CN109846464A - The system for non-invasive measurement and data processing system of blood flow mechanics parameter - Google Patents
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Abstract
The present invention discloses the data processing system of blood flow mechanics parameter, is used to collect the data of blood flow mechanics parameter measuring apparatus measurement, and the data processing for rower quasiconfiguaration of going forward side by side forms the available data information format of medical worker.The data processing system of the blood flow mechanics parameter includes data collection conversion interface module, data normalization module and data mining module；The data collection conversion interface module can collect the raw measurement data that a variety of different blood flow mechanics parameter measuring apparatus measurements obtain；The data normalization module can convert the standard measurement data to by calculation processing the blood flow mechanics supplemental characteristic of medicine；The blood flow mechanics supplemental characteristic merger can be blood flow state level data according to data mining rule by the data mining module.The beneficial effects of the present invention are: the diagnosis efficiency of doctor is improved, the brain burden of doctor is mitigated.
Description
Technical field
The present invention relates to the technical fields (A61B 5/026) for measuring blood flow for diagnostic purposes, and the invention particularly relates to blood
The system for non-invasive measurement of flow dynamic parameter；The invention further relates to be specially adapted at the numerical calculation or data of specific application
The equipment or method (G06F 19/00) of reason, the invention particularly relates to the data processing systems of blood flow mechanics parameter.
Background technique
The research of noninvasive hemodynamic parameter measuring device is at home and abroad research hotspot in field, wherein more with ultrasound
Based on Pu Le measurement and biological impedance two major classes.
Noninvasive hemodynamic parameter measuring device
Ultrasonic doppler measurements: the more of use is through esophageal dysplasia instrument.The instrument is using individually super
Sonic probe, after being sent into testee's oesophagus, acoustic beam passes through the through left side of esophageal wall, has atrium and other cardiac structures, can show a left side
Coronary artery master in and left anterior descending branch, left Circumflex branch proximal end and arteria coronaria dextra tangent plane picture.Available color Doppler simultaneously
Technology observes wherein hemodynamic state, and measure flow velocity, blood flow phase with pulse Doppler spectrum and ask the phase etc..This method
The drawbacks of be ultrasonic probe enter postesophageal measurement position on result influence it is very big, therefore operator is required it is excessively high, one
As medical practitioner need to have 5 years or more operating experiences and could skillfully use, data acquired unstable result, and instrument cost
Cost is excessively high.
CT angiography: as a kind of woundless testing technology, CT angiography three-dimensional reconstruction image can make up crosspiece
The limitation of bit scan, polyaxial multi-angle observation lesion；In addition, cheap expense and easy operation connect it easily by patient
By.But be limited in that: CT angiography is only capable of providing anatomic information, judges form, the degree of mobility of vena portae hepatica
And situations such as Doppler flow mapping, it can not direct quantitatively evaluating hemodynamic parameter.
Magnetic resonance angiography: this method gradually shows in the advantage of detection portal system hemodynamics information.Magnetic
Resonance angiography can not only show the Doppler flow mapping and spatial relationship of portalsystem, can also be to flow velocity, the flow amount of progress
Change analysis.However, the every analytical technology applied at present can not still quantify to obtain pylic pressure index, expensive diagnosis
Expense also limits its clinical application to a certain extent.
Biological impedance: the more of use is thoracic impedance measuring instrument.The measurement method is similarly originated from aviation
Space flight medical technology is proposed at first by US National Aeronautics and Space Administration NASA.Its working principle is that: because aorta full of blood,
Electrical conductivity is best, is the shortest path that electric signal conducts in thoracic cavity, therefore electric current penetrates sweat gland along backbone direction in aorta
Interior conduction.According to the impedance variation amount of the aorta measured, " stroke output " (SV) of heart is estimated using formula, in turn
Derive other hemodynamic parameters.The drawbacks of this method is low measurement accuracy, and instrumental sensitivity is poor, and technical principle is recognized
It can spend not high.
Demand in cardiovascular disease early diagnosis and therapy field, there is an urgent need to a kind of relatively accurate and can
With the Medical Devices detected under the conditions of noninvasive to cardiovascular function status.
Patent document CN1221325A, which is disclosed, a kind of determines heart rate, heartbeat according to thoracic bioimpedance signals and electrocardiogram
The method and apparatus of amount and heartbeat amount of bleeding.Using a kind of unique bio-impedance electrode arrangement, pass through measurement or detecting electrode
Identification distortion is made gain-phase-frequency distortion to bioimpedance signal using sinusoidal test signal and is corrected, in actual measurement
Period makees same correction.Using the time-derivative of bioimpedance signal, power spectrum is calculated, using the prominent heart of automatic convolution method
Rate of fighting harmonic wave.Removal respiratory wave and other signals for not indicating heart of patient circulation.Left ventricle is exported according to bioimpedance signal
Ejection time.Stroke volume is exported using improved Kubicek equation, thus exports heartbeat amount of bleeding.
Patent document CN103517670B discloses that disclosed herein is the device and method for measuring bioimpedance signal.One
Aspect may include head type headphones device, and the head type headphones device includes retainer and electrode.The retainer can be matched
It sets and the electrode is placed on the head of subject, to obtain instruction hemodynamic situation relevant to the area MCA
Bioimpedance signal.Processor can be included to measure and analyze bioimpedance signal obtained, and export for predicting
The information of hemodynamic situation relevant to the area MCA.
Patent document CN102579017A is disclosed the present invention relates to a kind of medical instrument, specifically discloses a kind of noninvasive blood flow
Kinetic parameter analyzer.It is mainly made of computer module and measurement module two parts, and the measurement module includes: sleeve
Band, micro-compressor, accumulator, operated pneumatic valve, pressure sensor, preamplifier, low-pass filter, gain amplifier, with
And analog-digital converter and single-chip microcontroller.The present invention acquires signal using pressure sensor, and single-chip microcontroller and computer real-time communication are handed over
Data are changed, are analyzed using the preset algorithm of computer, multinomial human bloodstream can be obtained within (30~40 seconds) in a short time
Kinetic parameter.The correlation of the obtained parameter of Non-invasive detection of the present invention and the invasive method of tradition is very good, data it is accurate and
Stablize.
Patent document CN104107039A discloses the present invention and provides a kind of Portal vein flow dynamics evaluation method and pressure
Parameter detecting technology, comprising the following steps: 1. utilize thin-layer CT image, construct the 3-D geometric model of vena portae hepatica；2. with stream
The finite element method of mechanics software for calculation ANSYS will establish out 3-d mathematics mould after above-mentioned geometrical model grid dividing
Type；3. simulation calculates pylic hemodynamic parameter, speed and pressure distributed effect figure are obtained.Method safety of the invention
Noninvasive, easy to operate, intuitive quantization and accuracy height, establish the valid model for scientific research and clinical service.
Heart impedance blood flow chart --- ICG
Electricity consumption bio-impedance technique measures cardiac output, judges the non invasive method of cardiac function.
The entitled heart impedance blood flow chart of Chinese, the entitled impedance cardiogram of foreign language, the entitled ICG of English letter.
Heart impedance blood flow chart is also known as impedance cardiogram.It is electricity consumption bio-impedance technique measurement cardiac output, judges cardiac function
Non invasive method.With electrocardiogram, caardiophonogram, carotic pulse graph synchronous recording can also measure heart contraction and diastolic time
Interphase, vascular compliance and total peripheral resistance etc..Compared with invasive methods, ICG have hurtless measure, it is safe and simple, can connect
It the advantages that continuous dynamic observation, has the certain significance to the diagnosis of certain cardiovascular diseases, observation of curative effect, Index for diagnosis etc., does not lose still
Its application value.
Heart impedance blood flow chart has the certain significance to the diagnosis of certain cardiovascular diseases, observation of curative effect, Index for diagnosis etc.
The RM-6000 type polygraph that determining instrument is produced for example, by using Japanese photoelectricity, with the matched PI- of the machine
600G and EQ-600G impedance and differentiating amplifier plug-in unit.If using domestic equipment, such as the thousand limited public affairs of sail Medical Instruments of Shenzhen
Noninvasive hemodynamic detection system CSM3100, the Ying Fuhe State Pharmaceutical Administration standard of department, in order to avoid measurement error.
The basic principle of heart impedance blood flow chart causes the variation of electrical impedance when being based on organism variation.Thoracic tissues are to lead
Electric body, places electrode at its both ends, inputs frequency low-amplitude constant electric current to chest by electrode on line, due to heart contraction and relaxes
Open cyclic activity.Cause thoracic cavity blood flow generating period to change, cause thoracic cavity resistance in periodically-varied, leads life with more
Reason recorder is traced out, is exactly heart impedance blood flow chart or impedance rheogram (△ z).Blood is good electric conductor, heart
When contraction, blood is injected in aorta, expands aorta lumen, and sectional area increases, and blood volume increases, therefore resistance reduces；Conversely,
When diastole, blood returns to heart, aorta lumen retraction, and sectional area reduces, and volumetric blood reduces, and increases resistance.From upper
It states as can be seen that the size of cardiac impedance and the size of aorta lumen volume are inversely proportional.Kubicek etc. confirms that when left ventricular ejection is hindered
It is inversely proportional between the maximum C (dz/dtmax) and aortic blood flow of anti-rate of change.Thus, it is supposed that thoracic cavity is cylindrical body, root
According to the thoracic cavity blood resistivity (ρ) length (two electrode spacing L of E2 to E3), basal impedance ZO, derivative of impedance wave C (dz/dt max)
Wave amplitude and time (T) five Fundamentals calculate cardiac output (SV), claim Kubicek formula, the heart calculated is defeated
Output result correlation compared with invasive methods is good.
ICG measuring and operating method is as follows:
(1) height, weight and blood pressure are measured；
(2) it makes even clinostatism, rest 10min, whole-body muscle loosens, dispels misgivings；
(3) couple impedance electrodes: it is general using cyclic annular four electrode method, with ethanol skin, by a pair of electrodes (E1-E2)
It encloses in neck root, another pair electrode (E3-E4) encloses, elastic appropriateness horizontal in ensiform process of sternum lower edge.Two lateral electrodes (E1,4) are
For galvanic electrode, couple with impedance instrument, to supply 100kHz frequency low-amplitude continuous current；Two medial electrodes (E2,3) are to detect electricity
Pole is connected with the amplifier of impedance instrument, traces cardiac impedance waveform, measures L (E2-E3 spacing) length.
(4) adjust impedance instrument: adjusting calibration ZO is 30 Ω, and (ZO value should be in 20~35 Ω for record thoracic cavity basal impedance ZO value
Between) and calibration square wave (calibration) and baseline etc..
(5) record figure: use polygraph, with 50~100mm/s chart speed synchronous recording electrocardiogram, caardiophonogram,
Total impedance figure (△ z) and impedance differential map (dz/dt) 5~10 cardiac cycle, take its mean value.
The normal figure of ICG and its meaning are as follows:
(1) total impedance figure △ Z: total impedance figure includes that A wave, C involve V wave, and clinical meaning is little, only refers to, generally
It does not measure.
(2) cardiac impedance differential map (dz/dt)
1. A wave (Adz/dt), also known as room contracting wave.It is located at after P wave of electrocardiogram, corresponding with fourth heart sound (S4),
It generates related with atrial contraction.The variation of main reflection left ventricular end-diastolic volume, is the index for evaluating left room compliance.Normal person
A wave-amplitude≤1/3c wave when increasing, prompts left room compliance to decline.
2. C wave (Cdz/dt), also known as room contracting wave.It is located at after ECG-QRS Wave, is that wave amplitude is maximum in differential map
Wave, generates and master when ventricular contraction, that pulmonary artery penetrates blood is related.Normal person's C wave-amplitude is 1.5~3 Ω/s.Work as myocardial contraction
Power enhancing, C wave increases when cardiac output increases, and vice versa.When ventricular contraction is uncoordinated, C wave may occur in which incisura or bimodal.
3. O wave (Odz/dt), also known as room Shu Bo.It is located at after ECG T wave, O point and caardiophonogram left room room with ACG
Valve Opening Snap (OS) is corresponding.O wave represents left atrioventricular valve and opens, and ventricle starts to fill.It reflects diastole early stage ventricular volume
Variation and Ventricular diastolic function state.Normal person's O wave-amplitude 4C wave, if amplitude increases, even > C wave then prompts Zuo Xingong
It can decline.
4. B point: for ventricular ejection initial point.It is the starting point of C wave, represents semilunar valve and opens, ventricle starts to penetrate blood.If B
Chu is lost count of, 15% height correction of C wave need to be used.
5. X point: for ventricular ejection terminal.It is located at after C wave, is the highest point of cardiac impedance differential map (dz/dt), with the heart
Sound figure aorta petal ingredient (A2) is corresponding, and representing left ventricular ejection terminates.
6. Y point: closing point for pulmonary valve.It is located at after X point, corresponding with pulmonary valve composition (P2), represents the right side
Ventricular ejection finishes.
7. E point: for the full point of ventricle.It is located at after O wave, corresponding with caardiophonogram S3, represents ventricle and quickly fills
Phase terminates the index point started with slow filling period.
The blood flow mechanics supplemental characteristic that measurement is obtained carries out computer disposal, to facilitate doctor or medical staff to make
With related content disclosed in the prior art is as follows:
It is a kind of encephalic vertebral-basilar artery Hemodynamic analysis side that patent document CN102370475B, which discloses the present invention,
Method.According to the clinical imaged image of encephalic vertebral-basilar artery blood vessel, anatomical model is established, the present invention devises encephalic vertebra-substrate
Artery physical model, and thereby establish corresponding governing equation.It, can be by measuring intracranial segment vertebral-basilar artery by equation
Geometric parameter, lumen diameter and the boundary condition of inlet of section, find out the blood flow velocity of the inlet of vertebral-basilar artery, ask
The Hydrodynamic character parameter of each vessel segment out.It is devised according to the above method by nuclear magnetic resonance technique and fluid dynamic credit
Analyse the analysis instrument of software composition.The present invention has very encephalic vertebral-basilar artery Hemodynamics Study and clinical guidance
Significance.
Patent document CN107992452A, which discloses the present invention and provides a kind of calculating central hemodynamics, refers to calibration method, dress
It sets, storage medium and equipment.It wherein calculates central hemodynamics and refers to calibration method, include the following steps: the upper arm using acquisition
Arterial pressure demarcates the radial artery pulse wave signal of acquisition, obtains radial artery wave shape；According to the pressure of the radial artery
Reeb shape predicts central aortic waveform morphology using linear regression model (LRM)；According to the central aortic waveform morphology, selection is corresponded to
The transmission function of the radial artery wave shape to central aortic pressure wave shape the oar is utilized according to the transmission function
Arterial pulse wave signal reconstruction central aortic pressure wave shape；Central hemodynamics are calculated according to the central aortic pressure wave shape
Index.Present invention only requires extract radial artery pulse wave to obtain the hemodynamic indexs such as central aortic pressure, radial artery
Pulse wave is more stable and is easy to extract, and security risk is not present in human test.
Patent document CN102622501B disclose the invention discloses a kind of hemodynamic parameter management method, system and
Custodial care facility, which comprises the preset one or more functions group template corresponding with illness of load；From each function
Selected hemodynamic parameter included by the functional group is obtained in group template；From each hemodynamic parameter of real-time monitoring
The parameter information of selected hemodynamic parameter is obtained in database；According to same monitoring time in parameter information statistical function group
The selected hemodynamic parameter of exception unusual condition；By the selected hemodynamic parameter of monitoring time same in functional group
Unusual condition compared with preset rules, determine the functional group in the display mode of the monitoring time；According to determining display side
Formula shows the map that each functional group changes over time.The present invention be conducive to doctor faster find, more acurrate diagnosis status of patient or
Person's disease.
Patent document CN1592595A disclose the invention discloses from central venous pressure (CVP), mean arterial pressure (MAP),
Heart rate (HR) and core temperature (T) press relation of plane formula measurement mean pulmonary arterial pressure (MPAP), average pulmonary capillary wedge pressure
(MPCWP) and the method or equipment of cardiac index: MPAP=(a × MAP)+CVP (for MAP < 58), Va；Or MPAP=(a
× MAP)+CVP-10 × INT [(MAX { (MAP-109), (CVP-7), 0 })/10]) (for MAP > 58), Vb；MPCWP
=(b × MPAP)+CVP-10 × INT [CVP-7/10], VI；And CI=K (TCVP/HR2), VII；Wherein a and b are about
0.15；It is maximum in MAX (x, y, z)=x, y and z this three；INT [x]=x integer part；MAP and CVP is carried out with mmHg
Measurement；T is degree Celsius；And HR is number/minute；CI is liter/square m/min；And K is variable constant, value depends on
The value of CVP and HR is 0~1000.
Patent document CN107785081A, which discloses the present invention and provides a kind of calculating central hemodynamics, refers to calibration method, dress
It sets, storage medium and equipment.It wherein calculates central hemodynamics and refers to calibration method, include the following steps: the upper arm using acquisition
Arterial pressure demarcates the radial artery pulse wave signal of acquisition, obtains radial artery wave shape；According to the pressure of the radial artery
Reeb shape predicts central aortic waveform morphology using linear regression model (LRM)；According to the central aortic waveform morphology, selection is corresponded to
The radial artery wave shape and central aortic pressure wave shape between transmission function institute is utilized according to the transmission function
State radial artery pulse wave signal reconstruction central aortic pressure wave shape；Center blood flow is calculated according to the central aortic pressure wave shape
Mechanical index.Present invention only requires extract radial artery pulse wave to obtain the hemodynamic indexs such as central aortic pressure, oar
Arterial pulse wave is more stable and is easy to extract, and security risk is not present in human test.
Patent document CN104010566B, which is disclosed, describes the methodology of the hardware and software for health of heart measurement.It obtains
The various haemodynamics waveforms of the subject taken are analyzed, with intrinsic in two regions of calculating or approximate bridging dicrotic pulse
Frequency.Intrinsic frequency provides measurement/measurement about subject's health of heart.System can be used to monitoring situation and/or by
For diagnosing.Exemplary use includes, and identifies the presence of (diagnosis) following situations: cardiac arrhythmia, heart failure, atrial fibrillation,
The necessity of aneurysm, hemadostewnosis or aortic valve dysfunction and valve implantation；And/or monitoring congestive heart failure
Development；Together with combine it is daily to it is any the fact that test, identify the emergency of hospitalization.
For this purpose, being that the present invention will solve as how economical and effective mode carries out non-invasive measurement to blood flow mechanics parameter
One of certainly the technical issues of.Another technical problem to be solved by the present invention is that using the blood flow mechanics for being different from the prior art
The computer processing method of supplemental characteristic, by doctor from complicated memory with judge to free in mental labour.
Therefore, the system for non-invasive measurement and data processing system of the blood flow mechanics parameter different from the prior art are designed
System is still the R&D direction of those skilled in the art.
Summary of the invention
For overcome the deficiencies in the prior art, it is an object of the present invention to propose the noninvasive of blood flow mechanics parameter
Measurement method, system, can be unable to human body generate traumatic operation in the case where, it is accurate and effective, widely measure it is more
Cardiovascular blood flow mechanics parameter of a human body provides strong help for the diagnosis of doctor.
The second object of the present invention is to propose the data processing method and system of blood flow mechanics parameter, uses and count
It calculates program and provides criterion rule according to the present invention to calculate analysis and handle large number of blood flow mechanics supplemental characteristic, obtain
The seldom intermediate parameters data result of quantity, doctor can easily be used for clinic according to these a small amount of intermediate parameters, improve
The diagnosis efficiency and accuracy rate of doctor, mitigates the brain burden of doctor.
An object of the present invention adopts the following technical scheme that realization: the non-invasive measurement system of the blood flow mechanics parameter
System includes display device, printing equipment, human body resistance anti-detection devices, eight core conducting wires and four pairs of electrode slices；
The human body resistance anti-detection devices is electrically connected by the eight cores conducting wire with four pairs of electrode slices；
The human body resistance anti-detection devices can apply constant high-frequency current by a narrow margin to four pairs of electrode slices ---
Electric current is referred to as detected, since aorta and heartbeat cause thoracic cavity blood flow generating period to change, causes thoracic cavity resistance
Anti- is in periodically-varied, thus, the human body resistance anti-detection devices can note down and output impedance differential cardiogram, and according to
The blood flow mechanics parameter is obtained by calculation in the differential cardiogram aroused in interest；
The display device and the printing equipment are connect with the human body resistance anti-detection devices data communication；
The display device includes display screen, for showing that measurement obtains in a manner of data form or data coordinates figure
Blood flow mechanics parameter；
The printing equipment can print the data form or data coordinates figure.
The second object of the present invention adopts the following technical scheme that realization: the data processing system of blood flow mechanics parameter,
Its data for being used to collect the measurement of blood flow mechanics parameter measuring apparatus, the data processing for rower quasiconfiguaration of going forward side by side form doctor
The available data information format of business personnel, it is characterised in that: the data processing system of the blood flow mechanics parameter includes number
According to collection conversion interface module, data normalization module and data mining module；
The data collection conversion interface module can collect a variety of different blood flow mechanics parameter measurement dresses
The raw measurement data that measurement obtains is set, and is converted into the data mode that the data normalization module can identify --- it is known as
Standard measurement data；The raw measurement data is measured under two kinds of positions and is obtained: the first position: end sitting position or the position that lies low, always
Body characteristics are that human heart is equivalent to lower limb and is in the first high position；Second position: compared to the first position, general characteristic is people
Systemic heart is equivalent to lower limb and is in the second lower position；
The data normalization module can convert the standard measurement data to by calculation processing the blood of medicine
Hydromechanics supplemental characteristic；
The data mining module can be regular according to data mining, be by the blood flow mechanics supplemental characteristic merger
Blood flow state level data.
Use the packing method of above mentioned goods packing device, comprising the following steps:
The other technical solutions of according to the present invention/invention can also include following one or more technical characteristics.As long as
The combination of such technical characteristic be it is enforceable, the new technical solution thus formed belongs to the present invention/invention one
Point.
Compared with prior art, the beneficial effects of the present invention are:
Human body wound is not generated to human body in measurement process, measurement is convenient, efficient, accurate；
The diagnosis efficiency and accuracy rate for improving doctor, mitigate the brain burden of doctor；
Be conducive to propagate and extension expert's diagnostic experiences and knowledge in medical health system；
Various haemodynamics data parameters electronizations are stored, convenient for subsequent further scientific research analysis；
By big data analysis, the haemodynamics data normal distribution range for being suitble to all kinds of ethnic groups is found.
Detailed description of the invention
Referring to attached drawing, feature, advantage of the invention and characteristic are able to more preferably by the description of following description
Understanding, in attached drawing:
Fig. 1: the measurement position of the electrode pair of an embodiment of the system for non-invasive measurement of blood flow mechanics parameter of the invention
Set schematic diagram；
Fig. 2: the thoracic impedance method and Swan- that the system for non-invasive measurement of blood flow mechanics parameter of the invention uses
The scatter plot of Ganz tremie method synchro measure stroke volume SV；
Fig. 3: the scientific literature research list of derivative of impedance cardiogram accuracy of the invention；
Fig. 4: the measurement of noninvasive hemodynamic conventional measurement technology and processing step schematic diagram；
Fig. 5: the present invention is using the measurement of WeChat ID amplification reduction method MIRDSAP technology and the schematic diagram of processing step；
Fig. 6: the haemodynamics that the system for non-invasive measurement of blood flow mechanics parameter of the invention is generated, shows, printed
The non-limiting example of report；
Fig. 7: the first embodiment schematic diagram of the system for non-invasive measurement of blood flow mechanics parameter of the invention；
Fig. 8: the second embodiment schematic diagram of the system for non-invasive measurement of blood flow mechanics parameter of the invention；
Fig. 9: the first embodiment schematic diagram of the data processing system of blood flow mechanics parameter of the invention；
Figure 10: the second embodiment schematic diagram of the data processing system of blood flow mechanics parameter of the invention；
Figure 11: the haemodynamics that the system for non-invasive measurement of blood flow mechanics parameter of the invention is generated, shows, printed
Another non-limiting example of report；
Figure 12: the signal of preferred two kinds of measurements position of the data processing system of blood flow mechanics parameter of the invention
Figure.
Same or similar element uses same numeral mark in the figure, and different elements uses different number marks
Note, in which: 1, first pair of electrode slice；2, second pair of electrode slice；3, third is to electrode slice；4, the 4th pair of electrode slice.
Specific embodiment
Hereinafter, in conjunction with attached drawing and specific embodiment, the present invention is described further.
Inventive concept
Testing principle: using cardiac function as circulatory function-haemodynamics of core be it is currently the only being capable of thoroughly evaluating
The technological means of entire circulatory function, single detection, can cover entire circulatory function, including heart, blood, blood
Pipe:
Cardiac Power, such as myocardial contractive power, detect contraction intensity and oxygen demand evaluates heart function；
Cardiac preload, such as blood volume, detection returned blood volume evaluate perfused tissue；
Cardiac afterload, such as vascular resistence, detection peripheral vascular resistance evaluate blood vessel elasticity.
Physiology chest Power Capacity impedance method --- ICG method
Physiological foundation is blood flow caused by aorta, heartbeat and volume variation, and working principle is Ohm's law.
Thoracic cavity is just like conductor, intraluminal tissue electric conductivity are different.Blood and body fluid impedance are minimum, and skeleton and alveolar impedance are most
Greatly.
Cardiac ejection, aortic volume expand, and blood volume increases, and blood flow velocity is fast, erythrocyte ordered arrangement, then impedance is dropped
It is low.
Follow Ohm's law: resistance=voltage/current.When electric current is constant, resistance is directly proportional with the variation of voltage.Such as Fig. 1
It is shown, at the top of the body surface of thoracic cavity at --- namely neck root and bottom --- namely flat xiphoid-process level of midaxillary line, apply constant
High-frequency current by a narrow margin, impedance variations caused by aorta, heartbeat restore as human body impedance, the output impedance differential heart
Cardon.
The accuracy of physiology chest Power Capacity impedance method
Detection electric current is 7 μ A, is suitble to long-term monitoring, and have strong anti-interference, and repeatability is high, and sensibility is strong；It is used safely in
It is mounted with pacemaker personage, is also suitable for the intensive environment of instrument, respectively ICU, operating room etc..
As shown in Figures 2 and 3, the clinical test more than 100 confirms that ICG method and Swan-Ganz tremie method related coefficient are situated between
In 0.73-0.91.
Digitize robust technique
Noninvasive hemodynamic detection system of the invention, the also referred to as system for non-invasive measurement of blood flow mechanics parameter, are adopted
With 32-bit number signal thoracic impedance signal analog-digital chip, WeChat ID amplification reduction method is used --- also referred to as Ma moral
Match, English abbreviation MIRDSAP can exclude electromagnetic interference, and can to high-frequency signal with digital carry out compression processing, and
Signal to be analyzed in data transmission, rejects clutter, recovering signal, wherein the high-frequency signal is, for example, 1600KHz,
1600000 times/second.Fig. 4 and Fig. 5 shows noninvasive hemodynamic conventional measurement technology and the measurement effect using MIRDSAP technology
Compare.
The hospital department that the system for non-invasive measurement of blood flow mechanics parameter of the invention adapts to: ICU, Cardiological, old age
Section, Nephrology dept., rehabilitation surgery, emergency department, department of anesthesia, gynemetrics, physical examination section.
Clinical application citing
Cardiological/Department of Aged: the Physiopathologic proceeding before objective evaluation treating cardiovascular disease and in treatment, to because controlling
It treats, adjusts therapeutic scheme in time.The various cardiovascular drugs of objective evaluation use opportunity, dosage, shutdown opportunity.Capacity management,
Objective evaluation is suitble to the amount of infusion of patient.Heart function recovery situation and surgical effect before and after comprehensive management heart interventional therapy are the heart
Rehabilitation provides objective basis.
ICU/ emergency department: monitoring is unsuitable for the haemodynamics of invasive human observer.Without calibration, highly sensitive Quantitative Monitoring is each
Kind curative effect of medication adapts to the state of an illness and quickly changes, the adjustment of real-time prompting therapeutic scheme.Hemodynamic school superintendent after invasive monitoring
It surveys.
Anesthesia/acceleration rehabilitation surgery: goal orientation liquid undergoing treatment is mesh with Hemodynamics index, such as stroke volume
Mark maintains average of operation periods stroke volume maximization scheme by liquid load.
Fig. 6 shows the hemodynamic that the system for non-invasive measurement of blood flow mechanics parameter of the invention is generated, shows, printed
Journal bulletin example.
The diagnostic rule of blood flow mechanics Parameters variation
In the diagnostic rule of blood flow mechanics Parameters variation below, two groups of data of two positions measurement are used,
Wherein, first position refers generally to: end sitting position or the position that lies low, and general characteristic is that human heart is equivalent to lower limb and is in high bit
It sets；(second position) refers generally to after increasing returned blood volume: compared to first position, general characteristic are that human heart is equivalent to
Lower limb are in lower position.Hereinafter, the simple subsequent digital representation of name of the English of blood flow mechanics parameter measures position sequence
Number, wherein 1 indicates the first position, and 2 indicate the second position, and the simple name of Chinese or English of blood flow mechanics parameter is not
Numeric suffix is marked, is defaulted as obtaining in the first position measurement.
The Chinese for the blood flow mechanics parameter that data processing system of the invention can be measured and is calculated and
English letter name control is as follows: cardiac output CO；Cardiac index CI；Stroke volume SV；Heartbeat index SI；The conduction of heart rate regimen chest fluid
Property TFC；Often win aberration rate SVV；Capacity of blood vessel；Often win peripheral resistance SSVR；Often win peripheral resistance index SSVRI；System resistance
SVR；Blood vessel elasticity；Left ventricle often wins work done LSW；Left ventricle often wins work index LSWI；Pre-ejection PEP；When left ventricular ejection
Between VET；Contraction time ratio STR；Penetrate blood shrinkage index EPCI；Inotropic state index ISI；It shrinks inotropic；Heart rate HR；Systolic pressure
SBP；Diastolic pressure DBP；Mean pressure MAP.
Basic condition analysis:
1, it is perfused:
It indicates that normal but relatively low (indicate if 50 > SV normal by the compensatory perfusion of fast heart rate is perfused if 3.0 > CI > 2.0；
60 > HR then indicates normal by the compensatory perfusion of SV)；
If 2.0 > CI, then it represents that Low perfusion；
If 4.5 > CI≤3.0, then it represents that perfusion is normal；
Indicate that perfusion is normal higher if 5.0≤CI≤4.5；
If CI > 5.0, then it represents that high perfusion.
2, blood pressure:
70 > mean pressure (MAP), then averagely force down；
MAP > 105, then mean pressure is high；
105≤MAP≤70, then mean pressure is normal.
Ya≤140 Shou Suo, then systolic pressure is high；
Ya≤90 140 > Shou Suo, then systolic pressure is normal；
90 > systolic pressure is then shunk and is forced down.
Ya≤90 Shu Zhang, then diastolic pressure is high；
Ya≤60 90 > Shu Zhang, then diastolic pressure is normal；
60 > diastolic pressure, then diastole is forced down.
3, heart rate (HR):
100≤HR≤60, then heart rate is normal；
60 > HR, then heart rate is partially slow；
Heart rate regimen > 50, HR > 100, then heart rate is fast, it is proposed that reduces heart rate；
50 > heart rate regimen > -50, HR > 100, then prompting heart rate fast is since low output is beneficial to compensatory, it is proposed that
Improve low output.
4, edema with the lung involved situation:
TFC > 0.045, then it represents that edema with the lung involved is excessive；
TFC≤0.035, -50% > capacity of blood vessel, blood pressure are normal, then it represents that edema with the lung involved is excessive.
Haemodynamics internal factor analysis:
1, preload:
If TFC2≤TFC1 and inotropic 1 > contraction of contraction inotropic 2, then it represents that preload supersaturation, it is proposed that negative before subtracting
Lotus；
If TFC1 > TFC2, then it represents that preload supersaturation, it is proposed that subtract preload；
If TFC2≤TFC1 and inotropic 2 > -50% > contraction of contraction inotropic 1, then it represents that preload is relatively low, it is proposed that suitable
Amount increases preload；
If TFC2≤TFC1 and inotropic 2 > contraction of contraction inotropic 1 > -50%, then it represents that preload is normal；
If TFC2≤TFC1 and 5% > (shrinking if inotropic 2- shrinks inotropic 1) indicates that preload tends to be saturated；
If TFC2≤TFC1, -50% > shrink inotropic 2 and (shrink if inotropic 2- shrinks inotropic 1)≤30%
Indicate that preload is relatively low, it is proposed that increase preload in right amount.
2, myocardial contractive power:
If shrinking inotropic 1 and person's contraction inotropic 2 > -50%, myocardial contractive power is normal；
If shrinking inotropic 1 > -50%, -50% > shrinking inotropic 2, or -50% > is shunk inotropic 1 and is shunk
Inotropic 2 > -50% indicates that myocardial contractive power has deposit；
If shrinking inotropic 1 > 50% or contraction inotropic 2 > 50%, then it represents that cardiac muscle is excited, it is proposed that reduce cardiac muscle
Convergent force；
If -50% > inotropic 1 and contraction inotropic 2 are shunk, but | shrink inotropic 1- and shrink inotropic 2 | > 30%,
Then indicate that myocardial contractive power has deposit；
> contraction inotropic 1 but SV1 > 50 or receipts -50% > contracting inotropic 2 but SV2 > 50, then it represents that cardiac muscle if -50%
It does work relatively low, cardiac muscle occurs reconstruct but also compensatory, it is proposed that improves myocardial remodelling phenomenon.
If -50% > shrink inotropic 1 and shrink inotropic 2 and 50 > SV1 and SV2, then it represents that myocardial contractive power is low, builds
View improves myocardial contractive power.
3, Diastolic function:
| shrink inotropic 1- and shrink inotropic 2 |-| (SV1-SV2) ÷ SV1 × 100% | > 10% prompts myocardial relaxation
Function reduction, it is proposed that improve Diastolic function；
If shrinking inotropic 1 > -50% but 50 > SV1 or shrinking inotropic 2 > -50% but 50 > SV2, and do not send out
The case where existing heart valve backflows is thought, Diastolic function is prompted to decline, it is proposed that improves diastolic function.
4, heart valve backflows:
It > shrinks inotropic 1 or SV2 > SV1 if SV1 > SV2 but contraction inotropic 2 but shrinks inotropic 1 > and shrink and become
Power 2 then prompts heart valve reflux events occur, checks incorporated by reference to cardiac ultrasonic；
If shrinking inotropic 1 > -50% but 50 > SV1 or shrinking inotropic 2 > -50% but 50 > SV2,10% > | it receives
The inotropic 1- that contracts shrinks inotropic 2 |-| (SV1-SV2) ÷ SV1 × 100% | then heart valve is prompted reflux events occur, please tie
Close cardiac ultrasonic investigation.
5, afterload:
If blood pressure is normal, afterload adjusts normal；
If high blood pressure, but afterload height is prompted if 2.0 > CI, it is proposed that subtract afterload；
If high blood pressure, but CI > 4.5,50% > blood vessel elasticity, 1500 > SVR, then prompt afterload normal, high blood pressure is
Due to perfusion is higher；
If high blood pressure, but CI > 4.5, blood vessel elasticity > 50%, SVR > 1500, then prompt afterload high, high blood pressure be by
In higher, afterload high the reason of causing jointly is perfused；
But 4.5 > CI > 2.0,50% > blood vessel elasticity, 1500 > SVR then prompt afterload normal but Imbalance, high blood pressure
It is due to afterload Imbalance, it is proposed that subtract afterload；
If blood pressure is low, CI > 2.0 then prompt afterload less than normal, it is proposed that improve afterload；
If blood pressure is low, 2.0 > CI, blood vessel elasticity > 50%, SVR > 1500 item prompt afterload normal, blood pressure is low be due to
The reason of Low perfusion；
If blood pressure is low, 2.0 > CI, 50% > blood vessel elasticity, 1500 > SVR, then prompting blood pressure low is Low perfusion and afterload
Two reasons of Imbalance cause jointly.
Conceived based on foregoing invention, referring to figs. 1 to 7, the non-invasive measurement system of blood flow mechanics parameter according to the present invention
One embodiment of system, the system for non-invasive measurement of the blood flow mechanics parameter include display device, printing equipment, human body electricity
Impedance detection device, eight core conducting wires and four pairs of electrode slices；
The human body resistance anti-detection devices is electrically connected by the eight cores conducting wire with four pairs of electrode slices；
The human body resistance anti-detection devices can apply constant high-frequency current by a narrow margin to four pairs of electrode slices ---
Electric current is referred to as detected, since aorta and heartbeat cause thoracic cavity blood flow generating period to change, causes thoracic cavity resistance
Anti- is in periodically-varied, thus, the human body resistance anti-detection devices can note down and output impedance differential cardiogram, and according to
The blood flow mechanics parameter is obtained by calculation in the differential cardiogram aroused in interest；
The display device and the printing equipment are connect with the human body resistance anti-detection devices data communication；
The display device includes display screen, for showing that measurement obtains in a manner of data form or data coordinates figure
Blood flow mechanics parameter；
The printing equipment can print the data form or data coordinates figure.
It is understood that referring to Fig.1, four pairs of electrode slices are distributed in the top and bottom in thoracic cavity, eight core is led
On line has 8 conductor wires, is separately connected an electrode slice, and two adjacent electrode slices of the same side constitute a pair of electrodes piece, altogether
Form four pairs of electrode slices: first pair of electrode slice, 1, second pair of electrode slice 2, third are to electrode slice 3, the 4th pair of electrode slice 4.Favorably
Ground, the electrode slice are the form of disk, and optionally, the electrode slice is the form of elliptical piece, square plate.The human body resistance
Anti-detection devices is, for example, the noninvasive hemodynamic detection system CSM3100 of thousand sail Medical Instruments Co., Ltd of Shenzhen production, can
Selection of land, the human body resistance anti-detection devices are the RM-6000 type polygraphs of Japanese photoelectricity production, are matched with the machine
PI-600G and EQ-600G impedance and differentiating amplifier plug-in unit.The display screen of the display device is, for example, touch liquid
Crystal display screen, the printing equipment are, for example, laser printer or ink-jet printer.
Preferably, the system for non-invasive measurement of blood flow mechanics parameter further includes message input device, such as keyboard, mouse
Or writing pencil, for entering information into the human body resistance anti-detection devices.
The system for non-invasive measurement measures the blood flow mechanics parameter in the following manner:
As shown in Figure 1, two pairs in four pairs of electrode slices to be pasted on to the chest of testee by mutually opposed mode
At neck root at the top of cavity table；
As shown in Figure 1, other two pairs in four pairs of electrode slices are pasted on described be tested by mutually opposed mode
At the flat xiphoid-process level of midaxillary line of the thoracic cavity body surface bottom of examination person；
The testee keeps body quiet by prostrate or half sleeping position；
The essential information of the testee is set, starts to detect；
The blood flow mechanics parameter that measurement obtains is shown on the display screen of the display device；
The printing equipment prints the data form or data coordinates figure of the blood flow mechanics parameter.
Preferably, the detection electric current is 5 μ A to 10 μ A, or is 7 μ A.
Preferably, the distance between two electrode slices of the same side of same position is 3 centimetres to 7 centimetres, or is 5
Centimetre.
Preferably, the human body resistance anti-detection devices includes 32-bit number signal thoracic impedance signal digital-to-analogue conversion core
Piece, wherein the 32-bit number signal thoracic impedance signal analog-digital chip can exclude electromagnetic interference, and can be to high frequency
Signal analyzes signal, rejects clutter, recovering signal with digital carry out compression processing in data transmission.
Preferably, the blood flow mechanics parameter includes heart stroke parameter, Cardiac Power parameter, cardiac preload ginseng
Number, cardiac afterload parameter, heart conventional parameter.
Preferably, the heart stroke parameter include cardiac output CO, cardiac index CI, stroke volume SV, heartbeat index SI and
Heart rate regimen；
The cardiac preload parameter includes chest fluid conductibility TFC, often fight aberration rate SVV and capacity of blood vessel；
The cardiac afterload parameter includes often fight peripheral resistance SSVR, peripheral resistance of often fighting index SSVRI, system resistance
SVR and blood vessel elasticity；
The Cardiac Power parameter includes that left ventricle is often fought work done LSW, left ventricular stroke work index LSWI, pre-ejection
PEP, left ventricular ejection time VET, contraction time ratio STR, blood shrinkage index EPCI, inotropic state index ISI is penetrated and shrinks variable force
Property；
The heart conventional parameter includes heart rate HR, systolic pressure SBP, diastolic pressure DBP and mean pressure MAP.
Another embodiment of the system for non-invasive measurement of blood flow mechanics parameter according to the present invention, it is described referring to Fig. 8
The system for non-invasive measurement of blood flow mechanics parameter includes that display device, printing equipment, human body resistance anti-detection devices, eight cores are led
On line, four pairs of electrode slices and mounting bracket, wherein the mounting bracket is for supporting or fixing the display device, described beat
Printing equipment is set and the human body resistance anti-detection devices.Each device effectively can be integrated into a job by such design
Reliable and stable measuring system.
Automatic processing is carried out to the physiological data that the measuring system is collected, is commented in order to which doctor carries out medicine to it
Valence, this is big data era R&D direction.For this purpose, inventor proposes the data processing system of blood flow mechanics parameter.
The first embodiment of the data processing system of blood flow mechanics parameter according to the present invention, it is described referring to Fig. 9
The data processing system of blood flow mechanics parameter is used to collect the data of blood flow mechanics parameter measuring apparatus measurement, goes forward side by side
The data processing of rower quasiconfiguaration forms the available data information format of medical worker.The number of the blood flow mechanics parameter
It include data collection conversion interface module, data normalization module and data mining module according to processing system.
The data collection conversion interface module can collect a variety of different blood flow mechanics parameter measurement dresses
The raw measurement data that measurement obtains is set, and is converted into the data mode that the data normalization module can identify --- it is known as
Standard measurement data；The raw measurement data is measured under two kinds of positions and is obtained: the first position: end sitting position or the position that lies low, always
Body characteristics are that human heart is equivalent to lower limb and is in the first high position；Second position: compared to the first position, general characteristic is people
Systemic heart is equivalent to lower limb and is in the second lower position.It is understood that the data collection conversion interface module can receive
The data file sent from USB flash disk, Email, the data collection conversion interface module also can receive various communication associations
The real-time measuring data that view such as serial communication protocol, HTTP protocol, WINSOCKET communications protocol are sent, and according to phase
The data conversion rule answered is converted into the standard measurement data form that the data normalization module can identify.Referring to Fig.1 2,
The raw measurement data is measured according to heart relative to two different locations of lower limb, in the first high position, human heart
It is higher than or is flush to lower limb on the direction perpendicular to the earth's core, in the second lower position, human heart is in the direction perpendicular to the earth's core
It is upper to be lower than lower limb.Standard measurement data refers to the data format of data processing system setting of the invention, for example, text data,
Microsoft Excel data, ACCESS tables of data format, SQL Server tables of data format.Shown in code one as follows, standard is surveyed
Amount data format is text-string s.
The data normalization module can convert the standard measurement data to by calculation processing the blood of medicine
Hydromechanics supplemental characteristic.It, can be by the electricity of measurement for using noninvasive hemodynamic detection system CSM3100 of the invention
Signal data is converted into
The data mining module can be regular according to data mining, be by the blood flow mechanics supplemental characteristic merger
Blood flow state level data.
These data can be the data from invasive or non-invasive measurement, be also possible to any to obtain these data
Measuring technique.
The blood flow mechanics parameter measuring apparatus for example can be the nothing of blood flow mechanics parameter described above
Measuring system is created, the noninvasive blood of CSM-3000 of thousand sail Medical Instruments Co., Ltd of PICCO monitor or Shenzhen is also possible to
Flow force detection system.
The data processing system of the blood flow mechanics parameter, which is realized, accordingly converts text information for digital information
Function, reached and medical staff freed from the mental labour for largely studying digital information carefully, improve work effect
Rate.
It is the form of text-string s shown in following code one as the standard measurement data specific example.
Code one: the standard measurement data s is converted into the blood flow mechanics supplemental characteristic of medicine by simple process,
This is because raw measurement data has been converted using the system for non-invasive measurement of blood flow mechanics parameter of the invention itself
For blood flow mechanics supplemental characteristic.
Preferably, the raw measurement data is the time diffusion of impedance value and impedance value.As Fig. 4, Fig. 5 show measurement
Signal becomes the data information that can be read and calculate through technical treatment.
Preferably, the standard measurement data is heart impedance blood flow chart data, wherein the heart impedance blood flow chart data packet
Include total impedance figure △ Z and cardiac impedance differential map；Technical detail about heart impedance blood flow chart can be found in the finger of scientific literature in Fig. 3
It introduces row to understand, patent document CN1221325A also provides more relevant technical details.
The cardiac impedance differential map includes:
A wave, also known as room contracting wave are located at after P wave of electrocardiogram, corresponding with fourth heart sound S4, generate and receive with atrium
It contracts related；
C wave, also known as room contracting wave are located at after ECG-QRS Wave, generate and penetrate blood with master, pulmonary artery when ventricular contraction
It is related；
O wave, also known as room Shu Bo are located at after ECG T wave, O point and caardiophonogram left atrioventricular valve Opening Snap OS with ACG
It is corresponding；
B point: being the starting point of C wave for ventricular ejection initial point, represents semilunar valve and opens, ventricle starts to penetrate blood；
X point: for ventricular ejection terminal, it is located at after C wave, is the highest point of the cardiac impedance differential map, with caardiophonogram
Aorta petal ingredient A2 is corresponding, and representing left ventricular ejection terminates；
Y point: closing point for pulmonary valve, be located at after X point, corresponding with pulmonary valve composition P2, represents right ventricle
Blood is penetrated to finish；
E point: for the full point of ventricle, being located at after O wave, corresponding with caardiophonogram S3, represents ventricle phase of rapid filling
Terminate the index point started with slow filling period.
More details about above-mentioned heart impedance blood flow chart content can be found in Baidupedia entry " heart impedance blood flow chart ", this
Text is no longer described in detail.
Preferably, the blood flow mechanics supplemental characteristic includes heart stroke supplemental characteristic, Cardiac Power supplemental characteristic, the heart
Dirty preload supplemental characteristic, cardiac afterload supplemental characteristic and heart conventional parameter data；
The heart stroke parameter includes that cardiac output CO, cardiac index CI, stroke volume SV, heartbeat index SI and heart rate become
Rule property；
The cardiac preload parameter includes chest fluid conductibility TFC, often fight aberration rate SVV and capacity of blood vessel；
The cardiac afterload parameter includes often fight peripheral resistance SSVR, peripheral resistance of often fighting index SSVRI, system resistance
SVR and blood vessel elasticity；
The Cardiac Power parameter includes that left ventricle is often fought work done LSW, left ventricular stroke work index LSWI, pre-ejection
PEP, left ventricular ejection time VET, contraction time ratio STR, blood shrinkage index EPCI, inotropic state index ISI is penetrated and shrinks variable force
Property；
The heart conventional parameter includes heart rate HR, systolic pressure SBP, diastolic pressure DBP and mean pressure MAP.
The calculation method and calculation formula of above-mentioned parameter can be found from textbook and in the prior art, for example, " clinical blood
Hydromechanics " Liu Dawei chief editor, People's Health Publisher, 2013, ISBN 978-7-117-17650-7；"SYSTEMIC
HEMODYNAMICS AND HEMODYNAMIC MANAGEMENT》,by B.Bo Sramek,Ph.D.,ISBN 1-59196-
046-0.I will not elaborate, specifically, the calculation formula of cardiac output CO referring to doctor Sramek the English works
Equation Eq.2.14；Cardiac index CI=CO/BAS, wherein BAS is body surface area；Stroke volume SV is referring to equation
Eq.2.20, heartbeat index SI=SV/BAS, heart rate regimen is referring to page 89 of the English works of doctor Sramek the
5.5.3.2 section；Chest fluid conductibility TFC=1/Z0, wherein Z0 is impedance；Often fight aberration rate SVV=(SVmax-SVmin)/
SVmin；The calculation formula of system resistance SVR referring to the English works of doctor Sramek equation Eq.4.2a；It shrinks
The 5.5.3.1 of the inotropic English works referring to doctor Sramek is saved；Capacity of blood vessel is referring to described in doctor Sramek
The 5.5.3.2 of page 89 of English works is saved；Blood vessel elasticity 5.5.3.3 section of page 90.
Parameter TFC combination PLR about " thorax impedance method noninvasive haemodynamics detection " test after in anterior right ventricular load
Application in judgement is introduced:
1, TFC is a parameter for reflecting the electric conductivity of pleural fluid, and the pleural fluid scale of construction is more, and the value of TFC is bigger, instead
It is then smaller.
2, PLR is tested: referring to Fig.1 2, passively lifting leg (PLR) experiment is in autonomous respiration, or even in the patient of arrhythmia cordis
It is reactive " goldstandard " to assess capacity, it is possible to reduce the application of liquid.But the benefit that PLR increases preload is of short duration, it is maximum
Hemodynamic effect occurs 1 minute after lifting leg, so to sensitivity requirement height (such as SV or myocardial contractive power of observation index
Parameter).And most of hemodynamic monitoring tool all only monitors the SV or myocardial contraction force parameter of left ventricle at present,
If working as right ventricle such as right heart failure when something goes wrong, becomes in fact for left ventricle in fact after PLR and subtract returned blood volume
(returning left ventricle) passes through PLR at this time and the SV of left ventricle or the parameter combination Frank-Starling of myocardial contractive power is used to determine again
Rule is to judge capacity reactivity with regard to improper.So first to judge the right side in clinical application PLR experimental judgment capacity reactivity
The capacity reactivity of ventricle.
Comprehensive 1 and 2, can play a vivid analogy in fact: thoracic cavity like a reservoir, water number can use
TFC is indicated；Right ventricle is water inlet valve, and left ventricle is outlet valve, and only the two valves will abide by
Frank-Starling law.
For the ease of difference: the TFC that we measure position before PLR indicates that the TFC measured after PLR is used with " TFC1 "
" TFC2 " is indicated.1, as TFC1 > TFC2, the amount of liquid in entire thoracic cavity is reduced instead after expression increase right ventricle returned blood volume
, may determine that the capacity reactivity of right ventricle is negative according to law of heart, that is, right ventricular volume is more than myocardium inflection point.
2, when TFC1 < TFC2, the amount of liquid for indicating to increase entire thoracic cavity after right ventricle returned blood volume is increased, can be with according to law of heart
Judge that the capacity reactivity of right ventricle is positive, that is, right ventricular volume is less than myocardium inflection point.
It is understood that the calculation formula and calculation method of above-mentioned parameter are only preferred embodiments, other classes
As the supplemental characteristic that obtains of calculation method be also the manageable data of the present invention.
The major technique of the application, which is contributed, to be to carry out these blood flow mechanics supplemental characteristics into classification processing, and according to
Relevant medical and physiological knowledge combine interpretation to the blood flow mechanics supplemental characteristic, are analyzed with computer data and replace doctor
It is raw to carry out basic data interpretation, doctor's clinical a large amount of data interpretation time is saved, the working efficiency of doctor is improved.
Preferably, the blood flow state level data includes haemodynamics basic status level data and haemodynamics
Internal cause state grade data；
The haemodynamics basic status level data includes perfusion level data, blood pressure level data, heart rate grade
Data and edema with the lung involved level data；
The haemodynamics internal cause state grade data include preload level data, myocardial contraction level data, the heart
Flesh diastole level data, heart valve backflow level data and afterload level data.
Preferably, the perfusion level data includes that perfusion is low, perfusion is relatively low, perfusion is normal, perfusion is higher, it is high to be perfused；
The blood pressure level data include that mean blood pressure is high, mean blood pressure is normal, mean blood pressure is low；Systolic pressure is high, shrinks
Positive pressure is normal, shrinks and forces down；Diastolic pressure is high, diastolic pressure is normal, diastole is forced down；
The heart rate level data includes that heart rate is slow, heart rate is partially slow, heart rate is normal, heart rate is fast, heart rate is fast；
The edema with the lung involved level data includes that edema with the lung involved is excessive, edema with the lung involved is normal.
Preferably, the preload level data include preload supersaturation, preload tend to saturation, load it is normal, preceding
Load is relatively low；
The afterload level data includes that afterload is normal, afterload is high, afterload is less than normal；Afterload adjust it is normal,
Afterload Imbalance；
The myocardial contraction level data includes that myocardial contractive power is normal, myocardial contractive power has deposit, cardiac muscle excited, myocardium
Doing work, relatively low, myocardial contractive power is low；
The myocardial relaxation level data includes that Diastolic function declines, Diastolic function is normal, myocardial relaxation function
It can rise；
The heart valve backflow level data include heart valve occur backflowing, heart valve it is normal.
As described above, a large amount of numerical data is divided into several grades with textual representation, readability enhancing, doctor is not
It needs to obtain literal meaning again according to digital information, but directly infers physiologic information from text information, to save
Doctor largely studies the time of measurement data carefully.
Preferably, the data mining module includes perfusion classification submodule, mean blood pressure classification submodule, systolic pressure point
Grade submodule, diastolic pressure classification submodule, heart rate classification submodule, edema with the lung involved is classified submodule, preload is classified submodule, rear negative
Lotus classification submodule, myocardial contraction classification submodule, myocardial relaxation classification submodule, heart valve backflow and are classified submodule.It can
With understanding, no matter the blood flow mechanics supplemental characteristic is stored in text file or in database, by above-mentioned
Program module carries out classification processing to data.
It is preferably based on the blood flow mechanics supplemental characteristic, the perfusion classification submodule presses following hierarchical approaches
The perfusion level data is classified:
It is perfused low: 2.0 > cardiac index CI
It is perfused relatively low: 3.0 > cardiac index CI > 2.0
Perfusion is normal: 4.5 > cardiac index CI≤3.0
It is perfused higher: 5.0≤cardiac index CI≤4.5
Perfusion is high: cardiac index CI > 5.0.
The perfusion classification submodule can for example be realized by following C# source codes and computing device such as computer.
Code two: the example source code of the perfusion classification submodule.
It is preferably based on the blood flow mechanics supplemental characteristic, the mean blood pressure classification submodule presses following classification
Mode is classified the blood pressure level data:
Mean blood pressure is high: mean pressure MAP > 105；
Mean blood pressure is normal: 105≤mean pressure MAP≤70；
Mean blood pressure is low: 70 > mean pressure MAP.
The mean blood pressure classification submodule for example can be by following C# source codes and computing device such as computer come real
It is existing.
Code three: the example source code of the mean blood pressure classification submodule.
It is preferably based on the blood flow mechanics supplemental characteristic, the systolic pressure classification submodule presses following classification side
Formula is classified the blood pressure level data:
Systolic pressure is high: Ya≤140 Shou Suo；
Systolic pressure is normal: Ya≤90 140 > Shou Suo；
Contraction is forced down: 90 > systolic pressure.
The systolic pressure classification submodule can for example be realized by following C# source codes and computing device such as computer.
Code four: the example source code of the systolic pressure classification submodule.
It is preferably based on the blood flow mechanics supplemental characteristic, the diastolic pressure classification submodule presses following classification side
Formula is classified the blood pressure level data:
Diastolic pressure is high: Ya≤90 Shu Zhang；
Diastolic pressure is normal: Ya≤60 90 > Shu Zhang；
Diastole is forced down: 60 > diastolic pressure.
The diastolic pressure classification submodule can for example be realized by following C# source codes and computing device such as computer.
Code five: the example source code of the diastolic pressure classification submodule.
It is preferably based on the blood flow mechanics supplemental characteristic, the heart rate classification submodule presses following hierarchical approaches
The heart rate level data is classified:
Heart rate is partially slow: 60 > heart rate HR；
Heart rate is normal: 100≤heart rate HR≤60；
Heart rate is fast: 50 > heart rate regimen > -50, heart rate HR > 100；
Heart rate is fast: heart rate regimen > 50, heart rate HR > 100.
The heart rate classification submodule can for example be realized by following C# source codes and computing device such as computer.
Code six: the example source code of the heart rate classification submodule.
It is preferably based on the blood flow mechanics supplemental characteristic, the edema with the lung involved classification submodule presses following hierarchical approaches
The edema with the lung involved level data is classified:
Edema with the lung involved is excessive: chest fluid conductibility TFC > 0.045 or chest fluid conductibility TFC≤0.035 and -50% > blood vessel appearance
Product.
The edema with the lung involved classification submodule can for example be realized by following C# source codes and computing device such as computer.
Code seven: the example source code of the edema with the lung involved classification submodule.
It is preferably based on the blood flow mechanics supplemental characteristic, the preload classification submodule presses following classification side
Formula is classified the preload level data:
Preload supersaturation: chest fluid conductibility TFC2≤chest fluid conductibility TFC1, and it is inotropic to shrink inotropic 1 > contraction
2；Alternatively, chest fluid conductibility TFC1 > chest fluid conductibility TFC2；
Preload tends to be saturated: chest fluid conductibility TFC2≤chest fluid conductibility TFC1 and 5% > (shrink inotropic 2- to shrink
It is inotropic 1)；
Load is normal: chest fluid conductibility TFC2≤chest fluid conductibility TFC1 and shrink it is inotropic 2 > shrink inotropic 1 >-
50%；
Preload is relatively low: chest fluid conductibility TFC2≤chest fluid conductibility TFC1 and contraction inotropic 2 > -50% > contraction change
Power 1；Alternatively, chest fluid conductibility TFC2≤chest fluid conductibility TFC1, -50% > shrink and inotropic 2 and (shrink inotropic 2-
Shrink it is inotropic 1)≤30%；
Wherein, chest fluid conductibility TFC1, contraction inotropic 1 are measured and are calculated by first position, chest fluid conduction
Property TFC2, shrink inotropic 2 by second position measure and be calculated.
The preload classification submodule can for example be realized by following C# source codes and computing device such as computer.
Code eight: the example source code of the preload classification submodule.
It is preferably based on the blood flow mechanics supplemental characteristic, the afterload classification submodule presses following classification side
Formula is classified the afterload level data:
Afterload is normal: mean pressure MAP high, but cardiac index CI > 4.5,50% > blood vessel elasticity, 1500 > system resistance
SVR；Alternatively, 4.5 > cardiac index CI > 2.0,50% > blood vessel elasticity, 1500 > system resistance SVR；Alternatively, mean pressure MAP is low,
2.0 > cardiac index CI, blood vessel elasticity > 50%, system resistance SVR > 1500；
Afterload is high: mean pressure MAP high, but 2.0 > cardiac index CI；Alternatively, mean pressure MAP high, but cardiac index CI >
4.5, blood vessel elasticity > 50%, system resistance SVR > 1500；
Afterload is less than normal: mean pressure MAP is low, cardiac index CI > 2.0；
Afterload adjusts normal: mean pressure MAP is normal；
Afterload Imbalance: 4.5 > cardiac index CI > 2.0,50% > blood vessel elasticity, 1500 > system resistance SVR；Or
Person, blood pressure is low, 2.0 > cardiac index CI, 50% > blood vessel elasticity, 1500 > system resistance SVR.
The afterload classification submodule can for example be realized by following C# source codes and computing device such as computer.
Code nine: the example source code of the afterload classification submodule.
It is preferably based on the blood flow mechanics supplemental characteristic, the myocardial contraction classification submodule presses following classification
Mode is classified the myocardial contraction level data:
Myocardial contractive power is normal: (shrinking inotropic 1+ and shrinks inotropic 2) > -50%；
Myocardial contractive power has deposit: contraction inotropic 1 > -50%, and -50% > shrink inotropic 2；Alternatively, -50% > receive
It contracts inotropic 1, and shrinks inotropic 2 > -50%；Alternatively, -50% > (it shrinks inotropic 1+ and shrinks inotropic 2), but | it shrinks and becomes
Power 1- shrinks inotropic 2 | and > 30%；
Cardiac muscle is excited: shrinking inotropic 1 > 50%, or shrinks inotropic 2 > 50%
Cardiac muscle acting is relatively low: -50% > shrink inotropic 1, but SV1 > 50；Or -50% > shrink inotropic 2, but heartbeat
Measure SV2 > 50；
Myocardial contractive power is low: -50% > (it shrinks inotropic 1+ and shrinks inotropic 2), and 50 > (stroke volume SV1 and stroke volume
SV2)；
Wherein, stroke volume SV1, contraction inotropic 1 are measured and are calculated, stroke volume SV2, heartbeat by first position
Amount SV shrinks inotropic 2 and is measured and be calculated by second position.
The myocardial contraction classification submodule for example can be by following C# source codes and computing device such as computer come real
It is existing.
Code ten: the example source code of the myocardial contraction classification submodule.
It is preferably based on the blood flow mechanics supplemental characteristic, the myocardial relaxation classification submodule presses following classification
Mode is classified the myocardial relaxation level data:
Diastolic function decline: | shrink inotropic 1- and shrink inotropic 2 |-| (stroke volume SV1- stroke volume SV2) ÷
Stroke volume SV1 × 100% | > 10%；Alternatively, shrinking inotropic 1 > -50%, but 50 > stroke volume SV1；Alternatively, shrinking inotropic 2
> -50%, but 50 > stroke volume SV2, and backflow without discovery heart valve；
Wherein, stroke volume SV1, contraction inotropic 1 are measured and are calculated by first position, stroke volume SV2, are shunk
Inotropic 2 are measured and are calculated by second position.
The myocardial relaxation classification submodule for example can be by following C# source codes and computing device such as computer come real
It is existing.
Code 11: the example source code of the myocardial relaxation classification submodule.
It is preferably based on the blood flow mechanics supplemental characteristic, the heart valve, which backflows, is classified submodule by following
Hierarchical approaches are classified heart valve level data of backflowing:
Heart valve backflows: stroke volume SV1 > stroke volume SV2, but shrinks inotropic 2 > contraction inotropic 1；Alternatively,
Stroke volume SV2 > stroke volume SV1, but shrink inotropic 1 > contraction inotropic 2；Alternatively, contraction inotropic 1 > -50%, but 50 >
SV1；Alternatively, inotropic 2 > -50% is shunk, but 50 > stroke volume SV2,10% > | shrink inotropic 1- and shrink inotropic 2 |-|
(stroke volume SV1- stroke volume SV2) ÷ stroke volume SV1 × 100% |；
Wherein, stroke volume SV1, contraction inotropic 1 are measured and are calculated by first position, stroke volume SV2, are shunk
Inotropic 2 are measured and are calculated by second position.
The heart valve backflow be classified submodule for example can be by following C# source codes and computing device such as computer
To realize.
Code 12: the heart valve, which backflows, is classified the example source code of submodule.
Preferably, the data processing system of the blood flow mechanics parameter includes analysis and suggestion module, wherein described point
It analyses suggestion module and medical advice information is provided according to medical pathologies principle according to the blood flow state level data.It is understood that
, referring to Fig. 6, a large amount of digital informations of the blood flow mechanics supplemental characteristic, by the blood flow of the application
After the calculation processing of the data processing system of mechanics parameter, become text information, for example, 1. lie low be perfused still.2. myocardium power
There is deposit.3. preload is higher.4. afterload is normal, blood pressure is normal.And by means of medicine and physiological principle, the analysis is built
View module can provide measurement analysis and suggestion for example are as follows: measurement report shows left and right Cardiac volume excess load, incorporated by reference to doctor's clinic
Medicining condition.
Preferably, as shown in Figure 10, the data processing system of the blood flow mechanics parameter further includes haemodynamics
Report generation module, wherein haemodynamics report generation module is according to the blood flow mechanics supplemental characteristic, the blood flow
State grade data and the medical advice information, generating includes haemodynamics data reporting information table.It is understood that
It is that as shown in Fig. 6, Figure 11, the haemodynamics report generation module be can be generated including numerical data list, datagram
The report of the haemodynamics of table and character analysis result.
Preferably, the original measurement number is obtained by the system for non-invasive measurement of blood flow mechanics parameter described above
According to, the standard measurement data and the blood flow mechanics supplemental characteristic.It is understood that the skill of system for non-invasive measurement
Art advantage causes this system to be necessarily widely used in medical care technical field, measurement capabilities, data-handling capacity all with
The update of device systems and constantly enhance.Also, the data processing system of blood flow mechanics parameter of the invention can also
To be integrated with system for non-invasive measurement, improves the utilization rate of equipment and save cost.
Largely abstract digital information is converted text by the data processing system of blood flow mechanics parameter of the invention
Word information has reached the data interpretation time for saving medical staff, has improved work efficiency.
The preferred or specific embodiment of the invention is described in detail above.It should be appreciated that the technology of this field
Personnel make many modifications and variations without the design concept that creative work can be created according to the present invention.Therefore, all
In technical field technical staff according to the design concept of the invention pass through on the basis of existing technology logic analysis, reasoning or
The limited available technical solution of experiment of person, all should be within the scope of the invention and/or by claims institute
In determining protection scope.
Claims (22)
1. the data processing system of blood flow mechanics parameter is used to collect the measurement of blood flow mechanics parameter measuring apparatus
Data, the data processing for rower quasiconfiguaration of going forward side by side form the available data information format of medical worker, it is characterised in that: described
The data processing system of blood flow mechanics parameter includes data collection conversion interface module, data normalization module and data
Refine module；
The data collection conversion interface module can collect a variety of different blood flow mechanics parameter measuring apparatus and survey
The raw measurement data measured, and it is converted into the data mode that the data normalization module can identify --- it is known as standard
Measurement data；The raw measurement data is measured under two kinds of positions and is obtained: the first position: end sitting position or the position that lies low, overall special
Sign is that human heart is equivalent to lower limb and is in the first high position；Second position: compared to the first position, general characteristic is the human body heart
The dirty lower limb that are equivalent to are in the second lower position；
The data normalization module can convert the standard measurement data to by calculation processing the blood flow of medicine
Mechanics parameter data；
The blood flow mechanics supplemental characteristic merger can be blood flow according to data mining rule by the data mining module
State grade data.
2. the data processing system of blood flow mechanics parameter according to claim 1, it is characterised in that: the original survey
Amount data are the time diffusions of impedance value and impedance value.
3. the data processing system of blood flow mechanics parameter according to claim 1, it is characterised in that: the blood stream
Kinetic parameter includes heart stroke parameter, Cardiac Power parameter, cardiac preload parameter, cardiac afterload parameter, heart routine
Parameter.
4. the data processing system of blood flow mechanics parameter according to claim 3, it is characterised in that:
The heart stroke parameter includes cardiac output CO, cardiac index CI, stroke volume SV, heartbeat index SI and heart rate regimen；
The cardiac preload parameter includes chest fluid conductibility TFC, often fight aberration rate SVV and capacity of blood vessel；
The cardiac afterload parameter include often fight peripheral resistance SSVR, peripheral resistance of often fighting index SSVRI, system resistance SVR,
And blood vessel elasticity；
The Cardiac Power parameter include left ventricle often fight work done LSW, left ventricular stroke work index LSWI, pre-ejection PEP,
Left ventricular ejection time VET, contraction time ratio STR, blood shrinkage index EPCI, inotropic state index ISI are penetrated and is shunk inotropic；
The heart conventional parameter includes heart rate HR, systolic pressure SBP, diastolic pressure DBP and mean pressure MAP.
The heart stroke parameter includes cardiac output CO, cardiac index CI, stroke volume SV, heartbeat index SI and heart rate regimen；
The cardiac preload parameter includes chest fluid conductibility TFC, often fight aberration rate SVV and capacity of blood vessel；
The cardiac afterload parameter include often fight peripheral resistance SSVR, peripheral resistance of often fighting index SSVRI, system resistance SVR,
And blood vessel elasticity；
The Cardiac Power parameter include left ventricle often fight work done LSW, left ventricular stroke work index LSWI, pre-ejection PEP,
Left ventricular ejection time VET, contraction time ratio STR, blood shrinkage index EPCI, inotropic state index ISI are penetrated and is shunk inotropic；
The heart conventional parameter includes heart rate HR, systolic pressure SBP, diastolic pressure DBP and mean pressure MAP.
5. the data processing system of blood flow mechanics parameter according to claim 1, it is characterised in that: the blood flow shape
State level data includes haemodynamics basic status level data and haemodynamics internal cause state grade data；
The haemodynamics basic status level data includes perfusion level data, blood pressure level data, heart rate level data
With edema with the lung involved level data；
The haemodynamics internal cause state grade data include preload level data, myocardial contraction level data, cardiac muscle relax
Level data, heart valve backflow level data and afterload level data.
6. the data processing system of blood flow mechanics parameter according to claim 5, it is characterised in that: described perfusion etc.
Grade data include that perfusion is low, perfusion is relatively low, perfusion is normal, perfusion is higher, it is high to be perfused；
The blood pressure level data include that mean blood pressure is high, mean blood pressure is normal, mean blood pressure is low；Systolic pressure is high, shrinks positive pressure
Often, it shrinks and forces down；Diastolic pressure is high, diastolic pressure is normal, diastole is forced down；
The heart rate level data includes that heart rate is slow, heart rate is partially slow, heart rate is normal, heart rate is fast, heart rate is fast；
The edema with the lung involved level data includes that edema with the lung involved is excessive, edema with the lung involved is normal.
7. the data processing system of blood flow mechanics parameter according to claim 6, it is characterised in that: the preload
Level data include preload supersaturation, preload tend to saturation, load is normal, preload is relatively low；
The afterload level data includes that afterload is normal, afterload is high, afterload is less than normal；Afterload adjusts normal, rear negative
Lotus Imbalance；
The myocardial contraction level data includes that myocardial contractive power is normal, myocardial contractive power has deposit, excited, the myocardium acting of cardiac muscle
It is relatively low, myocardial contractive power is low；
The myocardial relaxation level data includes that Diastolic function declines, Diastolic function is normal, on Diastolic function
It rises；
The heart valve backflow level data include heart valve occur backflowing, heart valve it is normal.
8. the data processing system of blood flow mechanics parameter according to claim 7, it is characterised in that: the data mention
Refining module includes that perfusion is classified submodule, mean blood pressure is classified submodule, systolic pressure classification submodule, diastolic pressure are classified submodule
Block, heart rate classification submodule, edema with the lung involved classification submodule, preload classification submodule, afterload classification submodule, myocardial contraction point
Grade submodule, myocardial relaxation classification submodule, heart valve backflow and are classified submodule.
9. the data processing system of blood flow mechanics parameter according to claim 8, it is characterised in that:
Based on the blood flow mechanics supplemental characteristic, the perfusion classification submodule is by following hierarchical approaches to described perfusion etc.
Grade data are classified:
It is perfused low: 2.0 > cardiac index CI
It is perfused relatively low: 3.0 > cardiac index CI > 2.0
Perfusion is normal: 4.5 > cardiac index CI≤3.0
It is perfused higher: 5.0≤cardiac index CI≤4.5
Perfusion is high: cardiac index CI > 5.0.
10. the data processing system of blood flow mechanics parameter according to claim 8, it is characterised in that:
Based on the blood flow mechanics supplemental characteristic, the mean blood pressure classification submodule is by following hierarchical approaches to the blood
Pressure level data is classified:
Mean blood pressure is high: mean pressure MAP > 105；
Mean blood pressure is normal: 105≤mean pressure MAP≤70；
Mean blood pressure is low: 70 > mean pressure MAP.
11. the data processing system of blood flow mechanics parameter according to claim 8, it is characterised in that:
Based on the blood flow mechanics supplemental characteristic, the systolic pressure classification submodule is by following hierarchical approaches to the blood pressure
Level data is classified:
Systolic pressure is high: Ya≤140 Shou Suo；
Systolic pressure is normal: Ya≤90 140 > Shou Suo；
Contraction is forced down: 90 > systolic pressure.
12. the data processing system of blood flow mechanics parameter according to claim 8, it is characterised in that:
Based on the blood flow mechanics supplemental characteristic, the diastolic pressure classification submodule is by following hierarchical approaches to the blood pressure
Level data is classified:
Diastolic pressure is high: Ya≤90 Shu Zhang；
Diastolic pressure is normal: Ya≤60 90 > Shu Zhang；
Diastole is forced down: 60 > diastolic pressure.
13. the data processing system of blood flow mechanics parameter according to claim 8, it is characterised in that:
Based on the blood flow mechanics supplemental characteristic, the heart rate classification submodule is by following hierarchical approaches to described heart rate etc.
Grade data are classified:
Heart rate is partially slow: 60 > heart rate HR；
Heart rate is normal: 100≤heart rate HR≤60；
Heart rate is fast: 50 > heart rate regimen > -50, heart rate HR > 100；
Heart rate is fast: heart rate regimen > 50, heart rate HR > 100.
14. the data processing system of blood flow mechanics parameter according to claim 8, it is characterised in that:
Based on the blood flow mechanics supplemental characteristic, the edema with the lung involved classification submodule is by following hierarchical approaches to described edema with the lung involved etc.
Grade data are classified:
Edema with the lung involved is excessive: chest fluid conductibility TFC > 0.045 or chest fluid conductibility TFC≤0.035 and -50% > capacity of blood vessel.
15. the data processing system of blood flow mechanics parameter according to claim 8, it is characterised in that:
Based on the blood flow mechanics supplemental characteristic, the preload classification submodule is by following hierarchical approaches to described preceding negative
Lotus level data is classified:
Preload supersaturation: chest fluid conductibility TFC2≤chest fluid conductibility TFC1, and shrink inotropic 1 > contraction inotropic 2；Or
Person, chest fluid conductibility TFC1 > chest fluid conductibility TFC2；
Preload tends to be saturated: chest fluid conductibility TFC2≤chest fluid conductibility TFC1 and 5% > (shrink inotropic 2- and shrink variable force
Property 1)；
Load is normal: chest fluid conductibility TFC2≤chest fluid conductibility TFC1 and inotropic 2 > contraction of contraction inotropic 1 > -50%；
Preload is relatively low: chest fluid conductibility TFC2≤chest fluid conductibility TFC1 and inotropic 2 > -50% > contraction of contraction inotropic 1；
Alternatively, chest fluid conductibility TFC2≤chest fluid conductibility TFC1, -50% > shrink inotropic 2 and (shrink inotropic 2- and shrink variable force
1)≤30% of property；
Wherein, chest fluid conductibility TFC1, contraction inotropic 1 are measured and are calculated, chest fluid conductibility by first position
TFC2, inotropic 2 are shunk by second position measurement and is calculated.
16. the data processing system of blood flow mechanics parameter according to claim 8, it is characterised in that:
Based on the blood flow mechanics supplemental characteristic, the afterload classification submodule is by following hierarchical approaches to described rear negative
Lotus level data is classified:
Afterload is normal: mean pressure MAP high, but cardiac index CI > 4.5,50% > blood vessel elasticity, 1500 > system resistance SVR；Or
Person, 4.5 > cardiac index CI > 2.0,50% > blood vessel elasticity, 1500 > system resistance SVR；Alternatively, mean pressure MAP is low, 2.0 > heart
Dirty index CI, blood vessel elasticity > 50%, system resistance SVR > 1500；
Afterload is high: mean pressure MAP high, but 2.0 > cardiac index CI；Alternatively, mean pressure MAP high, but cardiac index CI > 4.5,
Blood vessel elasticity > 50%, system resistance SVR > 1500；
Afterload is less than normal: mean pressure MAP is low, cardiac index CI > 2.0；
Afterload adjusts normal: mean pressure MAP is normal；
Afterload Imbalance: 4.5 > cardiac index CI > 2.0,50% > blood vessel elasticity, 1500 > system resistance SVR；Alternatively, blood
It forces down, 2.0 > cardiac index CI, 50% > blood vessel elasticity, 1500 > system resistance SVR.
17. the data processing system of blood flow mechanics parameter according to claim 8, it is characterised in that:
Based on the blood flow mechanics supplemental characteristic, the myocardial contraction classification submodule is by following hierarchical approaches to the heart
Flesh shrinks level data and is classified:
Myocardial contractive power is normal: (shrinking inotropic 1+ and shrinks inotropic 2) > -50%；
Myocardial contractive power has deposit: contraction inotropic 1 > -50%, and -50% > shrink inotropic 2；Alternatively, -50% > shrink change
Power 1, and shrink inotropic 2 > -50%；Alternatively, -50% > (it shrinks inotropic 1+ and shrinks inotropic 2), but | it shrinks inotropic
1- shrinks inotropic 2 | and > 30%；
Cardiac muscle is excited: shrinking inotropic 1 > 50%, or shrinks inotropic 2 > 50%
Cardiac muscle acting is relatively low: -50% > shrink inotropic 1, but SV1 > 50；Or -50% > shrink inotropic 2, but stroke volume SV2
>50；
Myocardial contractive power is low: -50% > (shrink inotropic 1+ and shrink inotropic 2), and 50 > (stroke volume SV1 and stroke volume SV2)；
Wherein, stroke volume SV1, contraction inotropic 1 are measured and are calculated, stroke volume SV2, stroke volume SV by first position
Inotropic 2 are shunk to be measured and be calculated by second position.
18. the data processing system of blood flow mechanics parameter according to claim 8, it is characterised in that:
Based on the blood flow mechanics supplemental characteristic, the myocardial relaxation classification submodule is by following hierarchical approaches to the heart
Flesh diastole level data is classified:
Diastolic function decline: | shrink inotropic 1- and shrink inotropic 2 |-| (stroke volume SV1- stroke volume SV2) ÷ stroke volume
SV1 × 100% | > 10%；Alternatively, shrinking inotropic 1 > -50%, but 50 > stroke volume SV1；Alternatively, contraction inotropic 2 >-
50%, but 50 > stroke volume SV2, and backflow without discovery heart valve；
Wherein, stroke volume SV1, contraction inotropic 1 are measured and are calculated by first position, stroke volume SV2, shrink variable force
Property 2 by second position measure and be calculated.
19. the data processing system of blood flow mechanics parameter according to claim 8, it is characterised in that:
Based on the blood flow mechanics supplemental characteristic, the heart valve, which backflows, is classified submodule by following hierarchical approaches to institute
Heart valve level data of backflowing is stated to be classified:
Heart valve backflows: stroke volume SV1 > stroke volume SV2, but shrinks inotropic 2 > contraction inotropic 1；Alternatively, heartbeat
SV2 > stroke volume SV1 is measured, but shrinks inotropic 1 > contraction inotropic 2；Alternatively, shrinking inotropic 1 > -50%, but 50 > SV1；Or
Person, shrinks inotropic 2 > -50%, but 50 > stroke volume SV2,10% > | shrink inotropic 1- and shrink inotropic 2 |-| (stroke volume
SV1- stroke volume SV2) ÷ stroke volume SV1 × 100% |；
Wherein, stroke volume SV1, contraction inotropic 1 are measured and are calculated by first position, stroke volume SV2, shrink variable force
Property 2 by second position measure and be calculated.
20. the data processing system of blood flow mechanics parameter according to claim 1, it is characterised in that: the blood
The data processing system of hydromechanics parameter further includes analysis and suggestion module, wherein the analysis and suggestion module is according to the blood
Stream mode level data provides medical advice information according to medical pathologies principle.
21. the data processing system of blood flow mechanics parameter according to claim 20, it is characterised in that: the blood
The data processing system of hydromechanics parameter further includes haemodynamics report generation module, wherein haemodynamics report life
It is raw at module according to the blood flow mechanics supplemental characteristic, the blood flow state level data and the medical advice information
At including haemodynamics data reporting information table.
22. the data processing system of blood flow mechanics parameter according to claim 1, it is characterised in that: pass through blood
The system for non-invasive measurement of hydromechanics parameter obtains the raw measurement data, the standard measurement data and the blood stream
Kinetic parameter data.
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