CN103366072A - Digital simulation method for blood backflow caused by mitral valve insufficiency - Google Patents

Abstract

The invention relates to cardiovascular systems, in particular to a digital simulation method for blood backflow caused by mitral valve insufficiency. A, a four-cavity lumped parameter angiocarpy dynamic circuit model equivalent to lesser circulation system, a systemic circulation system, a left heart circulation system and a right heart circulation system is established according to the equivalent relation of hemodynamics parameters and circuit parameters; B, according to the circuit model established in the step A, an established dynamic circuit is analyzed through a state variable analysis method, and corresponding state equations are established for related nodes in the circuit; C, according to simulation needs, the corresponding parameters in the step A and the step B are set, the state equations are solved according to the circuit model arranged in the step A and the state equations arranged in the step B, and the time curve graphs of the nodes in the circuit are obtained; D, QM obtained in the step C is calculated, and the blood backflow amount VRM, the mitral valve forward output amount VFM and the mitral valve volume VM under the condition that the mitral valve insufficiency occurs are obtained.

Description

A kind of digital simulation method of mitral valve insufficiency blood reflux

Technical field

The present invention relates to cardiovascular system, especially relate to a kind of digital simulation method of mitral valve insufficiency blood reflux.

Background technology

Mitral valve insufficiency is one of pathological phenomenon common in the angiocardiopathy, and its origin cause of formation is that bicuspid valve can not normally be closed at paradoxical expansion, and blood flows to the aortal while from left ventricle, and some flows back into the atrium sinistrum from left ventricle.Mitral valve insufficiency can produce blood reflux, thereby causes left ventricle dilatation and left ventricular dysfunction, when serious even can cause in heart failure so that dead.Blood reflux situation during the research mitral valve insufficiency, incompetence especially in various degree has important directive significance on the impact of blood reflux for bicuspid valve clinical repair and valve replacement surgery.

Mostly be to utilize using color Doppler echocardiography to assess the degree of mitral valve insufficiency to the analysis of human body mitral reflux situation at present, this method depends on doctor and operator's experience too much, has certain subjectivity (Qiu Junwei, Sun Kun. mitral regurgitation degree imaging evaluation Advances in Methods [J]. Chinese interventional imaging and acology, 2010,7 (2): 203-206), and the method only can be measured certain individual actual conditions, because the constraint of ethics, a lot of experiments can not directly be carried out at human body with it, pathology situation in various degree can't be realized, therefore its inherent law can't be further studied.Also there is the animal experiment method of employing to study, but because the animal and human there are differences, the animal model experiment method can not reflect the feature (Sun Jing of human body fully, mitral regurgitation continuous-wave doppler frequency spectrum is assessed the animal experiment study [D] of left chamber Relaxation time constant. Military Surgeon Further Education College, PLA, master thesis, 2012).The scholar is also arranged by the method for physical simulation, adopt mechanical hook-up, sensor to set up physics mock-up simulation human heart active state (Yan Xuan space, the research of heart dynamic modeling imitaion and simulation device, Shanghai Communications University, master thesis, 2011), this mock-up is time-consuming, effort but set up, the parameter of model is difficult for adjusting, and the model of foundation and actual human body physiological characteristic also there are differences.Development along with computer technology, there is the scholar to adopt the mode of Digital Simulation, namely according to the equivalent relation between hemodynamic parameter and the circuit parameter, set up circuit model, the mathematical model of equivalence, simulate on computers the running status of cardiovascular system of human body.Adopt digital simulation method to have to save time, laborsaving, expense is low, model parameter is convenient to adjust, and can realize the advantages such as experiment under the extreme case, is convenient to study its inherent law.But these methods mostly are that the cardiovascular system of human body normal condition is carried out analog simulation at present, also there is the scholar that the mitral valve insufficiency situation is carried out analog simulation (Deng Min, the ultrasonic imaging simulation [D] of mitral regurgitation, Sichuan University, master thesis, 2006; Open and build, the quantitatively ultrasonic simulation research [D] of calculating of the eccentric anti-stream of bicuspid valve, Sichuan University, master thesis, 2007).But in these emulation modes for mitral valve insufficiency, have the following disadvantages:

1) present mitral valve insufficiency emulation mode is not coupled together systemic pulmonary circulation, three circulation systems of systemic circulatory system and cardiac cycle system.Because pulmonary circulation, body circulation, cardiac cycle system all can exert an influence to mitral reflux, need consider the impact of these three circulation systems when therefore analyzing mitral reflux.If only consider the cardiac cycle system, will produce larger error to the simulation calculation of mitral reflux.

2) emulation that present mitral valve insufficiency emulation mode can not be quantitative is the mitral valve insufficiency situation in various degree, only can emulation " existence " or " not existing " mitral valve insufficiency phenomenon.Owing to there being clinically mitral valve insufficiency phenomenon in various degree, therefore need to carry out emulation with a method that can change continuously, can quantificational expression in various degree mitral valve insufficiency, could be more near actual phenomenon.

3) present mitral valve insufficiency emulation mode only emulation the blood reflux situation, and the variation that can not measure the related physiological parameters such as left ventricular pressure, left ventricular volume, left atrial pressure, atrium sinistrum volume, pulmonary venous pressure, bicuspid valve flow, bicuspid valve volume.These physiological parameters are also significant to the research of mitral valve insufficiency.

Summary of the invention

The object of the invention is to the deficiency for existing mitral valve insufficiency emulation mode, provide and to consider that systemic pulmonary circulation, systemic circulatory system and cardiac cycle system are on the impact of mitral reflux, quantitative emulation is the mitral valve insufficiency situation in various degree, accurate Calculation blood reflux and other related physiological parameters situations, thereby the digital simulation method of a kind of mitral valve insufficiency blood reflux of offering help for the research of mitral valve insufficiency.

The present invention includes following steps:

One, according to the equivalent relation between hemodynamic parameter and the circuit parameter, the cardiovascular dynamic circuit model of four chamber lumped parameters of foundation and systemic pulmonary circulation, systemic circulatory system, left heart circulation system, the equivalence of right heart circulation system;

In step 1,

The circuit module M of described and the equivalence of left heart circulation system _LHConsisted of by following mode: resistance R _MOne is terminated at P _LANode, resistance R _MThe other end and diode D _MAnodal series connection, diode D _MNegative pole is connected to P _LVNode; P _LANode, P _LVNode respectively by the time become elastance E _LA(t) and E _LV(t) ground connection;

The circuit module M of described and systemic circulatory system equivalence _TConsisted of by following mode: resistance R _APOne be terminated at P _APNode, resistance R _APThe other end and inductance L _APSeries connection, inductance L _APThe other end and resistance R _ADBe connected in P _ADNode, resistance R _ADThe other end be connected in P _VCNode; P in the circuit _APNode, P _ADNode, P _PVThese 3 of nodes pass through respectively capacitor C _AP, C _AD, C _PVCGround connection;

The circuit module M of described and systemic pulmonary circulation equivalence _FConsisted of by following mode: resistance R _PAOne be terminated at P _PANode, resistance R _PAThe other end and inductance L _PASeries connection, inductance L _PAThe other end and resistance R _PPBe connected in P _PPNode, resistance R _PPThe other end be connected in P _PVNode; P in the circuit _PANode, P _PPNode, P _PVThese 3 of nodes pass through respectively capacitor C _PA, C _PP, C _PVGround connection;

The circuit module M of described and the equivalence of right heart circulation system _RHConsisted of by following mode: resistance R _TOne is terminated at P _RANode, resistance R _TThe other end and diode D _TAnodal series connection, diode D _TNegative pole is connected to P _RVNode; P _RANode, P _RVNode respectively by the time become elastance E _RA(t) and E _RV(t) ground connection;

Described circuit module M _LHConnecting resistance R _AOne end, resistance R _AThe other end and diode D _AAnodal series connection, diode D _ANegative pole and circuit module M _TLink to each other; Resistance R _VCOne is terminated at circuit module M _T, resistance R _VCThe other end is connected to circuit module M _RHCircuit module M _RHConnecting resistance R _PTOne end, resistance R _PTThe other end and diode D _PTAnodal series connection, diode D _PTNegative pole and circuit module M _FLink to each other; Circuit module M _FConnecting resistance R _PVOne end, resistance R _PVOther end connection circuit module M _LH

The emulation physiological significance of the implication of each components and parts and expression in the circuit is as shown in table 1;

Table 1

Symbol	The emulation physiological significance	The actual physics element
			R M	The bicuspid valve characteristic impedance	Resistance
R A	The aorta petal characteristic impedance	Resistance
			R T	The tricuspid valve characteristic impedance	Resistance
R PT	The pulmonary valve characteristic impedance	Resistance
			R AP	The characteristic impedance of sustainer proximal part	Resistance
C AP	Sustainer proximal part blood flow compliance	Electric capacity
			L AP	Sustainer proximal part blood flow inertia	Inductance
R AD	The characteristic impedance of sustainer distal end	Resistance
			C AD	Sustainer distal end blood flow compliance	Electric capacity
R VC	The vena cave characteristic impedance	Resistance
			C VC	Vena cave blood flow inertia	Electric capacity
R PA	The characteristic impedance of pulmonary artery proximal part	Resistance
			C PA	Pulmonary artery proximal part blood flow compliance	Electric capacity
L PA	Pulmonary artery proximal part blood flow inertia	Inductance
			R PP	The characteristic impedance of pulmonary artery distal end	Resistance
C PP	Pulmonary artery distal end blood flow compliance	Electric capacity
			R PV	The pulmonary vein characteristic impedance	Resistance
C PV	Pulmonary Venous Flow inertia	Electric capacity
			E RV(t)	Become Elastic Function during right ventricle	The time become elastance
E RA(t)	Become Elastic Function during the atrium dextrum	The time become elastance
			E LV(t)	Become Elastic Function during left ventricle	The time become elastance
E LA(t)	Become Elastic Function during the atrium sinistrum	The time become elastance
			D A	The aorta petal on off state	Diode
D T	The tricuspid valve on off state	Diode
			D PT	The pulmonary valve on off state	Diode
D M	The mitral valve insufficiency degree	Diode

E in the circuit _RV(t), E _RA(t), E _LV(t), E _LA(t) become the time elastance respectively when following the change Elastic Function represent:

(1) E _LA(t) locate the time become Elastic Function into:

E _LA(t)＝E _minLA+(E _maxLA-E _minLA)×En(t)

Wherein:

E _MaxLABecome the Elastic Function maximum occurrences during expression atrium sinistrum,

E _MinLABecome the minimum value of Elastic Function during the expression atrium sinistrum,

En (t) represents with following formula:

Wherein: t represents time variable, and T represents cardiac cycle, T _AcExpression atrial contraction start time, T _AcpThe expression atrial contraction duration, T _ArExpression auricular diastole start time, T _ArpThe expression atrium Active Diastolic duration;

(2) E _RA(t) locate the time become Elastic Function into:

E _RA(t)＝E _minRA+(E _maxRA-E _minRA)×En(t)

Wherein:

E _MaxRABecome the Elastic Function maximum occurrences during expression atrium dextrum,

E _MinRABecome the minimum value of Elastic Function during the expression atrium dextrum,

Shown in the method for expressing of En (t) is the same, namely use formula (1) expression;

(3) E _RV(t) locate the time become Elastic Function into:

E _RV(t)＝E _minRV+(E _maxRV-E _minRV)×En(t)

Wherein:

E _MaxRVBecome the Elastic Function maximum occurrences during expression right ventricle,

E _MinRVBecome the minimum value of Elastic Function during the expression right ventricle,

En (t) represents with following formula:

Wherein:

T represents time variable, and T represents cardiac cycle, T _dThe expression ventricular systole time;

(4) E _LV(t) locate the time become Elastic Function into:

E _LV(t)＝E _minLV+(E _maxLV-E _minLV)×En(t)

Wherein:

E _MaxLVBecome the Elastic Function maximum occurrences during expression left ventricle,

E _MinLVBecome the minimum value of Elastic Function during the expression left ventricle,

Shown in the method for expressing of En (t) is the same, namely use formula (2) expression;

(5) D in the circuit _MValue be:

$D_M=\left\{\begin{array}{c}1,\mathrm{\&Delta;P}\&GreaterEqual;0\\ 0~1,\mathrm{\&Delta;P}<0\end{array}\right.$

Δ P is expressed as P _LAWith P _LVThe voltage difference at place,

When Δ P＜0,0≤D _M＜1, D _MExpression mitral valve insufficiency degree, be one can change continuously, can the quantificational expression parameter, work as D _MEqual to represent not exist the normal physiological state of mitral valve insufficiency pathology at 0 o'clock, D _MThe larger expression mitral valve insufficiency of value degree more serious.

Two, the circuit model of setting up according to step 1, the dynamic circuit of setting up with the State-Variable Analysis Method analysis, to interdependent node in the circuit according to the corresponding state equation of following Formula;

$(P_{\mathrm{LV}}-P_{\mathrm{AP}})D_A/R_A=Q_{\mathrm{AP}}+C_{\mathrm{AP}}\frac{d{P}_{\mathrm{AP}}}{\mathrm{dt}}$

$P_{\mathrm{AP}}-P_{\mathrm{AD}}=L_{\mathrm{AP}}\frac{d{Q}_{\mathrm{AP}}}{\mathrm{dt}}+Q_{\mathrm{AP}}{R}_{\mathrm{AP}}$

$Q_{\mathrm{AP}}=(P_{\mathrm{AD}}-P_{\mathrm{VC}})/R_{\mathrm{AD}}+C_{\mathrm{AD}}\frac{d{P}_{\mathrm{AD}}}{\mathrm{dt}}$

$(P_{\mathrm{AD}}-P_{\mathrm{VC}})/R_{\mathrm{AD}}=C_{\mathrm{VC}}\frac{d{P}_{\mathrm{VC}}}{\mathrm{dt}}+\frac{P_{\mathrm{VC}}-P_{\mathrm{RA}}}{R_{\mathrm{VC}}}$

$(P_{\mathrm{RV}}-P_{\mathrm{PA}})D_{\mathrm{PT}}/R_{\mathrm{PT}}=C_{\mathrm{PA}}\frac{d{P}_{\mathrm{PA}}}{\mathrm{dt}}+Q_{\mathrm{PA}}$

$P_{\mathrm{PA}}-P_{\mathrm{PP}}=Q_{\mathrm{PA}}{R}_{\mathrm{PA}}+L_{\mathrm{PA}}\frac{d{Q}_{\mathrm{PA}}}{\mathrm{dt}}$

$Q_{\mathrm{PA}}=C_{\mathrm{PP}}\frac{d{P}_{\mathrm{PP}}}{\mathrm{dt}}+(P_{\mathrm{PP}}-P_{\mathrm{PV}})/R_{\mathrm{PP}}$

$(P_{\mathrm{PP}}-P_{\mathrm{PV}})/R_{\mathrm{PP}}=C_{\mathrm{PV}}\frac{d{P}_{\mathrm{PV}}}{\mathrm{dt}}+(P_{\mathrm{PV}}-P_{\mathrm{LA}})/R_{\mathrm{PV}};$

Three, according to the demand of emulation, the relevant parameter in setting steps one, the step 2, and the state equation that arranges of the circuit model that arranges according to step 1 and step 2 carry out the solving state equation and obtain a node time curve map in the circuit; The parameter of required setting and the implication of expression thereof are as shown in table 2, and the time plot of a node represents that implication is as shown in table 3 in the circuit.

Table 2

Symbol	The emulation physiological significance
		R M	The bicuspid valve characteristic impedance
R A	The aorta petal characteristic impedance
		R T	The tricuspid valve characteristic impedance
R PT	The pulmonary valve characteristic impedance
		R AP	The characteristic impedance of sustainer proximal part
C AP	Sustainer proximal part blood flow compliance
		L AP	Sustainer proximal part blood flow inertia
R AD	The characteristic impedance of sustainer distal end
		C AD	Sustainer distal end blood flow compliance
R VC	The vena cave characteristic impedance
		C VC	Vena cave blood flow inertia g
R PA	The characteristic impedance of pulmonary artery proximal part
		C PA	Pulmonary artery proximal part blood flow compliance
L PA	Pulmonary artery proximal part blood flow inertia
		R PP	The characteristic impedance of pulmonary artery distal end
C PP	Pulmonary artery distal end blood flow compliance
		R PV	The pulmonary vein characteristic impedance
C PV	Pulmonary Venous Flow inertia g
		T	Cardiac cycle
T d	Ventricular systole time
		T ac	The atrial contraction start time
T acp	The atrial contraction duration
		T ar	The auricular diastole start time
T arp	The atrium Active Diastolic duration
		E minLA	Become the minimum value of Elastic Function during left ventricle
E maxLA	Become the Elastic Function maximum occurrences during left ventricle
		E minRA	Become the minimum value of Elastic Function during right ventricle
E maxRA	Become the Elastic Function maximum occurrences during right ventricle
		E minLV	Become the minimum value of Elastic Function during the atrium sinistrum
E maxLV	Become the Elastic Function maximum occurrences during atrium sinistrum
		E minRV	Become the minimum value of Elastic Function during the atrium dextrum
E maxRV	Become the Elastic Function maximum occurrences during atrium dextrum
		D M	The mitral valve insufficiency degree

Table 3

The node symbol	The emulation physiological significance
		P LV	Left ventricular pressure
P LA	Left atrial pressure
		P AP	Aortic pressure
V LV	The atrium sinistrum volume
		V LA	Left ventricular volume
P PV	Pulmonary venous pressure
		Q M	The bicuspid valve flow

Four, the Q that step 3 is obtained _MCalculate blood reflux amount V when obtaining mitral valve insufficiency according to following formula _RM, bicuspid valve forward direction output quantity V _FMAnd bicuspid valve volume V _M,

$V_{\mathrm{RM}}=-{\&Integral;}_{{\mathrm{<figure-callout\; id="0"\; label="T"\; filenames="HDA00003626458100032.png,HDA00003626458100033.png"\; state="\{\{state\}\}">T</figure-callout>}}_0+T_d}^{{\mathrm{<figure-callout\; id="0"\; label="T"\; filenames="HDA00003626458100032.png,HDA00003626458100033.png"\; state="\{\{state\}\}">T</figure-callout>}}_0+T}{Q}_M\left(t\right)\mathrm{dt},{\mathrm{<figure-callout\; id="0"\; label="T"\; filenames="HDA00003626458100032.png,HDA00003626458100033.png"\; state="\{\{state\}\}">T</figure-callout>}}_0+T_d\&le;t\&le;{\mathrm{<figure-callout\; id="0"\; label="T"\; filenames="HDA00003626458100032.png,HDA00003626458100033.png"\; state="\{\{state\}\}">T</figure-callout>}}_0+T$

$V_{\mathrm{FM}}={\&Integral;}_{T_0}^{{\mathrm{<figure-callout\; id="0"\; label="T"\; filenames="HDA00003626458100032.png,HDA00003626458100033.png"\; state="\{\{state\}\}">T</figure-callout>}}_0+T_d}{Q}_M\left(t\right)\mathrm{dt},{\mathrm{<figure-callout\; id="0"\; label="T"\; filenames="HDA00003626458100032.png,HDA00003626458100033.png"\; state="\{\{state\}\}">T</figure-callout>}}_0\&le;t\&le;{\mathrm{<figure-callout\; id="0"\; label="T"\; filenames="HDA00003626458100032.png,HDA00003626458100033.png"\; state="\{\{state\}\}">T</figure-callout>}}_0+T_d$

$V_M={\&Integral;}_{T_0}^{{\mathrm{<figure-callout\; id="0"\; label="T"\; filenames="HDA00003626458100032.png,HDA00003626458100033.png"\; state="\{\{state\}\}">T</figure-callout>}}_0+T}{Q}_M\left(t\right)\mathrm{dt},{\mathrm{<figure-callout\; id="0"\; label="T"\; filenames="HDA00003626458100032.png,HDA00003626458100033.png"\; state="\{\{state\}\}">T</figure-callout>}}_0\&le;t\&le;{\mathrm{<figure-callout\; id="0"\; label="T"\; filenames="HDA00003626458100032.png,HDA00003626458100033.png"\; state="\{\{state\}\}">T</figure-callout>}}_0+T$

T in the formula ₀Represent the start time of arbitrary cardiac cycle, T represents cardiac cycle.

The digital simulation method of a kind of mitral valve insufficiency blood reflux that the present invention proposes, substitute physical model in kind, dynamic Real Time Observation simulation result, this method shortens experimental period, decrease cost, the dirigibility of Enhancement test and security can be simulated the phenomenon that some can't produce on human body, animal and physical model in kind.The digital simulation method of the mitral valve insufficiency blood reflux that the present invention proposes has overcome existing methodical weak point, combine systemic pulmonary circulation, three systems of systemic circulatory system and cardiac cycle system, can change continuously, quantificational expression mitral valve insufficiency degree, can accurate Calculation blood reflux and other related physiological parameters situations, the clinical research mitral valve insufficiency is had great importance.

Description of drawings

Fig. 1 is the cardiovascular circuit model of four chamber lumped parameters that comprises systemic pulmonary circulation, systemic circulatory system and cardiac cycle system of the embodiment of the invention.

Fig. 2 is left ventricular pressure time curve simulation result figure.

Fig. 3 is left ventricular volume time curve simulation result figure.

Fig. 4 is left atrial pressure time curve simulation result figure.

Fig. 5 is atrium sinistrum volume time curve simulation result figure.

Fig. 6 is pulmonary venous pressure time curve simulation result figure.

Fig. 7 is bicuspid valve flow time curve simulation result figure.

Fig. 8 is bicuspid valve volume time curve simulation result figure.

Embodiment

The present invention will be further described in connection with accompanying drawing for following examples.

The concrete steps of the embodiment of the invention are as follows:

Step 1,

Set up the cardiovascular dynamic circuit model of four chamber lumped parameters according to Fig. 1, the emulation physiological significance of the implication of each components and parts and expression in the circuit is as shown in table 1.

Step 2,

The circuit model of setting up according to step 1, the dynamic circuit of setting up with the State-Variable Analysis Method analysis, to interdependent node in the circuit to specifications in the corresponding state equation of Formula.

Step 3, relevant parameter (seeing table 4 for details) and solving state equation, wherein D are set _MValue according to following formula, expression emulation moderate mitral valve insufficiency situation.

$D_M=\left\{\begin{array}{c}1,\mathrm{\&Delta;P}\&GreaterEqual;0\\ 0.01,\mathrm{\&Delta;P}<0\end{array}\right.$

Table 4

Parameter	Value
		R M	0.007mmHg*s/ml
R A	0.01mmHg*s/ml
		R T	0.007mmHg*s/ml
R PT	0.01mmHg*s/ml
		R AP	0.230mmHg*s/ml
C AP	1.800ml/mmHg
		L AP	0.014mmHg*s2/ml
R AD	1.000mmHg*s/ml
		C AD	0.140ml/mmHg
R VC	0.0368mmHg*s/ml
		C VC	2.5181ml/mmHg
R PA	0.023mmHg*s/ml
		C PA	5.000ml/mmHg
L PA	0.0018mmHg*s2/ml
		R PP	0.100mmHg*s/ml
C PP	5.800ml/mmHg
		R PV	0.0056mmHg*s/ml
C PV	25.00ml/mmHg
		E minLA	0.15mmHg/ml
E maxLA	0.25mmHg/ml
		E minRA	0.15mmHg/ml
E maxRA	0.25mmHg/ml
		E minLV	0.06mmHg/ml
E maxLV	3mmHg/ml
		E minRV	0.06mmHg/ml
E maxRV	1mmHg/ml
		T	0.8
T ac	0.69
		T acp	0.10
T ar	0.79
		T arp	0.10

Adopt fourth order Runge-Kutta method finding the solution state equation.Obtain main state variable (P _LV, V _LV, P _LA, V _LA, P _PV) time plot, such as Fig. 2～6.

Step 4, the Q that step 3 is obtained _MAccording to such as the capable calculating of the formula in the instructions, blood reflux amount V when obtaining mitral valve insufficiency _RM, bicuspid valve forward direction output quantity V _FMAnd bicuspid valve volume V _M

Result such as Fig. 7 and 8.

It should be noted last that, above embodiment is only unrestricted in order to patented technology scheme of the present invention to be described, although describe the present invention with reference to preferred embodiment, those of ordinary skill in the art is to be understood that, can make amendment or on an equal basis replacement to technical scheme of the present invention, and the spirit and scope that do not break away from the present invention program.

Claims (8)

1. the digital simulation method of a mitral valve insufficiency blood reflux is characterized in that may further comprise the steps:

One, according to the equivalent relation between hemodynamic parameter and the circuit parameter, the cardiovascular dynamic circuit model of four chamber lumped parameters of foundation and systemic pulmonary circulation, systemic circulatory system, left heart circulation system, the equivalence of right heart circulation system;

Two, the circuit model of setting up according to step 1 with the dynamic circuit that the State-Variable Analysis Method analysis is set up, is set up corresponding state equation to interdependent node in the circuit;

Three, according to the demand of emulation, the relevant parameter in setting steps one, the step 2, and the state equation that arranges of the circuit model that arranges according to step 1 and step 2 carry out the solving state equation and obtain a node time curve map in the circuit;

Four, the Q that step 3 is obtained _MCalculate blood reflux amount V when obtaining mitral valve insufficiency _RM, bicuspid valve forward direction output quantity V _FMAnd bicuspid valve volume V _M

2. a kind of digital simulation method of mitral valve insufficiency blood reflux as claimed in claim 1 is characterized in that in step 1, the circuit module M of described and the equivalence of left heart circulation system _LHConsisted of by following mode: resistance R _MOne is terminated at P _LANode, resistance R _MThe other end and diode D _MAnodal series connection, diode D _MNegative pole is connected to P _LVNode; P _LANode, P _LVNode respectively by the time become elastance E _LA(t) and E _LV(t) ground connection.

3. a kind of digital simulation method of mitral valve insufficiency blood reflux as claimed in claim 1 is characterized in that in step 1, the circuit module M of described and systemic circulatory system equivalence _TConsisted of by following mode: resistance R _APOne be terminated at P _APNode, resistance R _APThe other end and inductance L _APSeries connection, inductance L _APThe other end and resistance R _ADBe connected in P _ADNode, resistance R _ADThe other end be connected in P _VCNode; P in the circuit _APNode, P _ADNode, P _PVThese 3 of nodes pass through respectively capacitor C _AP, C _AD, C _PVCGround connection.

4. a kind of digital simulation method of mitral valve insufficiency blood reflux as claimed in claim 1 is characterized in that in step 1, the circuit module M of described and systemic pulmonary circulation equivalence _FConsisted of by following mode: resistance R _PAOne be terminated at P _PANode, resistance R _PAThe other end and inductance L _PASeries connection, inductance L _PAThe other end and resistance R _PPBe connected in P _PPNode, resistance R _PPThe other end be connected in P _PVNode; P in the circuit _PANode, P _PPNode, P _PVThese 3 of nodes pass through respectively capacitor C _PA, C _PP, C _PVGround connection.

5. a kind of digital simulation method of mitral valve insufficiency blood reflux as claimed in claim 1 is characterized in that in step 1, the circuit module M of described and the equivalence of right heart circulation system _RHConsisted of by following mode: resistance R _TOne is terminated at P _RANode, resistance R _TThe other end and diode D _TAnodal series connection, diode D _TNegative pole is connected to P _RVNode; P _RANode, P _RVNode respectively by the time become elastance E _RA(t) and E _RV(t) ground connection.

6. a kind of digital simulation method of mitral valve insufficiency blood reflux as claimed in claim 1 is characterized in that in step 1 described circuit module M _LHConnecting resistance R _AOne end, resistance R _AThe other end and diode D _AAnodal series connection, diode D _ANegative pole and circuit module M _TLink to each other; Resistance R _VCOne is terminated at circuit module M _T, resistance R _VCThe other end is connected to circuit module M _RHCircuit module M _RHConnecting resistance R _PTOne end, resistance R _PTThe other end and diode D _PTAnodal series connection, diode D _PTNegative pole and circuit module M _FLink to each other; Circuit module M _FConnecting resistance R _PVOne end, resistance R _PVOther end connection circuit module M _LH

E in the circuit _RV(t), E _RA(t), E _LV(t), E _LA(t) become the time elastance respectively when following the change Elastic Function represent:

(1) E _LA(t) locate the time become Elastic Function into:

E _LA(t)＝E _minLA+(E _maxLA-E _minLA)×En(t)

Wherein:

E _MaxLABecome the Elastic Function maximum occurrences during expression atrium sinistrum,

E _MinLABecome the minimum value of Elastic Function during the expression atrium sinistrum,

En (t) represents with following formula:

Wherein: t represents time variable, and T represents cardiac cycle, T _AcExpression atrial contraction start time, T _AcpThe expression atrial contraction duration, T _ArExpression auricular diastole start time, T _ArpThe expression atrium Active Diastolic duration;

(2) E _RA(t) locate the time become Elastic Function into:

E _RA(t)＝E _minRA+(E _maxRA-E _minRA)×En(t)

Wherein:

E _MaxRABecome the Elastic Function maximum occurrences during expression atrium dextrum,

E _MinRABecome the minimum value of Elastic Function during the expression atrium dextrum,

Shown in the method for expressing of En (t) is the same, namely use formula (1) expression;

(3) E _RV(t) locate the time become Elastic Function into:

E _RV(t)＝E _minRV+(E _maxRV-E _minRV)×En(t)

Wherein:

E _MaxRVBecome the Elastic Function maximum occurrences during expression right ventricle,

E _MinRVBecome the minimum value of Elastic Function during the expression right ventricle,

En (t) represents with following formula:

Wherein:

T represents time variable, and T represents cardiac cycle, T _dThe expression ventricular systole time;

(4) E _LV(t) locate the time become Elastic Function into:

E _LV(t)＝E _minLV+(E _maxLV-E _minLV)×En(t)

Wherein:

E _MaxLVBecome the Elastic Function maximum occurrences during expression left ventricle,

E _MinLVBecome the minimum value of Elastic Function during the expression left ventricle,

Shown in the method for expressing of En (t) is the same, namely use formula (2) expression;

(5) D in the circuit _MValue be:

$D_M=\left\{\begin{array}{c}1,\mathrm{\&Delta;P}\&GreaterEqual;0\\ 0~1,\mathrm{\&Delta;P}<0\end{array}\right.$

Δ P is expressed as P _LAWith P _LVThe voltage difference at place,

When Δ P＜0,0≤D _M＜1, D _MExpression mitral valve insufficiency degree, be one can change continuously, can the quantificational expression parameter, work as D _MEqual to represent not exist the normal physiological state of mitral valve insufficiency pathology at 0 o'clock, D _MThe larger expression mitral valve insufficiency of value degree more serious.

7. a kind of digital simulation method of mitral valve insufficiency blood reflux as claimed in claim 1 is characterized in that in step 2, and the corresponding state equation of described foundation can be according to following Formula:

$(P_{\mathrm{LV}}-P_{\mathrm{AP}})D_A/R_A=Q_{\mathrm{AP}}+C_{\mathrm{AP}}\frac{d{P}_{\mathrm{AP}}}{\mathrm{dt}}$

$P_{\mathrm{AP}}-P_{\mathrm{AD}}=L_{\mathrm{AP}}\frac{d{Q}_{\mathrm{AP}}}{\mathrm{dt}}+Q_{\mathrm{AP}}{R}_{\mathrm{AP}}$

$Q_{\mathrm{AP}}=(P_{\mathrm{AD}}-P_{\mathrm{VC}})/R_{\mathrm{AD}}+C_{\mathrm{AD}}\frac{d{P}_{\mathrm{AD}}}{\mathrm{dt}}$

$(P_{\mathrm{AD}}-P_{\mathrm{VC}})/R_{\mathrm{AD}}=C_{\mathrm{VC}}\frac{d{P}_{\mathrm{VC}}}{\mathrm{dt}}+\frac{P_{\mathrm{VC}}-P_{\mathrm{RA}}}{R_{\mathrm{VC}}}$

$(P_{\mathrm{RV}}-P_{\mathrm{PA}})D_{\mathrm{PT}}/R_{\mathrm{PT}}=C_{\mathrm{PA}}\frac{d{P}_{\mathrm{PA}}}{\mathrm{dt}}+Q_{\mathrm{PA}}$

$P_{\mathrm{PA}}-P_{\mathrm{PP}}=Q_{\mathrm{PA}}{R}_{\mathrm{PA}}+L_{\mathrm{PA}}\frac{d{Q}_{\mathrm{PA}}}{\mathrm{dt}}$

$Q_{\mathrm{PA}}=C_{\mathrm{PP}}\frac{d{P}_{\mathrm{PP}}}{\mathrm{dt}}+(P_{\mathrm{PP}}-P_{\mathrm{PV}})/R_{\mathrm{PP}}$

$(P_{\mathrm{PP}}-P_{\mathrm{PV}})/R_{\mathrm{PP}}=C_{\mathrm{PV}}\frac{d{P}_{\mathrm{PV}}}{\mathrm{dt}}+(P_{\mathrm{PV}}-P_{\mathrm{LA}})/R_{\mathrm{PV}}.$

8. a kind of digital simulation method of mitral valve insufficiency blood reflux as claimed in claim 1 is characterized in that in step 4 the described Q that step 3 is obtained _MCalculate, can calculate according to following formula:

$V_{\mathrm{RM}}=-{\&Integral;}_{T_0+T_d}^{T_0+T}{Q}_M\left(t\right)\mathrm{dt},T_0+T_d\&le;t\&le;T_0+T$

$V_{\mathrm{FM}}={\&Integral;}_{T_0}^{T_0+T_d}{Q}_M\left(t\right)\mathrm{dt},T_0\&le;t\&le;T_0+T_d$

$V_M={\&Integral;}_{T_0}^{T_0+T}{Q}_M\left(t\right)\mathrm{dt},T_0\&le;t\&le;T_0+T$

T in the formula ₀Represent the start time of arbitrary cardiac cycle, T represents cardiac cycle.

Images