- Publication number
- CN100413464C CN100413464C CNB2006100815436A CN200610081543A CN100413464C CN 100413464 C CN100413464 C CN 100413464C CN B2006100815436 A CNB2006100815436 A CN B2006100815436A CN 200610081543 A CN200610081543 A CN 200610081543A CN 100413464 C CN100413464 C CN 100413464C
- Authority
- CN
- China
- Prior art keywords
- pulse wave
- time
- blood pressure
- pwtt
- translation time
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Fee Related
Links
Images
Abstract
The present invention relates to a method and a device for continuously measuring blood pressure, and the method comprises the steps that a regression equation between pulse wave translation time and arterial blood pressure is established for a person to be measured * BP=a+b*PWTT *; the intercept and a regression coefficient b of the person to be measured are determined by individuation correction technology. The method for continuously obtaining pulse wave translation time PWTT comprises the steps that pulse wave signals, electrocardiogram signals and cardiophonogram signals of a human body are synchronously collected to form pulse waves, an electrocardiogram and a cardiophonogram; a second component aortic valve closure component (A2) of second heart sound (S2) is used as a starting point, the time of a superior thyroid notch (In) of a pulse wave catacrotic limb (AU') is used as an end point in the same cardiac cycle, and the time difference of the starting point and the end point is calculated to be as the pulse wave translation time by the signal figures. The method has the advantage of simple operation, and furthermore, the accuracy for continuously measuring the blood pressure is enhanced. The present invention can be used for measuring the blood pressure of the head and synchronously obtains the relevant dynamic heart physiological parameters.
Description
Technical field
The invention belongs to the method and the device that obtain related data in a kind of human body artery blood pressure measurement, particularly human body is carried out obtaining in the measurement of noinvasive continuous blood pressure the method and the device of related data.
Background technology
Blood pressure measuring method generally can be divided into two big classes: have wound to measure and non-invasive measurement, the noinvasive method can be divided into two classes: batch (-type) and continous way.What batch (-type) recorded is at certain particular measurement pressure value constantly.Because each time point blood is in the equal earthquake of the pressure of ductus arteriosus wall in each heart beating and the every jumping, systolic pressure that the method is measured and diastolic pressure be the representational blood pressure of measured not necessarily, and is not with the numerical value in the heartbeat.Continous way can not have and measures blood pressure off and on, and it can provide whenever fight blood pressure or successive arterial pressure waveform.The continous way non-invasive blood pressure measuring method has tensammetry, constant volume method, pulse wave velocity method, multiparameter regression analysis, wherein the tool practicality of pulse wave velocity method (pulse wave translation time method).
As far back as nineteen twenty-two, promptly the someone finds that pulse wave conduction speed (PWTV) or conduction time (PWTT) are relevant with arteriotony, also relevant with the vessel wall elasticity amount with capacity of blood vessel; Nineteen fifty-seven, the someone proposes within the specific limits again, and is linear between PWTT and the arteriotony BP, and this pass ties up on one's body some bodies, is metastable in one period.Medically prove now: under certain condition, the variation relation between pulse wave translation time and the blood pressure is that the physiology goes up clear and definite phenomenon, under the gauged prerequisite of individuation, can characterize blood pressure by the measurement of pulse wave translation time.
Utilization is during said method, and people are according to the linear relationship that presents between pulse wave translation time PWTT and the arteriotony BP, for the measured sets up following PWTT and the regression equation between the arteriotony BP by shooting:
BP＝a+b*?PWTT ……(A)
Wherein BP is an arteriotony, PWTT is a pulse wave translation time, a and b are regression coefficient undetermined, a, the size of b varies with each individual, but same individuality is at short notice, this numerical value is determined, like this as long as each individuality has been determined the regression coefficient a and the b of its individuation can utilize the METHOD FOR CONTINUOUS DETERMINATION of pulse wave translation time PWTT (also can utilize pulse wave conduction speed PWTV) to estimate each individual successive arteriotony BP according to above-mentioned equation (A) by the individuation alignment technique.
Since the measurement of PWTT is more convenient and itself and blood pressure between variation relation also clear and definite, so the method that adopts PWTT to measure blood pressure is adopted at present widely, thereby become the strong means of noinvasive continuous monitoring blood pressure.
When implementing above-mentioned PWTT blood pressure continuous measurement method, for determining of regression coefficient a and b, existing multiple at present individuation is proofreaied and correct the method for determining; For obtaining of pulse wave translation time PWTT, generally adopt now with Electrocardiographic R crest value to time of the starting point u of the synperiodic pulse wave that records at the peripheral arterial place as pulse wave translation time, this is called as R ripple pulse wave translation time RWPWTT (referring to Fig. 1);
Because the peak value of ECG R wave itself can not be represented the moment of cardiac ejection, so the R ripple pulse wave translation time RWPWTT that obtains with said method also just can not the authentic representative pulse wave propagates into the time of peripheral arterial from heart, in fact, above-mentioned R ripple pulse wave translation time RWPWTT has also comprised heart contraction beginning phase RWPIT and isovolumic contraction period ICT (referring to Fig. 2), if these two kinds of compositions are constants, they can not exert an influence to final result so, but if variable, then they will inevitably influence the accurate sign of pulse wave translation time RWPWTT to blood pressure.Discover through the applicant: there is variability with isovolumic contraction period (ICT) in the R ripple heart contraction beginning phase (RWPIT) of above-mentioned RWPWTT time in forming under different condition, this certainly will cause the inaccuracy of measuring the blood pressure method with R ripple pulse wave translation time.
Particularly if adopt the pulse wave translation time RWPWTT of said method to characterize the head blood pressure, because breast-head distance is short, conduction time is short, more can influence its accuracy, the head blood pressure had both reflected the brain blood supply situation, the adjusting of cardiac autonomic nervous when also embodying the head blood pressure, the continuous monitoring of head blood pressure is significant in Military Application field such as Aeronautics and Astronautics and clinical position, and existing R ripple pulse wave translation time RWPWTT measures the method for blood pressure can't be used for the head blood pressure because of its inaccuracy continuous monitoring.
Cardiac function and blood pressure are closely related in addition, in continuous blood pressure measuring, obtain relevant dynamic heart physiological parameter synchronously, for researchs such as further accurately analyzing the blood pressure reason important and practical meanings are arranged.
Summary of the invention
The technical problem to be solved in the present invention provides a kind of not only easy to operate but also can improve the acquisition methods and the device of the pulse wave translation time in the arteriotony continuous measurement of measurement accuracy.
The technical problem that the present invention further will solve provides a kind of acquisition methods and device that can obtain the pulse wave translation time in the arteriotony continuous measurement of the dynamic heart physiological parameter relevant with blood pressure simultaneously.
The method that solves the problems of the technologies described above comprises following content:
One sets up pulse wave translation time and the regression equation between the arteriotony by shooting for the measured:
BP＝a+b*PWTT
BP is an arteriotony in the formula, and PWTT is a pulse wave translation time, and a and b are regression coefficient;
One usefulness individuation alignment technique is determined measured's regression coefficient a and b;
One obtains measured's pulse wave translation time PWTT continuously;
It is characterized in that the method for the described measured's of obtaining pulse wave translation time PWTT is:
One gathers pulsation ripple, electrocardio, the cardiechema signals of human body synchronously, forms synchronous pulsation ripple, electrocardio and phonocardiogram;
-by above-mentioned three kinds of signal graphs, in same cardiac cycle, the second composition aortic valve closing composition A2 point with second heart sound S2 is made starting point, makes terminal point with the moment that catacrotic limb Au ' superior thyroid notch In occurs, and the time difference of calculating the two is a pulsation ripple conduction time.
The device that solves the problems of the technologies described above is:
Be provided with EGC sensor, pulse wave sensor, described EGC sensor is connected with the computer data processor input that is provided with display screen by modulate circuit respectively with pulse wave sensor, it is characterized in that: also be provided with heart sound transducer, heart sound transducer is connected with described computer data processor input by modulate circuit.。
The method that the further scheme of the present invention is obtained pulse wave translation time comprises one of following two parts content at least:
-in same cardiac cycle, obtain the R ripple to time of the MC composition M1 (first high amplitude, radio-frequency component) of first heart sound S1 be the phase (RWPIT) heart contraction beginning;
-in same cardiac cycle, use the time of the MC composition M1 of first heart sound S1 to the second composition aortic valve closing composition A2 of second heart sound S2, deduct the heart isovolumic contraction period ICT that left ventricular ejection time LVET obtains; Described left ventricular ejection time LVET is meant that left ventricle begins to penetrate blood (opening of aortic valve) to the time of penetrating blood agglomeration bundle (aortic valve closing), specifically is to get pulse wave starting point U to go out spacing between now to incisura point In.
Below the inventive method is further described; in each cardiac cycle; along with the contraction of cardiac muscle and diastole, the opening and closing of valve, the generation and the transmission of blood eddy current; some particular moment that can be in cardiac cycle; use stethoscope and be placed on some auscultation position of thoracic wall, can obtain the normal or abnormal sound of heart.If application sensors changes these mechanical vibration into current signal, after amplifying the record curve, be called phonocardiogram (phonocardiogram, PCG).
Referring to Fig. 3, four hear sounds should appear in each cardiac cycle, and first, second, third and fourth hear sounds is expressed as S1, S2, S3, S4 respectively;
The Bicuspid valve component list of first heart sound S1 is shown M1 (the expression left atrioventricular valve is closed);
The Tricuspid valve component list of first heart sound S1 is shown T1;
The aortic valve closing component list of second heart sound S2 is shown A2;
The valve of pulmonary trunk component list of second heart sound S2 is shown P2.
Can write down the waveform of shallow table arterial pulse with the sphygmogram instrument, this recording geometry is called sphygmogram, is called the pulse wave starting point referring to Fig. 4: u, A is main ripple, and B is tidal wave (a dicrotic wave prewave), and C is dicrotic pulse wave-wave peak, D is a dicrotic pulse wave-wave paddy, and u ' is called next pulse wave starting point.UA is a upstroke, and Au ' is a decent, and T is a cardiac cycle.
Upstroke (uA): at the ventricle phase of maximum ejection, arteriotony rises rapidly, and tube wall is expanded, and forms the upstroke in the pulse wave.The influence that the slope of upstroke and amplitude are penetrated blood speed, cardiac output and penetrated the resistance that blood meets.
Decent (Au '): the later stage of Ve, penetrate blood speed and slow down, descending branch represents that cardiac ejection enters slow ejection period, and be less than the blood volume of outside all diffluence because of entering the interior blood volume of human artery this moment, so arterial pressure reduces, the external caliber retraction forms the leading portion of descending branch.A fluctuation that makes progress occurring in the descending branch is positive wave, is called dicrotic wave.A little downward ripple before the dicrotic wave perhaps is called trough, incisura or dicrotic notch (Incisura) negative wave, and In commonly used represents.The generation of negative wave is that intraventricular pressure quickly falls to and is lower than the aorta internal pressure because ventricle begins diastole, and blood refluxes caused to the aortic valve direction.Dicrotic wave is that blood impacts to valve, causes that a recoil slightly raises the Arterial system internal pressure again and forms because aortic valve is closed suddenly.The second composition aortic valve closing composition A2 of corresponding second heart sound S2 also is that intraventricular pressure descends suddenly owing to ventricular diastole, and the anti-stream of aorta inner blood causes that closing of aortic valve produces " closing sound ".
Because the second composition A2 of second heart sound S2 has represented the moment of aortic valve closing in incisura In in the catacrotic limb and the phonocardiogram.Incisura In in the catacrotic limb that peripheral arterial obtains go out now than phonocardiogram in moment of occurring of the second composition A2 of second heart sound S2 postpone to some extent, the time of delay is exactly that aortic valve is closed blood suddenly and impacted and time that the dicrotic wave that forms is propagated in blood vessel to valve.And the waveform shape of hear sounds and pulse wave can not change in a short time for same subjects, so the time that dicrotic wave is propagated in blood vessel is exactly pulse wave translation time.
Fig. 5 is the present invention calculates pulse wave translation time with second composition (aortic valve closing composition) A2 of second heart sound S2 a sketch map.
Heart contraction beginning phase (RWPIT) physiological parameter that the further scheme of the present invention is obtained refers generally to left ventricle and begins to shrink, and makes the time that left ventricular pressure power rises and causes MC.Normally adopted the C point of apexcardiography ACG to represent left ventricle to shrink beginning in the past, and with first high amplitude of first heart sound S1, radio-frequency component M1 sign as MC.
Referring to Fig. 6, apexcardiography ACG comprises four ripples and five characteristic points, and wherein the C point is atrial systole ripple end (atrial systole finishes), and ventricular systolic wave begins the sharply point of rising, starting point is shunk in satisfactory again chamber, and is consistent with the R wave crest peak time of electrocardiogram ECG substantially.。
Owing to being very easy to be subjected to the position attitude in the clinical practice application, being recorded in of apexcardiography ACG write down less than correct ACG waveform, so the identification that C is ordered is just very difficult with breathing to influence.According to apexcardiography ACG about the definition of its characteristic point and the description of characteristic, the C point is consistent with Electrocardiographic R ripple position, and what comprise among the RWPWTT is exactly the time of R ripple to Bicuspid valve composition (first high amplitude, the radio-frequency component) M1 of first heart sound S1, so adopt the R ripple to begin the phase as heart contraction to the time of the Bicuspid valve composition M1 of first heart sound S1 in the method for the further scheme continuous blood pressure measuring of the present invention, note is RWPIT.This method is more simple, easy operating.
Another heart physiological parameter isovolumic contraction period that the further scheme of the present invention is obtained is a phase crucial the time in the cardiac cycle.It is meant after phase heart contraction beginning, and MC is to time that aortic valve is opened.At MC and before aortic valve do not open as yet, ventricular muscles was shunk, but blood pressure is can not be compressed, and pressure raises rapidly so left ventricular volume is constant.When intraventricular pressure surpassed aorta inner blood pressure, aortic valve was opened, and blood penetrates, and isovolumic contraction period finishes.
The method of the further scheme of the present invention is carried out value by pulse wave starting point U and incisura point In.Because the pulse wave conduction needs certain hour, so the moment that the starting point U of pulse wave and incisura point In occur will be later than the moment of opening of aortic valve and aortic valve closing.But the time interval of U-In equates with the left ventricular ejection time LVET that traumatic method is measured.So can adopt the time interval of In to replace LVET, this method is simple, has non-invasive.
The inventive method and device have following advantage:
1, original R ripple pulse wave translation time RWPWTT has comprised heart contraction beginning phase RWPIT and isovolumic contraction period ICT, study according to the applicant, the variation relation in the same way that has confirmed heart contraction beginning phase RWPIT and RWPWTT reaches the exaggerative effect to the RWPWTT quotient, and the inverse change of isovolumic contraction period ICT and RWPWTT relation reaches the effect of underestimating to RWPWTT, therefore the inventive method has proposed accurately to obtain the method for pulse wave translation time, got rid of heart contraction beginning phase RWPIT and isovolumic contraction period ICT forward and the reverse interference to pulse wave translation time, the measurement that will be used for arteriotony with the pulse wave translation time parameter that the inventive method is obtained can improve the accuracy of continuous blood pressure measuring;
2, the process of obtaining cardiechema signals in the inventive method is with to obtain ECG signal convenient equally, so easy operating;
3, because the inventive method has been eliminated the interference effect that original R ripple pulse wave translation time measuring method cardiac is shunk phase beginning RWPIT and isovolumic contraction period ICT, improved the accuracy of measuring, so can be used for continuous measurement head blood pressure, solved in original blood pressure measurement and lacked, can not be used for the difficult problem of head blood pressure measurement because of breast-head distance weak point, conduction time.
4, can be on same set of device, utilize between Electrocardiographic R ripple, phonocardiogram and three kinds of signals of pulse wave the time phase relation continuous blood pressure measuring in, obtain other and the closely-related heart physiological parameter of blood pressure synchronously, the analysis and the research that concern between blood pressure and the heart physiological function are provided convenience for further utilizing these parameters;
5, the heart contraction beginning issue value that can obtain of the further scheme of the present invention not only can facilitate for the further relation between analysis and research blood pressure and the heart physiological function, but also can be used as the index of assess cardiac preload, thereby for adopting heart contraction beginning issue value assess cardiac preload index that a kind of non-invasive measurement method is provided;
6, the further scheme of the present invention isovolumic contraction period numerical value that can obtain not only can facilitate for the further relation between analysis and research blood pressure and the heart physiological function, but also can be used as the index of assess cardiac afterload, thereby for adopting isovolumic contraction period numerical Evaluation cardiac afterload that a kind of non-invasive measurement method is provided.
Description of drawings
Fig. 1, prior art are calculated pulse wave translation time algorithm signal resistance with ECG R wave
The different piece of Fig. 2, the R ripple pulse wave translation time RWPWTT that obtains with prior art is formed sketch map
Fig. 3, phonocardiographic four constituent figure
Fig. 4, pulse waveform and characteristic point sketch map
Fig. 5, the inventive method are calculated the pulse wave translation time sketch map with the second composition A2 of second heart sound
Fig. 6, apexcardiography
The software flow pattern of Fig. 7, enforcement the inventive method embodiment
Fig. 8, apparatus of the present invention frame principle figure
Specific embodiments
This example is the acquisition methods and the device of the pulse wave translation time parameter when being used for that the human body head blood pressure carried out continuous measurement.
Earlier set up pulse wave translation time and the regression equation between the arteriotony by shooting for the measured:
BP＝a+b*PWTT
BP is an arteriotony in the formula, and PWTT is a pulse wave translation time, and a and b are regression coefficient; Determine measured's regression coefficient a and b with the individuation alignment technique;
Obtain measured's pulse wave translation time PWTT then continuously, characterize measured's arteriotony by shooting with equation BP=a+b*PWTT.
The method of obtaining pulse wave translation time PWTT is:
With EGC sensor and heart sound transducer attached to measured's body surface, pulse wave sensor is fixed on measured's head, transducing signal is input to computer behind signal condition, the software of computer system comprises the two large divisions: data in real time shows the analytical calculation of record and data, data in real time shows that record is to adopt Visual C++ to write, the sense samples data that come from Acquisition Circuit in order to reception, and show in real time, then initial data and the crucial intermediate object program of part are recorded in the disk file; Data analysis software adopts Matlab 6.5 programmings to realize, this software has powerful computing ability, can make it have the interface alternation ability same equally by programming with other high-level programming language, the data analysis software that programming realizes through Matlab is handled the data of record, extract the characteristic point of relevant waveform, and calculate corresponding index and graphing.
According to electrocardiogram, phonocardiogram, the pulse wave figure of the same sequential of computer output, this example is calculated pulse wave translation time with second composition (aortic valve closing composition) A2 of second heart sound.Promptly the second composition A2 with second heart sound does starting point, and the moment that catacrotic limb A0 ' superior thyroid notch In occurs is a terminal point, calculates pulsation ripple conduction time A2PWTT:
A
2PWTT＝In-A
2
Above-mentioned algorithm need be determined two spies on schedule: A2 and In.
The principle of judging the A2 characteristic point is:
One, determine Electrocardiographic R ripple position,
5 single order differential diffECG of 1-1, calculating electrocardiosignal, and seek the position dPeakECG that first maximum negative differential value occurs therein, the position of this value generally is positioned in the decline or upstroke of R ripple, and is R ripple differential characteristics threshold value with this maximum negative differential value dECG;
1-2, be 60-110ms, about dPeakECG, in the scope of each 40ms, in the original electrocardiographicdigital signal, seek the position RECG that maximal peak point occurs, be the position of R ripple according to the time span of electrocardiogram QRS ripple;
1-3, repeat to seek next R ripple, and calculate RR interval RRtime with 1-1 and 1-2 step.With RRtime as RR interval matching template value;
1-4, be reference with R ripple differential characteristics threshold value and RR interval matching template value, begin to cross the time span shorter slightly than RR interval matching template value (changes the most very much not according to adjacent R R interval and can surpass 100ms from the position of secondary R wave, determine to shorten slightly 100ms), seek differential value and R ripple differential characteristics threshold value in the certain limit and differ less than 20% point negative differential value dECGtemp as new R ripple.And about this point, in the scope of each 40ms, in the original electrocardiographicdigital signal, seek the position RECG that maximal peak point occurs, be the position of R ripple;
1-5, upgrading RR interval matching template value, is that benchmark is asked for the maximum negative differential value dECG in this QRS ripple with the position of R ripple, and is worth with this and upgrades R ripple differential characteristics threshold value;
1-4 and 1-5 step are carried out in 1-6, circulation, calculate all R ripple position datas;
Two, according to the hear sounds theory, the altofrequency, the high amplitude ripple that occur the earliest in the second heart sound are the aortic valve closing composition, and after cardiechema signals was handled, the peak of asking for the altofrequency that occurs the earliest in the second heart sound, high amplitude ripple was as A2.
2-1, first and second hear sounds appear at after the R ripple certainly, so according to the position of R ripple, be that the data of RR interval matching template value are averaged with thereafter time span;
2-2, be zero point, cardiechema signals asked absolute value with the average, will inevitably be after the R ripple and RR interval matching template value with two bigger envelopes of interior appearance, the i.e. first and second hear sounds envelopes;
2-3, absolute value signal is done normalized, and 50% being threshold value, just have only first and second hear sounds greater than the envelope of this threshold value;
2-4, the signal that the 2-3 step is obtained carry out smoothing processing, and be threshold value with 50% of level and smooth later signal, greater than this threshold value is 1, less than being 0, a digital signal that has only two positive pulses will be obtained, the rising edge of first pulse is exactly the rough moment that second heart sound occurs, and writing down this position is PCG2.
2-5, the time that continues owing to whole second heart sound are 70-80ms, so calculate 5 single order differential from about the PCG2 position in the scope of each 50ms, because A2 is the high frequency high-amplitude signal, so the single order differential value of this signal certainty is greater than the first one-tenth sub-signal of the low frequency short arc of front, and be unexpected variation, imitate 2-2 step computing differential result's envelope, the record envelope signal is BeginA2 greater than first point of baseline mean;
The point that the differential value direction changes after 2-6, the calculating BeginA2 is as EndA2;
2-7, between BeginA2 and EndA2, seek maximum or minimum point as A2;
The decision principle of In:
Because the appearance of A2 appears being certain to be later than in periphery pulse wave incisura, so can be by A2 as the starting point of judging;
To corresponding A on the pulse wave 2 moment constantly as zequin, 300ms is with interior 5 the single order differential (pulse wave translation time with this algorithm computation is not more than 300ms) of doing backward, because the incisura point correspondence is trough point on the pulse wave, so just the differential direction becomes positive point from negative, with this point as In.
Fig. 7 is for implementing the computer software flow chart of said method.
In general the characteristic point of calculating by above-mentioned rule is accurately, correctly the deal with data file.But when occurring because of the individual variation between the subjects is more serious, signal is interfered and causes waveform change and when influencing the situation of algorithm identified, need increase the link of manual intervention correction in characteristic point identification.
This example is utilized electrocardio, hear sounds, when pulse wave figure obtains pulse wave translation time, also can be obtained measured's phase heart contraction beginning and isovolumic contraction period numerical value synchronously in continuous measurement head blood pressure process, and method is:
In same cardiac cycle, obtain the R ripple to time of the MC composition M1 (first high amplitude, radio-frequency component) of first heart sound S1 be heart contraction beginning phase RWPIT;
In same cardiac cycle, use the time of the MC composition M1 of first heart sound S1 to the second composition aortic valve closing composition A2 of second heart sound S2, deduct left ventricular ejection time LVET and obtain heart isovolumic contraction period ICT; Described left ventricular ejection time LVET is meant that left ventricle begins to penetrate blood (opening of aortic valve) to the time of penetrating blood agglomeration bundle (aortic valve closing), specifically is to get pulse wave starting point 0 to go out spacing between now to incisura point In.
The device of implementing the said method employing is:
Pulse wave sensor is the bladder-type pulse wave sensor, its structure is: pressure transducer is fixed on the circuit board that is contained on the dull and stereotyped pedestal, dull and stereotyped pedestal is fixedlyed connected with air bag, pressure transducer pin lead-in wire is drawn from sidepiece, passage is left at the pedestal middle part, to guarantee inside and outside gas pressure balancing.
Pressure transducer adopts the silicon microstructure piezoresistive transducer 5350-008 of U.S. SMI company exploitation, full scale be 0.8psi (5kPa, 40mmHg).Its substrate can be directly as measuring sensing element, and diffusion resistance is connected into the electric bridge form in substrate.When substrate is subjected to the external force effect and when producing deformation, each resistance value will change, electric bridge will produce corresponding uneven output.During use, pick off is fixed on the tremulous pulse with elastic webbing, can not fix too tight, in order to avoid influence pulse wave propagation and prevent that the piezoresistive transducer in the air bag is in nonlinear area.This example is provided with two pulse wave sensors, is separately fixed on the temple of measured's head both sides.
Heart sound transducer adopts active hear sounds vibrating sensor, its inside includes amplifying circuit, so have good interference free performance, can pick up the low frequency signal smaller or equal to 100Hz effectively, adopt positive and negative 3.3 volts of dual power supplies, operating current is 110 μ A.It is little to have volume, characteristics that can waterproof.
EGC sensor is conventional electrocardio probe.
Pulse wave sensor, heart sound transducer, EGC sensor connect data handling machine by pulse wave modulate circuit, hear sounds modulate circuit, electrocardio amplifying circuit respectively.
Pick off, modulate circuit, data handling machine all can adopt existing electrocardiogram, pulsation ripple figure, phonocardiographic data acquisition, conditioning, definition technique to implement.
Claims (3)
1. the acquisition methods of the pulse wave translation time in the continuous measurement of pulse wave method arteriotony comprises following content:
-set up pulse wave translation time and the regression equation between the arteriotony by shooting for the measured:
BP＝a+b*PWTT
BP is an arteriotony in the formula, and PWTT is a pulse wave translation time, and a and b are regression coefficient;
-determine measured's regression coefficient a and b with the individuation alignment technique;
-obtain measured's pulse wave translation time PWTT continuously;
It is characterized in that the method for the described measured's of obtaining pulse wave translation time PWTT is:
The pulsation ripple of-synchronous acquisition human body, electrocardio, cardiechema signals form synchronous pulsation ripple, electrocardio and phonocardiogram;
-by above-mentioned three kinds of signal graphs, in same cardiac cycle, second composition aortic valve closing composition (A2) point with second heart sound (S2) is made starting point, makes terminal point with the moment that catacrotic limb (Au ') superior thyroid notch (In) occurs, and the time difference of calculating the two is a pulsation ripple conduction time.
2. the acquisition methods of the pulse wave translation time in the continuous measurement of pulse wave method arteriotony according to claim 1, it is characterized in that: in same cardiac cycle, obtain the R ripple to phase (RWPIT) heart contraction beginning time of the MC composition (M1) of first heart sound (S1) for this cycle.
3. the acquisition methods of the pulse wave translation time in the continuous measurement of pulse wave method arteriotony according to claim 1 and 2, it is characterized in that: in same cardiac cycle, with the MC composition (M1) of first heart sound (S1) time, deduct the heart isovolumic contraction period (ICT) that left ventricular ejection time (LVET) obtains this cycle to the second composition aortic valve closing composition (A2) of second heart sound (S2); Described left ventricular ejection time (LVET) is meant that left ventricle begins to penetrate blood to the time of penetrating the blood agglomeration bundle, specifically is to get pulse wave starting point (U) to incisura point (In) to go out spacing between now.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CNB2006100815436A CN100413464C (en) | 2006-05-26 | 2006-05-26 | Method and apparatus for continuously measuring blood pressure |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CNB2006100815436A CN100413464C (en) | 2006-05-26 | 2006-05-26 | Method and apparatus for continuously measuring blood pressure |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN1849998A CN1849998A (en) | 2006-10-25 |
| CN100413464C true CN100413464C (en) | 2008-08-27 |
Family
ID=37131513
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CNB2006100815436A Expired - Fee Related CN100413464C (en) | 2006-05-26 | 2006-05-26 | Method and apparatus for continuously measuring blood pressure |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN100413464C (en) |
Families Citing this family (38)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN100515327C (en) * | 2007-12-06 | 2009-07-22 | 山东大学 | Detector methods and apparatus of cardiovascular system combining with variability guideline |
| JP5043707B2 (en) * | 2008-02-12 | 2012-10-10 | テルモ株式会社 | Blood pressure measurement device and control method thereof |
| US20100331708A1 (en) * | 2009-06-29 | 2010-12-30 | Edwards Lifesciences Corporation | Monitoring cardiovascular conditions using signal transit times |
| CN102258364A (en) * | 2010-05-31 | 2011-11-30 | 深圳市盛力康实业发展有限公司 | Pulse wave identification method, system and artery function detection instrument |
| CN101862201B (en) * | 2010-06-23 | 2011-08-31 | 南京邮电大学 | Method for representing cardiophonogram in intelligent cardiophone of mobile phone |
| CN102370472A (en) * | 2010-08-12 | 2012-03-14 | 遵义医学院附属医院 | Method and device for detecting descending aorta pulse wave through gullet to obtain descending arterial blood pressure |
| CN102440768B (en) * | 2010-10-13 | 2013-08-28 | 兰州理工大学 | Method for extracting pulse waveform feature points |
| CN102688024A (en) * | 2012-04-24 | 2012-09-26 | 北京大学 | Blood pressure noninvasive measuring method |
| JP6090424B2 (en) * | 2013-02-26 | 2017-03-08 | 株式会社村田製作所 | Pulse wave propagation time measurement device |
| CN106073742A (en) * | 2013-05-13 | 2016-11-09 | 天津点康科技有限公司 | A kind of blood pressure measuring system and method |
| CN103598876B (en) * | 2013-11-22 | 2016-08-17 | 哈尔滨工业大学深圳研究生院 | Data processing method and system |
| CN103976721B (en) * | 2014-04-22 | 2016-07-06 | 辛勤 | Blood pressure measuring method and for realizing the embedded equipment of the method |
| JP6306463B2 (en) * | 2014-07-30 | 2018-04-04 | 日本光電工業株式会社 | Biological information measuring device, biological information measuring method, and program |
| CN107072560B (en) * | 2014-10-20 | 2021-02-26 | 浜松光子学株式会社 | Blood pressure measurement device and computer-readable storage medium storing blood pressure measurement program |
| JP6366463B2 (en) * | 2014-10-31 | 2018-08-01 | オムロンヘルスケア株式会社 | Blood pressure measurement device |
| US20170347895A1 (en) | 2015-01-04 | 2017-12-07 | Vita-Course Technologies Co.,Ltd | System and method for health monitoring |
| CN204515353U (en) | 2015-03-31 | 2015-07-29 | 深圳市长桑技术有限公司 | A kind of intelligent watch |
| CN105030277B (en) * | 2015-03-03 | 2018-02-09 | 青岛美诺泰科信息技术有限公司 | A kind of monitoring device based on intelligent terminal |
| CN104720777B (en) * | 2015-03-10 | 2017-11-03 | 中国科学院电子学研究所 | A kind of noninvasive continuous blood pressure physiological monitoring system |
| US10709383B2 (en) | 2015-04-02 | 2020-07-14 | Microsoft Technology Licnesing, Llc | Wrist-worn pulse transit time sensor |
| CN106175720A (en) * | 2015-05-06 | 2016-12-07 | 深圳迪美泰数字医学技术有限公司 | The monitoring of a kind of Physiological And Biochemical Parameters and the method and device recorded |
| CN104970781B (en) * | 2015-06-08 | 2017-12-26 | 脉极客医疗科技（北京）有限公司 | A kind of ankle brachial index measurement apparatus, sphygmomanometer |
| CN105147269B (en) * | 2015-06-16 | 2017-10-13 | 江苏斯坦德利医疗科技有限公司 | A kind of noninvasive continuous BP measurement method |
| CN105105734B (en) * | 2015-09-11 | 2018-02-27 | 深圳先进技术研究院 | A kind of noninvasive continuous blood pressure measurement device based on cardiechema signals |
| CN114343713A (en) * | 2015-09-28 | 2022-04-15 | 浙江佳云医疗科技有限公司 | Sleeveless blood pressure continuous monitoring method and system |
| CN105310724B (en) * | 2015-09-28 | 2018-12-14 | 北京云智创想信息技术有限公司 | Method and system for measuring pulse wave propagation speed |
| CN108697342B (en) * | 2015-12-07 | 2021-11-16 | 美第奇科技有限责任公司 | Observational heart failure monitoring system |
| CN107865647B (en) * | 2016-09-28 | 2020-01-14 | 京东方科技集团股份有限公司 | Blood pressure detection device and method for calibrating blood pressure detection device |
| TWI653032B (en) * | 2016-12-01 | 2019-03-11 | 深禾醫學科技股份有限公司 | ECG monitoring device and blood pressure monitoring system |
| CN108245148B (en) * | 2016-12-28 | 2022-08-23 | 三星电子株式会社 | Adaptive biological signal feature combination device and method |
| CN107126201A (en) * | 2017-03-31 | 2017-09-05 | 悦享趋势科技（北京）有限责任公司 | Continuous blood pressure detection method, equipment and the device of non-invasive |
| CN108742697B (en) * | 2018-05-29 | 2022-06-03 | 深圳市太空科技南方研究院 | Heart sound signal classification method and terminal equipment |
| CN109008999B (en) * | 2018-06-13 | 2023-04-25 | 福建工程学院 | Method for measuring heart sound and pulse wave conduction time and portable measuring device |
| CN109171677A (en) * | 2018-09-20 | 2019-01-11 | 芯海科技（深圳）股份有限公司 | A kind of Portable type measurement unit and the hemodynamic parameter measurement method based on the device |
| CN109497991B (en) * | 2019-01-04 | 2021-07-02 | 济南汇医融工科技有限公司 | Heart failure detection device based on machine learning |
| CN110367959A (en) * | 2019-07-18 | 2019-10-25 | 上海海事大学 | A kind of blood pressure measuring device based on pulse wave phase difference and pulse wave characteristic parameters |
| CN114521876A (en) * | 2022-03-11 | 2022-05-24 | Oppo广东移动通信有限公司 | Blood pressure estimation method, blood pressure estimation device, storage medium, and electronic apparatus |
| CN116712051A (en) * | 2023-06-08 | 2023-09-08 | 合肥中科博谐科技有限公司 | Noninvasive blood pressure measurement method and device, computer equipment and storage medium |
Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1042064A (en) * | 1988-10-22 | 1990-05-16 | 昆明电脑公司 | Diagnosis instrument for ventricle blood vessel of human body |
| CN1062648A (en) * | 1990-12-25 | 1992-07-15 | 中国人民解放军空军杭州医院 | Left, right heart function synchronous testing analysis instrument |
| WO1999026529A1 (en) * | 1997-11-20 | 1999-06-03 | Seiko Epson Corporation | Pulse wave diagnostic apparatus, blood pressure monitor, pulse wave shape monitor and pharmacologic effect monitor |
| CN2363654Y (en) * | 1999-01-19 | 2000-02-16 | 华南理工大学 | Heart function parameter tester |
-
2006
- 2006-05-26 CN CNB2006100815436A patent/CN100413464C/en not_active Expired - Fee Related
Patent Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1042064A (en) * | 1988-10-22 | 1990-05-16 | 昆明电脑公司 | Diagnosis instrument for ventricle blood vessel of human body |
| CN1062648A (en) * | 1990-12-25 | 1992-07-15 | 中国人民解放军空军杭州医院 | Left, right heart function synchronous testing analysis instrument |
| WO1999026529A1 (en) * | 1997-11-20 | 1999-06-03 | Seiko Epson Corporation | Pulse wave diagnostic apparatus, blood pressure monitor, pulse wave shape monitor and pharmacologic effect monitor |
| CN2363654Y (en) * | 1999-01-19 | 2000-02-16 | 华南理工大学 | Heart function parameter tester |
Non-Patent Citations (2)
| Title |
|---|
| 用脉搏波传导时间实现血压的连续测量. 向海艳，俞梦孙.研究论著，第27卷第2期. 2006 |
| 用脉搏波传导时间实现血压的连续测量. 向海艳，俞梦孙.研究论著，第27卷第2期. 2006 * |
Also Published As
| Publication number | Publication date |
|---|---|
| CN1849998A (en) | 2006-10-25 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN100413464C (en) | Method and apparatus for continuously measuring blood pressure | |
| US10092268B2 (en) | Method and apparatus to monitor physiologic and biometric parameters using a non-invasive set of transducers | |
| WO2020007041A1 (en) | Blood pressure measurement apparatus and method, electronic device, and computer readable storage medium | |
| JP6131404B2 (en) | Method and instrument for measuring information indicative of cardiac dysfunction and abnormality | |
| US11241170B2 (en) | Monitor for blood pressure and other arterial properties | |
| CN101765398B (en) | Assessment of preload dependence and fluid responsiveness | |
| US20150038856A1 (en) | Method and apparatus for estimating myocardial contractility using precordial vibration | |
| US10349838B2 (en) | Methods and apparatus for determining arterial pulse wave velocity | |
| CN102834047A (en) | Elimination of the effects of irregular cardiac cycles in the determination of cardiovascular parameters | |
| WO2012055498A4 (en) | Method for myocardial segment work analysis | |
| CA2604337A1 (en) | System and method for non-invasive cardiovascular assessment from supra-systolic signals obtained with a wideband external pulse transducer in a blood pressure cuff | |
| US9872638B2 (en) | Method and apparatus for determining information indicative of cardiac malfunctions | |
| US10004473B2 (en) | Heart rate detection method and device using heart sound acquired from auscultation positions | |
| CN106923812B (en) | A kind of rate calculation method based on cardiechema signals autocorrelation analysis | |
| CN114652351A (en) | Continuous blood pressure measuring method and device based on ultrasonic Doppler and electronic equipment | |
| US8112150B2 (en) | Optimization of pacemaker settings | |
| JP2008295517A (en) | Analysis system and method of pulse diagnosis in doctor of chinese medicine | |
| CN111493843B (en) | Pressure-volume loop determination apparatus, system, method, device and storage medium | |
| JP7244509B2 (en) | Risk assessment for coronary artery disease | |
| Forouzanfar et al. | Model-based oscillometric blood pressure estimation | |
| Singh et al. | Hilbert vibration decomposition of seismocardiogram for hr and hrv estimation | |
| Azad et al. | Spatial distribution of seismocardiographic signals | |
| Jain et al. | Seismocardiography: An alternate method to estimate electro-mechanical window | |
| Khosrow-Khavar | Automatic and Non-Invasive Delineation of the Seismocardiogram Signal for the Estimation of Cardiac Time Intervals with Applications in Diastolic Timed Vibration and Early Stage Hemorrhage Detection | |
| KR20200025738A (en) | Method, apparatus and program for obtaining information of cardiovascular system using heart sound |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C06 | Publication | ||
| PB01 | Publication | ||
| C10 | Entry into substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| C17 | Cessation of patent right | ||
| CF01 | Termination of patent right due to non-payment of annual fee |
Granted publication date: 20080827 Termination date: 20130526 |