CN106618504A - High-accuracy continuous non-invasive blood pressure measuring device with self-adaptation calibration function - Google Patents

Abstract

The invention belongs to the technical field of arterial blood pressure measurement, and discloses a high-accuracy continuous non-invasive blood pressure measuring device with the self-adaptation calibration function. A photoelectric sensor is adopted for detecting pulse waves, reverse bias voltage is provided for a light receiving tube, the sensitivity and stability of the light receiving tube are enhanced, quite weak pulse wave signals can be detected, and the waveform quality of the detected signals can be improved; a broadband filter is adopted, and it is ensured that pulse wave shapes are distortionless; due to the technologies, correcting variables can be correctly extracted from pulse waves. The device recognizes propagation time PTT related to systolic pressure and diastolic pressure from pulse waves, and extracts various variables according to pulse wave form changes to recognize various anomalous changes of self-adaptation correction PTT in real time; on the basis of an existing mathematic model, blood pressure can be measured in a high-accuracy, continuous and noninvasive mode under the complex clinic condition, and calibration and repeated standardization can be achieved not depending on conventional methods such as cuff oscillography.

Description

A kind of high accuracy continuous non-invasive blood pressure measuring device for possessing adaptive calibration

Technical field

The present invention relates to arterial pressure field of measuring technique, and in particular to a kind of high precision for possessing adaptive calibration function Degree continuous non-invasive blood pressure measuring device.

Background technology

Arterial pressure is to reflect one of circulatory system state, leading indicator of assessment organ perfusion, is Perioperative Care Important vital sign parameter.At present the conventional monitoring of blood pressure method of perioperative can be divided into invasive measurement and non-invasive measurement.Have Wound measurement is referred to inserts pipe special in the circulatory system of body, and mechanical potential is converted into after electronic signal by converter The technology of real-time display of blood pressure change on custodial care facility.Invasive measuring method can continuously, accurately measure and often fight blood pressure, but The danger that it is likely to result in also can not be ignored with injury.The conventional method of non-invasive measurement is cuff oscillographic method, this technical operation It is simple and accuracy has obtained clinical accreditation, it is widely used in health examination and Perioperative Nursing.But, cuff oscillographic method can only Blood pressure is discontinuously measured every 3-5 minutes, it is impossible to the change of real-time tracking arterial pressure.

For this purpose, medical circle proposes the requirement that continuous non-invasive measures blood pressure of often fighting.In existing various technical schemes, profit The method for often winning blood pressure with the measurement of pulse wave propagation time/speed (PTT/PWV) continuous non-invasive is increasingly becoming the focus of research.Should Measuring method is by one or more photoelectric sensors and one group of electrocardioelectrode synchronization gain volume pulsation wave (PhotoPlethysmoGraphy PPG) and electrocardiosignal (ECG), using the time difference between PPG and ECG or two PPG it Between time difference calculate PTT/PWV；The functional relation and founding mathematical models between PTT/PWV and blood pressure is explored, utilizing can The PTT/PWV of measurement is estimating blood pressure.Many scientific papers report the original that blood pressure is often won using the measurement of PTT/PWV continuous non-invasives Reason, such as Yan Chen, Changyun Wen, Guocai Tao, Min Bi, and Guoqi Li《A Novel Modeling Methodology of the Relationship Between Blood Pressure and Pulse Wave Velocity》；Yan Chen, Changyun Wen, Guocai Tao and Min Bi《Continuous and Noninvasive Measurement of Systolic and Diastolic Blood Pressure by One Mathematical Model with the Same Model Parameters and Two Separate Pulse Wave Velocities》；Younhee Choi,Qiao Zhang,Seokbum Ko《Noninvasive cuffless blood pressure estimation using pulse transit time and Hilbert–Huang transform》； Zheng Y,Poon CC,Yan BP,Lau JY《Pulse Arrival Time Based Cuff-Less and 24-H Wearable Blood Pressure Monitoring and its Diagnostic Value in Hypertension》； Mukkamala R,Hahn JO,Inan OT,Mestha LK,Kim CS,H,Kyal S《Toward Ubiquitous Blood Pressure Monitoring via Pulse Transit Time:Theory and Practice》.The specific implementation method or device that blood pressure is often won using the measurement of PTT/PWV continuous non-invasives is many patents disclosed, Such as Chinese patent CN101229058A, CN102811659A, CN1127939C, United States Patent (USP) 5865755,5857975, 5649543rd, 9364158 and European patent 0413267 etc..

The methods and techniques of existing utilization PTT/PWV measurements blood pressure are required for using traditional cuff oscillographic method measurement one To carry out, the reasons why initial calibration, calibration is PTT/PWV to individual or one group of pressure value and the dependency relation of blood pressure is object dependency, There is the relation of determination between each individual PTT/PWV and blood pressure, the purpose of calibration is to determine the number being adapted with object Learn model parameter.However, existing method has certain limitation, the circulatory system is can be only applied to not by the bar of external interference Under part.Because only that under the conditions of glitch-free, PTT just has stronger regularity with the relation of blood pressure for individuality, May be described by the function of determination and Mathematical Modeling.But in peri-operation period, the circulatory system of patient is in liquid undergoing treatment, medicine Under the influence of the Confounding Factors such as thing, operation technique, temperature, PTT can occur a series of ANOMALOUS VARIATIONSs, using the PTT of mutation and solid Some Mathematical Modelings can produce larger error estimating blood pressure.Determine because the PTT of mutation no longer has with the relation of blood pressure Regularity, even if the mutation that PTT is adapted to by frequent calibration mathematical model parameter does not solve root problem yet, it is impossible to full Requirement of the sufficient clinical measurement to accuracy and real-time.

Existing method generally detects pulse wave using the detection means of traditional blood oxygen degree of saturation instrument.This kind of detection means Only drive signal is provided to the luminous tube in sensor, drive signal is not provided to light-receiving tube, this is because blood oxygen degree of saturation instrument Measuring point be typically nail cover, the pulse signal at the position is stronger, such to be designed to meet clinical requirement.But it is right In pulse signal weaker human body such as toe, the insufficient sensitivity of this kind of sensor is high, in causing the pulse wave for detecting Interference is larger, and waveform quality is bad, is not suitable for studying the rule of pulse wave metamorphosis, while also causing identification PTT's Error increases.Additionally, traditional detection means typically filters off by force breathing using the narrow band filter of 0.5～12Hz doing Disturb, cause the pulse wave form distortion for detecting, this is feasible for the blood oxygen degree of saturation instrument for being not concerned with pulse wave form, but It is the rule for not being suitable for studying pulse wave metamorphosis.

The content of the invention

For the defect in existing method and technology, the present invention provides a kind of high accuracy for possessing adaptive calibration function Continuous non-invasive blood pressure measuring device, can utilize the change of pulse wave form, for being lived by blood transfusion and infusion, blood vessel under clinical condition Property medicine, operation intervention etc. caused by reason the mutation of PTT carry out self adaptive correction；Improve simultaneously sensor sensitivity and The waveform quality of detection signal, is able to detect that extremely faint pulse wave signal and guarantees that the form of waveform is undistorted.

A kind of high accuracy continuous non-invasive blood pressure measuring device for possessing adaptive calibration, including：

Control unit:For sending control signal, the drive signal of sensor driving and signal conversion unit is adjusted, and The DC level and multiplication factor of pulse wave detector unit output signal；

Sensor drive and signal conversion unit, for detection ear and toe pulse wave sensor luminous tube and Light-receiving tube provides drive signal, and the output signal of light-receiving tube is converted into voltage signal；

Pulse wave detector unit, for being filtered to voltage signal and amplifying；

Pulse wave is sampled and recognition unit, and the two paths of signals to processing through pulse wave detector unit synchronizes sampling, Data signal is obtained, and the waveform segment to ear in data signal and toe is identified；

Propagation time recognizes and filter unit, for being respectively obtained and contraction according to the time difference of ear and toe waveform segment Pressure related propagation time and the propagation time related to diastolic pressure, and the respiration interference to the propagation time carries out smooth filter Ripple；

Correcting variable is extracted and filter unit, for extracting correcting variable from ear pulse wave and toe pulse wave, Correction matrix is obtained, and the respiration interference to correcting variable carries out smothing filtering；

Propagation time corrects unit, and using correction matrix propagation time related to systolic pressure and and diastolic pressure are corrected respectively The ANOMALOUS VARIATIONS in related propagation time；

Computing unit, for calculating pulse wave velocity and pressure value of often fighting；

Human and machine interface unit, for being input into physiological parameter and showing continually varying pressure value and pulse wave.

Preferably, the sensor drives and signal conversion unit includes：

Luminous tube driver element, for providing corresponding electric current to luminous tube according to body measurements；

Light-receiving tube drives and detector unit, for providing reverse bias voltage to light-receiving tube, and according to the control of control unit The output signal of light-receiving tube is converted to voltage signal by signal processed；

Signal conversion unit, for filtering off voltage signal in reverse bias voltage.

Preferably, the reverse bias voltage is produced by measuring circuit or float power.

Preferably, the pulse wave detector unit includes：

Differential amplification unit, for being amplified to voltage signal, eliminates common mode disturbances；

Bandpass filtering unit, for being filtered to voltage signal, filtered band is 0.1～30Hz；

Gain adjustment unit, for adjusting multiplication factor according to the control signal of control unit.

Preferably, the pulse wave sampling and recognition unit include：

Pulse wave sampling unit, continuously adopts for synchronizing to the two paths of signals processed through pulse wave detector unit Sample, obtains continuous data signal；

Pulse wave recognition unit, it is corresponding with toe pulse wave for ear during each cardiac cycle is obtained from data signal Waveform segment and wave character.

Preferably, the propagation time identification and filter unit include：

Pulse wave propagation time recognition unit, for according to the waveform of ear and toe pulse wave in same cardiac cycle Section respectively obtains the propagation time T related to diastolic pressure_dThe propagation time T related to systolic pressure_s；

Pulse wave propagation time filter unit, for filtering off the respiration interference in the propagation time, recursion it is continuous 8 it is aroused in interest The T in cycle_sAnd T_d, calculate mean valueWithWherein T_siFor the T of i-th cardiac cycle_s, T_diFor The T of i-th cardiac cycle_d。

Preferably, the correcting variable is extracted and filter unit includes：

Correcting variable recognition unit, for extracting correcting variable a from ear pulse wave and toe pulse wave₁～a₇With K_m, wherein a₁Including a_1sAnd a_1d, a₂Including a_2sAnd a_2d, obtain correction matrixWith

Correcting variable filter unit, for filtering correcting variable in respiration interference, recursion continuous 8 cardiac cycle A, B and K_m, averageWithWherein A_iFor i-th cardiac cycle A, B_iFor the B of i-th cardiac cycle, K_miFor the K of i-th cardiac cycle_m。

Preferably, the propagation time correction unit includes：

The propagation time correction unit related to systolic pressure, for correcting T_sma=T_sm(1-A_m)；

The propagation time correction unit related to diastolic pressure, for correcting T_dmb=T_dm(1-B_m)。

Preferably, the computing unit includes：

The pulse wave velocity computing unit related to systolic pressure, propagates for calculating the pulse wave related to systolic pressure SpeedL is the propagation distance of pulse wave；

The pulse wave velocity computing unit related to diastolic pressure, for calculating the related pulse wave of diastolic pressure speed is propagated Degree

Systolic pressure computing unit, for calculating systolic pressureWherein k_ijAnd b_ijFor all ages and classes and sex The model parameter of crowd, i represents age, i=1,2 ..., n；n≤100；J represents sex, j=M/F, and M represents the model of the male sex Parameter, F is the model parameter of women；

Diastolic pressure computing unit, for calculating diastolic pressure

Mean arterial pressure computing unit, for calculating mean arterial pressure MAP=DBP+0.75K_mm(SBP-DBP)。

Preferably, the human and machine interface unit includes：

Physiological parameter input block, for being input into the age, sex and height of the measured；

Pressure value and pulse wave display unit, for display of blood pressure value and pulse wave, and in real time offer blood pressure gets over report from a liner police.

As shown from the above technical solution, the present invention needs frequent calibration for the technology that existing utilization PTT/PWV measures blood pressure Problem and traditional pulse wave detection device limitation, there is provided a kind of new high precision for possessing adaptive calibration function Degree, continuous, Woundless blood pressure measuring device.The device detects pulse wave, and identification and receipts from pulse wave using photoelectric sensor Contractive pressure correlation and the propagation time PTT related to diastolic pressure；In measurement process, extract various according to the metamorphosis of pulse wave Variable carrys out the various ANOMALOUS VARIATIONSs of Real time identification and adaptively correcting PTT；Connected using the Mathematical Modeling between PTT and blood pressure Blood pressure is often won in continuous, hurtless measure measurement.Unlike the prior art, the device possesses adaptive calibration function, it is not necessary to rely on Conventional method such as cuff oscillographic method calibrating and calibrate repeatedly, can under complicated clinical condition in real time, accurately measure blood Pressure, its accuracy is no less than cuff oscillographic method.Due to during the measurement device blood pressure need not to patient apply external force, do not interfere with by The sleep of survey person, is particularly suitable for nighttime blood pressures measurement；There is outstanding advantage particularly with patient's blood pressure monitoring of postoperative 48 hours, The R＆R of patient is not affected while preferably ensureing patient safety.

From unlike traditional pulse wave detection device, the device provides reverse bias voltage receiving to photoelectric sensor Light pipe, enhances sensitivity and the stability of light-receiving tube, is able to detect that extremely faint pulse wave signal and improves detection letter Number waveform quality；And adopting wide-band filter, it is ensured that pulse wave form is undistorted.Be conducive to from pulse using these technologies It is correct on ripple extract correcting variable, to realize that adaptive calibration function is laid a good foundation.

Figure of description

In order to be illustrated more clearly that the specific embodiment of the invention or technical scheme of the prior art, below will be to concrete The accompanying drawing to be used needed for embodiment or description of the prior art is briefly described.In all of the figs, similar element Or part is typically identified by similar reference.In accompanying drawing, each element or part might not draw according to actual ratio.

Fig. 1 is the theory diagram of the high accuracy continuous non-invasive blood pressure measuring device of adaptive calibration.

Fig. 2 is the circuit diagram of light-receiving tube driving and detector unit.

Fig. 3 is the circuit diagram of signal conversion unit.

Fig. 4 is the circuit diagram of differential amplification unit.

Fig. 5 is the circuit diagram of gain adjustment unit.

Specific embodiment

The embodiment of technical solution of the present invention will be described in detail below.Following examples are only used for clearer Ground explanation technical scheme, therefore example is intended only as, and can not be limited the scope of the invention with this.

The change of peri-operation period PTT can be divided into two classes：One class changes：The PTT changes that blood pressure causes；Two classes change： PTT and the nonsynchronous change of blood pressure (both change directions or variable quantity be not accordant to the old routine function rule).For example, blood volume is light PTT can increase when degree is not enough, but the regulation due to body itself to peripheral resistance, and blood pressure may change less；In chest and abdomen operation PTT may be had a strong impact on using drag hook, but the impact to blood pressure is less；Norepinephrine makes parteriole strong contraction, blood pressure Significantly raised but average on whole body PTT affects less.

When PTT occurs a class to be changed, it remains able to be expressed with determination function with the relation of blood pressure, can be by number Learn model to estimate the change of blood pressure.And when PTT occur two classes change when, using be based on regular circulation system Mathematical Modeling come Estimation blood pressure can produce larger error.This kind of error is the original reason error that blood pressure is measured using PTT, it is impossible to by initial fixed Mark with periodic calibration mathematical model parameter to solve.The difference of PTT and same individual PTT mutations are property between Different Individual Two different class problems, need to be solved with different methods.For this purpose, the present invention extracts various according to the metamorphosis of pulse wave Variable carrys out the various two classes change of indirect identification and adaptively correcting PTT, overcomes above-mentioned original reason error；Can be with reference to existing number Learn model and formed and possess the method that the continuous non-invasive of adaptive calibration function measures blood pressure, it is not necessary to by conventional method such as cuff Oscillographic method calibrating repeatedly.

The preferred ear of position of human body and toe of detection pulse wave, the pulse wave at the two positions can obtain main artery and The physiology of peripheral arterial, pathological information, possess representativeness in route of transmission.The preferred infrared light of sensor of detection pulse signal Power Capacity recording instrument (PPG).The present invention guarantees correctly to extract the metamorphosis of pulse wave by two methods：1. provide reverse Bias voltage strengthens sensitivity and the stability of light-receiving tube to the light-receiving tube of photoelectric sensor, improves the waveform matter of detection signal Amount；2. wide-band filter is adopted, it is ensured that pulse wave form is undistorted.

The relative change of form between ear and the metamorphosis and two kinds of pulse waves of toe pulse wave itself, to identification The change of the difference of the change of two classes and human body different parts blood pressure of PTT provides abundant information.The present invention lasts the several years and adopts The pulse wave and PTT of the invasive arterial pressure, ear and toe of a large amount of operation cases of collection is analyzed, according to two pulses Ripple itself and relative metamorphosis extract various variables, work out between the two classes change different from PTT of different variables Relation, and define the scope of application of various variables.

During clinical practice, during PPT continuous blood pressure measurings, real-time detection, analysis pulse wave simultaneously extract change Amount, judges whether PTT occurs the change of two classes according to whether variable falls into the scope of application, and is determined according to the property for being suitable for variable The nature and extent of the classes of PTT bis- change, if certain variable does not occur corresponding two class beyond scope of application explanation PTT become Change, then the variable is not applied to；Applicable several variables are merged, correcting value is calculated and PTT is corrected, after correction PTT/PWV accurately calculates blood pressure suitable for existing Mathematical Modeling.

The present invention expresses main, the most basic Changing Pattern of pulse wave form using limited variable, and works out Relation between these rules and PTT.Described below pulse wave ordinate on plane coordinates is amplitude h, and abscissa is the time T, pulse wave starting point is the origin of coordinates.

Embodiment：

As shown in figure 1, the device includes that control unit 11, sensor drives and signal conversion unit 12 and 13, pulse wave Detector unit 14 and 15, pulse wave sample and recognition unit 16, propagation time identification and filter unit 17, correcting variable extract and Filter unit 18, propagation time correction unit 19, computing unit 20, human and machine interface unit 21.

Described control unit 11, for sending control signal, makes each functional unit co-ordination, including：With negative-feedback Control principle, control signal is sent according to the size of the output signal of differential amplification unit 141 and 151 come adjust light-receiving tube drive and DC level in the output signal of detector unit 122 and 132；According to the pulse wave amplitude of the output of pulse wave detector unit 14 and 15 Size sends control signal to control the multiplication factor of gain adjustment unit 143 and 153.The function of control unit 11 is by monolithic meter Calculation machine and software are realizing.

The sensor drives and signal conversion unit 12 and 13, for the sensing of pulse wave at detection ear and toe The luminous tube of device and light-receiving tube provide drive signal, and according to the control signal of control unit 11 by the output signal of light-receiving tube Be converted to the voltage signal that pulse wave is detected under suitable clinical condition.In the present embodiment, it is preferable that the sensor drives and believes Number converting unit 12 and 13 includes that luminous tube driver element 121 and 131, light-receiving tube drives and detector unit 122 and 132, signal Converting unit 123 and 133.The luminous tube driver element 121 and 131, for different with the position of toe respectively according to ear Suitable electric current is provided to luminous tube.The light-receiving tube drives and the driving function of detector unit 122 and 132 is to provide reversely partially Voltage is put to light-receiving tube, reverse bias voltage is produced by measuring circuit, improve sensitivity and the stability of light-receiving tube, measuring circuit Reverse bias voltage is provided while light-receiving tube output signal is detected to light-receiving tube.Reverse bias voltage can also be by floating Power supply is produced, and with measuring circuit not altogether, its reverse bias voltage for producing does not affect measuring circuit to float power.The light Pipe drives and the detection function of detector unit 122 and 132 is, according to the control signal of control unit 11, light-receiving tube is exported Current signal is converted to adjustable voltage signal.The signal conversion unit 123 and 133, for filtering off from voltage signal Reverse bias voltage, it is to avoid post-amplifier saturation.

As shown in Fig. 2 the light-receiving tube drives and detector unit includes operational amplifier U1A and operational amplifier U1B；Fortune Calculate the input in the same direction connection+2.5V power supplys of amplifier U1A, the input in the same direction connection -2.5V power supplys of operational amplifier U1B； The light-receiving tube is connected between the reverse input end of the reverse input end of operational amplifier U1A and operational amplifier U1B；Computing The reverse input end of amplifier U1A is connected to its output end, the reverse input end of operational amplifier U1B by digital regulation resistance R4 Its output end is connected to by digital regulation resistance R3.The input in the same direction of operational amplifier U1A and U1B connect respectively+2.5V and- 2.5V voltages；Its reverse input end connection light-receiving tube D1, therefore D1 two ends are applied with 5V reverse bias voltages；Light-receiving tube D1 is exported Current signal by adjustable digital regulation resistance R3 and R4, be converted to adjustable voltage letter in the output end of U1A and U1B Number I/V_P and I/V_N, the resistance value of digital regulation resistance R3 and R4 is adjusted by the control signal of control unit 11.

As shown in figure 3, the signal conversion unit includes first adder and second adder；First adder includes fortune Amplifier U2A is calculated, the reverse input end of operational amplifier U2A connects -2.5V power supplys by resistance R7, operational amplifier U2A's Reverse input end is connected to its output end by resistance R11, and the reverse input end of operational amplifier U2A is connected to operational amplifier The output end of U1A, the input end grounding in the same direction of operational amplifier U2A；Second adder includes operational amplifier U2B, and computing is put The reverse input end of big device U2B connects+2.5V power supplys by resistance R8, and the reverse input end of operational amplifier U2B passes through resistance R12 is connected to its output end, and the reverse input end of operational amplifier U2B is connected to the output end of operational amplifier U1B, and computing is put The input end grounding in the same direction of big device U2B.The operational amplifier U2A and U2B constitutes adder, the input resistance of two adders R7 and R8 connect respectively -2.5V and+2.5V voltages, for deduct that it includes from voltage signal I/V_P and I/V_N it is reverse partially Put voltage.

The pulse wave detector unit 14 and 15, for pulse wave voltage signal to be filtered and amplified.The present embodiment In, it is preferable that the pulse wave detector unit 14 and 15 includes differential amplification unit 141 and 151, the and of bandpass filtering unit 142 152nd, gain adjustment unit 143 and 153.The differential amplification unit 141 and 151, for putting to pulse wave voltage signal Greatly, common mode disturbances are eliminated.The bandpass filtering unit 142 and 152, for being filtered to pulse wave voltage signal, ensures arteries and veins Wave morphology of fighting is undistorted, and frequency band is 0.1～30Hz.The gain adjustment unit 143 and 153, for according to control unit 11 Control signal adjusts multiplication factor, adapts to the change of pulse wave amplitude under clinical condition.

As shown in figure 4, the differential amplification unit includes operational amplifier U3A, the reverse input end of operational amplifier U3A The output end of operational amplifier U2A is connected to, the input in the same direction of operational amplifier U3A is connected to the defeated of operational amplifier U2B Go out end, the output end of operational amplifier U3A is connected to the input port of control unit by resistance R17, and operational amplifier U3A's is defeated Go out end as the output end of differential amplification unit.The operational amplifier U3A constitutes difference amplifier, does for eliminating common mode Disturb；Control unit 11 detects the output voltage DIFF_OUT of U3A by resistance R17, judges its size and sends control signal It is straight during digital regulation resistance R3 and R4, the i.e. size of regulation voltage I/V_P and I/V_N are adjusted to control light-receiving tube D1 output signals Flow component so as in the range of being maintained at.

The bandpass filtering unit includes high-pass filter and low pass filter.The electric capacity C3 and resistance R19 and C5 and R25 constitutes high-pass filter；Electric capacity C4 and resistance R23 constitutes low pass filter, and frequency band is 0.1～30Hz, it is ensured that pulse wave Form is undistorted.

As shown in figure 5, the gain adjustment unit includes operational amplifier U4A, the reverse input end of operational amplifier U4A The output end of differential amplification unit is connected to by digital regulation resistance R21；The input end grounding in the same direction of operational amplifier U4A, fortune The reverse input end for calculating amplifier U4A is connected to its output end by low pass filter.The operational amplifier U4A is by adjustable The digital regulation resistance R21 of section adjusts the size of output voltage AMP_OUT adjusting multiplication factor；The resistance of digital regulation resistance R21 Value is controlled by the control signal of control unit 11.The output voltage EER_SIG_OUT of the operational amplifier U4B is pulse wave Signal, for A/D converter sampling；Control unit 11 adjusts digital regulation resistance R21 by judging the size of pulse wave amplitude, control Pulse wave amplitude processed is in suitable scope.

The pulse wave sampling and recognition unit 16, for carrying out to the two paths of signals processed through pulse wave detector unit Synchronized sampling, obtains data signal, and the waveform segment to ear in data signal and toe is identified.It is excellent in the present embodiment Selection of land, the pulse wave sampling and recognition unit 16 include pulse wave sampling unit 161, pulse wave recognition unit 162.The arteries and veins Fight ripple sampling unit 161, for synchronizing continuous sampling to the two paths of signals processed through pulse wave detector unit, obtain number Word information.The pulse wave recognition unit 162, for obtaining ear and toe pulse in each cardiac cycle from data signal The waveform segment and wave character of ripple.

The propagation time identification and filter unit 17, for being respectively obtained according to the time difference of ear and toe waveform segment Propagation time related to the systolic pressure and diastolic pressure related propagation time, and the respiration interference to the propagation time filters Ripple.In the present embodiment, it is preferable that the propagation time identification and filter unit 17 include propagation time recognition unit 171, propagate Time filtering unit 172.The propagation time recognition unit 171, for from the time of starting point on ear and toe pulse wave Difference identifies the propagation time T related to diastolic pressure_d, and from the time difference of aortic valve closing point on ear and toe pulse wave Identify the propagation time T related to systolic pressure_s.The propagation time filter unit 172, for filtering exhaling in the propagation time Blot and disturb, the T of recursion continuous 8 cardiac cycle_sAnd T_d, averageWithWherein T_siFor The T of i-th cardiac cycle_s, T_diFor the T of i-th cardiac cycle_d。

The correcting variable is extracted and filter unit 18, for extracting correcting variable from ear and toe pulse wave, Correction matrix is obtained, and the respiration interference in correcting variable is filtered.In the present embodiment, it is preferable that the correction becomes Amount is extracted and filter unit 18 includes correcting variable extraction unit 181, correcting variable filter unit 182.The correcting variable is carried Unit 181 is taken, for extracting correcting variable a from ear and toe pulse wave₁～a₇And K_m, wherein a₁Including a_1sAnd a_1d, a₂ Including a_2sAnd a_2d, obtain correction matrixWithThe correcting variable filtering Unit 182, for filtering correcting variable in respiration interference, A, B and the k of recursion continuous 8 cardiac cycle_m, averageWithWherein A_iFor the A of i-th cardiac cycle, B_iIt is aroused in interest for i-th The B in cycle, K_miFor the K of i-th cardiac cycle_m。

Propagation time corrects unit 19, with two correction matrixs correct respectively it is related to systolic pressure and with diastolic pressure phase The ANOMALOUS VARIATIONS in the propagation time of pass.In the present embodiment, it is preferable that the propagation time correction unit 19 includes and systolic pressure phase The propagation time that the propagation time correction unit 191 of pass is related to diastolic pressure corrects unit 192.It is described related to systolic pressure Propagation time corrects unit 191, for correcting T_sma=T_sm(1-A_m).The propagation time correction unit related to diastolic pressure 192, for correcting T_dmb=T_dm(1-B_m)。

The computing unit 20, often fight pressure value for calculating pulse wave velocity and calculating according to Mathematical Modeling. In the present embodiment, it is preferable that the computing unit 20 include the pulse wave velocity computing unit 201 related to systolic pressure, The pulse wave velocity computing unit 202 related to diastolic pressure, systolic pressure computing unit 203, diastolic pressure computing unit 204, Mean arterial pressure computing unit 205.The pulse wave velocity computing unit 201 related to systolic pressure, for calculate with The related pulse wave velocity of systolic pressureL is the propagation distance of pulse wave；The pulse related to diastolic pressure Velocity of wave propagation computing unit 202, the pulse wave velocity related for calculating diastolic pressureThe systolic pressure meter Unit 203 is calculated, for calculating systolic pressureWherein k_ijAnd b_ijModel for all ages and classes and sex population is joined Number, i represents age, i=1,2 ..., n, n≤100；J represents sex, j=M/F, and M represents the model parameter of the male sex, and F is women Model parameter.The diastolic pressure computing unit 204, for calculating diastolic pressureThe mean arterial pressure meter Unit 205 is calculated, for calculating mean arterial pressure MAP=DBP+0.75K_mm(SBP-DBP)。

The human and machine interface unit 21, for being input into physiological parameter and showing continually varying pressure value and pulse wave, this In embodiment, it is preferable that the human and machine interface unit 21 includes physiological parameter input block 211, Dynamic Announce pressure value and arteries and veins Fight ripple unit 212.The physiological parameter input block 211, for being input into the physiology such as age, the sex and height ginseng of the measured Number.The Dynamic Announce pressure value and pulse wave unit 212, for showing often fight continually varying pressure value and pulse wave, and Blood pressure is provided in real time and gets over report from a liner police.

In the present embodiment, the correcting variable is extracted and respiration interference is extracted and filtered with correcting variable in filter unit 18 Method, comprises the following steps：

S1) pulse wave and analysis obtains the data below of ear pulse wave at ear under each cardiac cycle of real-time detection： The height h of aortic valve closing point on ear pulse wave_sd, i.e., the intersection that the systole phase is presented with diastole on ear pulse wave Highly, time in the systole phase t of ear pulse wave_s, unit is millisecond, the time diastole t of ear pulse wave_d, unit is millisecond, Maximum height h of ear pulse wave_max；

S2) pulse wave and analysis obtains the data below of toe pulse wave at toe under each cardiac cycle of real-time detection： Time in the systole phase t of toe pulse wave_s-toe, unit is millisecond, the time diastole t of toe pulse wave_d-toe, unit is millisecond, Maximum height h of toe pulse wave_max-toe, the time t of the starting point of toe pulse wave to crest midpoint_ch-toe, unit is in the least Second, the time t of the starting point of toe pulse wave to crest_max-toe, unit is millisecond；The crest midpoint refers to upper at crest Rise along turning point and the midpoint of trailing edge turning point；The definition at crest midpoint refers to document YAN CHEN, CHANGYUN WEN, GUOCAI TAO,and MIN BI《Continuous and Noninvasive Measurement of Systolic and Diastolic Blood Pressure by One Mathematical Model with the Same Model Parameters and Two Separate Pulse Wave Velocities》Understand.

S3) the pulse wave propagation time T related to diastolic pressure is calculated_dThe pulse wave propagation time T related to systolic pressure_s, Its definition refers to document YAN CHEN, CHANGYUN WEN, GUOCAI TAO, and MIN BI《Continuous and Noninvasive Measurement of Systolic and Diastolic Blood Pressure by One Mathematical Model with the Same Model Parameters and Two Separate Pulse Wave Velocities》Understand；H is the amplitude of ear pulse wave or toe pulse wave on y direction；

S4) using the data obtained by step S1, S2 under same cardiac cycle, it is calculated school under the cardiac cycle Positive variable；

S5) correcting variable under cardiac cycle is obtained according to step S4, is calculated correction matrix under the cardiac cycle；

S6 the correction matrix under multiple cardiac cycles) is continuously obtained, to the T obtained by step S3_dAnd T_sIt is corrected.

The method can be under real-time detection same cardiac cycle ear pulse wave and toe pulse wave, calculate pulse wave Propagation time, and the morphological feature extraction correcting variable according to pulse wave, acquisition correction matrix, to above-mentioned pulse wave propagation time Mutation be corrected, the propagation time after correction can be used for existing Mathematical Modeling, and each is continuously measured in the clinical setting The diastolic pressure and systolic pressure of cardiac cycle.

First correcting variable a₁：

The correcting variable obtained in step S4 includes the first correcting variable a₁, a₁Including a_1sAnd a_1d, a_1sAnd a_1dProperty Matter is identical and of different sizes, a_1dFor the low blood pressure state correction propagation time T related to diastolic pressure_dTwo classes change, a_1sWith In the low blood pressure state correction propagation time T related to systolic pressure_sTwo classes change；a₁The scope of application be a₁>0, a₁More it is big then Show that blood pressure is lower.

k_sd-m-0Represent h_sdWith the ratio of ear pulse wave systole phase average height.

When diastolic pressure is corrected, d_1-b=74～82, preferably 78.d_1-2-b=98～106, preferably 102.

If d_1-b≤k_sd-m-0≤d_1-2-b, then a_1d=(d_1-2-b-k_sd-m-0)×0.4；If k_sd-m-0<d_1-b, then a_1d=24 × 0.4；If k_sd-m-0>d_1-2-b, then a is made_1d=0.

When systolic pressure is corrected, d₁=76～84, preferably 80；d_1-2=104～112, preferably 108.

If d₁≤k_sd-m-0≤d_1-2, then a_1s=(d_1-2-k_sd-m-0)×0.50；If k_sd-m-0<d₁, then a_1s=28 × 0.50；If k_sd-m-0>d_1-2, then a_1s=0.

Second correcting variable a₂：

The correcting variable obtained in step S4 also includes the second correcting variable a₂, a₂Include a again_2sAnd a_2d, a_2sAnd a_2d Property it is identical and of different sizes, a_2dChange procedure for hypertensive state and from normal arterial pressure state to hypertensive state The middle correction propagation time T related to diastolic pressure_dTwo classes change, a_2sFor hypertensive state and from normal arterial pressure state to The pulse wave propagation time T related to systolic pressure is corrected in the change procedure of hypertensive state_sTwo classes change；a₂Applicable model Enclose for a₂>0, a₂It is more big, show that diastolic pressure or systolic pressure are higher.

k_sd-m-tsRepresent h_sdWith ear pulse wave diastole t_s-2t_sThe ratio of section average height.k_sd-m-2Represent h_sdWith ear pulse wave 0-2t_sThe ratio of section average height.

If | k_sd-m-0-k_sd-m-ts| >=40 and (k_sd-m-0+k_sd-m-ts)/2≥k_sd-m-2, then k_sd-m=2 × k_sd-m-2- (k_sd-m-0+k_sd-m-ts)/2, otherwise k_sd-m=k_sd-m-2；

During correction diastolic pressure, d_2-b=1.33～1.43, preferably 1.38.

If k_sd-m>(d_2-b+ (age-14)/15/100), wherein age is the age,

Then a_2d=(k_sd-m-(d_2-b+(age-14)/15/100))×0.5；

If k_sd-m≤(d_2-b+ (age-14)/15/100), then make a_2d=0.

During correction systolic pressure, d₂=1.17～1.27, preferably 1.22.

If k_sd-m>(d₂+ (age-14)/15/100), then a_2s=k_sd-m-(d₂+(age-14)/15/100)。

If k_sd-m≤(d₂+ (age-14)/15/100), then make a_2s=0.

3rd correcting variable a₃：

The correcting variable obtained in step S3 also includes the 3rd correcting variable a₃, a₃For changing or passing in blood volume To T in the state of sensor installation site Temperature changing_dAnd T_sIt is corrected.

For ear pulse wave diastole average height and maximum height h_maxRatio.

If k_sd-m-ts≤d_3-2, it is right to needIt is modified, correction result is designated as

IfThend₃ =0.02～0.14, preferably 0.08；d_3-2=1.21～1.31, preferably 1.26.

For toe pulse wave diastole average height and maximum height h_max-toeRatio, t_s-toeRepresent the paradoxical expansion time recognized on toe pulse wave, t_d-toeRepresent and recognized on toe pulse wave Time diastole.IfThen

If the waveform of pulse wave diastole morphs, to k_d-m-aEnter Row correction.

If | k_sd-m-0-k_sd-m-ts| >=40 and (k_sd-m-0+k_sd-m-ts)/2≥k_sd-m-2And k_sd-m-ts≥d_3-2,

Then

If c₄<k_d-m-a<c₅, then a is made₃=0.c₄=(d₄+ (age-14)/8)/100, d₄=23～35, preferably 29；c₅= (d₅+ (age-14)/8)/100, d₅=27～39, preferably 33.

If k_sd-m-0<d₆Or k_sd-m-2>d₇, then a is made₃=0.d₆=0.97～1.03, preferably 1.00；d₇=1.52～ 1.58, preferably 1.55.

If k_sd-m-0≥d₆+ 0.10 and k_sd-m-2≤d₈And k_d-m-a≤c₄, then a₃=(c₄-k_d-m-a)×67/100。d₈= 1.42～1.48, preferably 1.45.

IfOrThen a₃=(c₄-k_d-m-a)×50/100；

If k_sd-m-0≥d₆+ 0.10 and k_sd-m-2≤d₈And k_d-m-a≥c₅, then a₃=(c₅-k_d-m-a)×62/100；

IfOrThen a₃=(c₅-k_d-m-a)×45/100。

4th correcting variable a₄：

The correcting variable obtained in step S4 also includes the 4th correcting variable a₄, a₄In the case where periphery blood vessel dilatation causes In the case that limb blood pressure (relative to radial artery blood pressure) is reduced, to T_dAnd T_sIt is corrected, a₄The scope of application be a₄>0, a₄It is bigger Show blood pressure of lower extremities relative to radial artery blood pressure drop is low must be more.

If t_max-toe≥t_ch-toe, thenOtherwise k_s-t-toeFor the ratio of time and the Syst time of toe pulse wave starting point to crest, 200 is adjustment factor.If k_s-t-toe> 0.8, then a₄=k_s-t-toe-0.8.If k_s-t-toe≤ 0.8, a₄It is inapplicable, then make a₄=0.

5th correcting variable a₅；

The correcting variable obtained in step S4 also includes the 5th correcting variable a₅, a₅Effect and property and a₄With phase Together, in the case where blood pressure of lower extremities is low relative to radial artery blood pressure drop to T_dAnd T_sIt is corrected.

k_s-m-toeFor toe pulse wave systole phase average height and maximum height h_max-toe Ratio；

If k_s-m-toe<d₉, then a is made₅=0.d₉=0.67～0.73, preferably 0.7.

If k_s-m-toe≥d₉And k_s-t-toe>=0.8, then a₅=k_s-m-toe-d₉。

If k_s-m-toe≥d₉And k_s-t-toe<0.8, then a₅=(k_s-m-toe-d₉)/2。

6th correcting variable a₆；

The correcting variable obtained in step S4 also includes the 6th correcting variable a₆, a₆Represent two pulse wave areas Relative change, for toe blood vessel dilatation, blood pressure of lower extremities relative to radial artery blood pressure drop it is low when to T_dAnd T_sIt is corrected.a₆'s The scope of application is a₆>0；

k_s-m-toe-earFor the Syst face of toe pulse wave Product and the Syst area ratio of ear pulse wave, 100 is adjustment factor.

Work as k_s-m-toe-ear<1.0, then make a₆=0.

Work as k_s-m-toe-ear>1.08, then make c₆=1.08.

If t_s>220 and k_sd-m-0>0.88, then a₆=c₆-1.0。

If t_s<160 or k_sd-m-0<0.80, then a₆=(c₆-1.0)×0.34。

If 160<t_s≤ 220 or 0.80<k_sd-m-0≤ 0.88, then a₆=(c₆-1.0)×0.67。

As 1.0≤k_s-m-toe-ear≤ 1.08, then c₆=k_s-m-toe-ear-1.0。

If t_s>220 and k_sd-m-0>0.88, then a₆=c₆。

If t_s≤ 160 or k_sd-m-0≤ 0.80, then a₆=c₆×0.34。

If 160<t_s≤ 220 or 0.80<k_sd-m-0≤ 0.88, then a₆=c₆×0.67。

7th correcting variable a₇；

The correcting variable obtained in step S4 also includes the 7th correcting variable a₇, a₇Effect and property and a₆With phase Together, a₇Represent the relative change of two pulse wave systole phase width (time in systole phase).

k_ts-toe-earFor the time of the paradoxical expansion of identification and ear on toe pulse wave The ratio of the Syst time recognized on pulse wave, 825 is adjustment factor；k_ts-toe-earIncrease prompting toe blood vessel dilatation, under Limb blood pressure is pressed in reduction relative to radial artery blood.

Work as k_ts-toe-ear<1.0, then make a₇=0.

Work as k_ts-toe-ear>1.08, then make c₇=1.08.

If t_s>220 and k_sd-m-0>0.88, then a₇=c₇-1.0。

If t_s<160 or k_sd-m-0<0.80, then a₇=(c₇-1.0)×0.34。

If 160<t_s≤ 220 or 0.80<k_sd-m-0≤ 0.88, then a₇=(c₇-1.0)×0.67。

As 1.0≤k_ts-toe-ear≤ 1.08, then c₇=k_ts-toe-ear-1.0。

If t_s>220 and k_sd-m-0>0.88, then a₇=c₇。

If t_s≤ 160 or k_sd-m-0≤ 0.80, then a₇=c₇×0.34。

If 160<t_s≤ 220 or 0.80<k_sd-m-0≤ 0.88, then a₇=c₇×0.67。

Variable k_m：

Ear pulse wave systole phase average height and maximum height h_maxRatio；

The ear pulse wave of systole phase and diastole The compound average of the relative altitude of relative altitude and toe pulse wave, for calculating mean arterial pressure.

Correction matrix for diastolic pressure, in step S5If wherein there is a_id=0 Or a_iThe a is represented when=0_idOr a_iIt is inapplicable.Step S6 is specially：The correction matrix under 8 cardiac cycle is continuously acquired, The interference of respiration wave, 8 variables is overcome to choose using recursion mode, often count with the mean value of the variable of 8 cardiac cycle Calculate a newest variable and just eliminate an oldest variable.Bearing calibration is：T_dmb=T_dm(1-B_m)；Wherein,B_iFor the correction matrix under i-th cardiac cycle, T_diFor under i-th cardiac cycle T_d。

Correction matrix for systolic pressure, in step S5If wherein there is a_is=0 Or a_iThe a is represented when=0_isOr a_iIt is inapplicable.Step S6 is specially：The correction matrix under 8 cardiac cycle is continuously acquired, The interference of respiration wave, 8 variables is overcome to choose using recursion mode, often count with the mean value of the variable of 8 cardiac cycle Calculate a newest variable and just eliminate an oldest variable.Bearing calibration is：T_sma=T_sm(1-A_m)；Wherein,A_iFor the correction matrix under i-th cardiac cycle, T_siFor i-th cardiac cycle Under T_s。

Finally it should be noted that：Various embodiments above only to illustrate technical scheme, rather than a limitation；To the greatest extent Pipe has been described in detail with reference to foregoing embodiments to the present invention, it will be understood by those within the art that：Its according to So the technical scheme described in foregoing embodiments can be modified, either which part or all technical characteristic are entered Row equivalent；And these modifications or replacement, do not make the essence disengaging various embodiments of the present invention technology of appropriate technical solution The scope of scheme, it all should cover in the middle of the claim of the present invention and the scope of specification.

Claims (10)

1. a kind of high accuracy continuous non-invasive blood pressure measuring device for possessing adaptive calibration, it is characterised in that include：

Control unit:For sending control signal, the drive signal of sensor driving and signal conversion unit, and pulse are adjusted The DC level and multiplication factor of ripple detector unit output signal；

Sensor drives and signal conversion unit, for the luminous tube and light of detection ear and the sensor of toe pulse wave Pipe provides drive signal, and the output signal of light-receiving tube is converted into voltage signal；

Pulse wave detector unit, for being filtered to voltage signal and amplifying；

Pulse wave is sampled and recognition unit, and the two paths of signals to processing through pulse wave detector unit synchronizes sampling, is obtained Data signal, and the waveform segment to ear in data signal and toe is identified；

Propagation time recognizes and filter unit, for being respectively obtained and systolic pressure phase according to the time difference of ear and toe waveform segment The propagation time of pass and the propagation time related to diastolic pressure, and the respiration interference to the propagation time carries out smothing filtering；

Correcting variable is extracted and filter unit, for extracting correcting variable from ear pulse wave and toe pulse wave, is obtained Correction matrix, and the respiration interference to correcting variable carries out smothing filtering；

Propagation time corrects unit, using correction matrix correct respectively propagation time related to systolic pressure and with diastolic pressure correlation Propagation time ANOMALOUS VARIATIONS；

Computing unit, for calculating pulse wave velocity and pressure value of often fighting；

Human and machine interface unit, for being input into physiological parameter and showing continually varying pressure value and pulse wave.

2. the high accuracy continuous non-invasive blood pressure measuring device for possessing adaptive calibration according to claim 1, its feature It is that the sensor drives and signal conversion unit includes：

Luminous tube driver element, for providing corresponding electric current to luminous tube according to body measurements；

Light-receiving tube drives and detector unit, for providing reverse bias voltage to light-receiving tube, and is believed according to the control of control unit Number the output signal of light-receiving tube is converted into voltage signal；

Signal conversion unit, for filtering off voltage signal in reverse bias voltage.

3. the high accuracy continuous non-invasive blood pressure measuring device for possessing adaptive calibration according to claim 2, its feature It is that the reverse bias voltage is produced by measuring circuit or float power.

4. the high accuracy continuous non-invasive blood pressure measuring device for possessing adaptive calibration according to claim 1, its feature It is that the pulse wave detector unit includes：

Differential amplification unit, for being amplified to voltage signal, eliminates common mode disturbances；

Bandpass filtering unit, for being filtered to voltage signal, filtered band is 0.1～30Hz；

Gain adjustment unit, for adjusting multiplication factor according to the control signal of control unit.

5. the high accuracy continuous non-invasive blood pressure measuring device for possessing adaptive calibration according to claim 1, its feature It is that the pulse wave sampling and recognition unit include：

Pulse wave sampling unit, for synchronizing continuous sampling to the two paths of signals processed through pulse wave detector unit, obtains Obtain continuous data signal；

Pulse wave recognition unit, for obtaining ear and the corresponding ripple of toe pulse wave in each cardiac cycle from data signal Shape section and wave character.

6. the high accuracy continuous non-invasive blood pressure measuring device for possessing adaptive calibration according to claim 1, its feature It is that the propagation time identification and filter unit include：

Pulse wave propagation time recognition unit, for according to the waveform segment of ear and toe pulse wave in same cardiac cycle point Do not obtain the propagation time T related to diastolic pressure_dThe propagation time T related to systolic pressure_s；

Pulse wave propagation time filter unit, for filtering off the respiration interference in the propagation time, recursion continuous 8 cardiac cycle T_sAnd T_d, calculate mean valueWithWherein T_siFor the T of i-th cardiac cycle_s, T_diFor i-th The T of individual cardiac cycle_d。

7. the high accuracy continuous non-invasive blood pressure measuring device for possessing adaptive calibration according to claim 1, its feature It is that the correcting variable is extracted and filter unit includes：

Correcting variable recognition unit, for extracting correcting variable a from ear pulse wave and toe pulse wave₁～a₇And K_m, its Middle a₁Including a_1sAnd a_1d, a₂Including a_2sAnd a_2d, obtain correction matrixWith

Correcting variable filter unit, for filtering correcting variable in respiration interference, the A, B of recursion continuous 8 cardiac cycle And K_m, averageWithWherein A_iFor the A of i-th cardiac cycle, B_iFor the B of i-th cardiac cycle, K_miFor the K of i-th cardiac cycle_m。

8. the high accuracy continuous non-invasive for possessing adaptive calibration according to claim 1 measures blood pressure device, its feature It is that the propagation time correction unit includes：

The propagation time correction unit related to systolic pressure, for correcting T_sma=T_sm(1-A_m)；

The propagation time correction unit related to diastolic pressure, for correcting T_dmb=T_dm(1-B_m)。

9. the high accuracy continuous non-invasive blood pressure measuring device for possessing adaptive calibration according to claim 1, its feature It is that the computing unit includes：

The pulse wave velocity computing unit related to systolic pressure, for calculating the pulse wave velocity related to systolic pressureL is the propagation distance of pulse wave；

The pulse wave velocity computing unit related to diastolic pressure, the pulse wave velocity related for calculating diastolic pressure

Systolic pressure computing unit, for calculating systolic pressureWherein k_ijAnd b_ijFor all ages and classes and sex population Model parameter, i represents age, i=1,2 ..., n；n≤100；J represents sex, j=M/F, and M represents the model parameter of the male sex, F For the model parameter of women；

Diastolic pressure computing unit, for calculating diastolic pressure

Mean arterial pressure computing unit, for calculating mean arterial pressure MAP=DBP+0.75K_mm(SBP-DBP)。

10. the high accuracy continuous non-invasive blood pressure measuring device for possessing adaptive calibration according to claim 1, its feature It is that the human and machine interface unit includes：

Physiological parameter input block, for being input into the age, sex and height of the measured；

Pressure value and pulse wave display unit, for display of blood pressure value and pulse wave, and in real time offer blood pressure gets over report from a liner police.