ent 318/3 artificial organsportal.unimap.edu.my/portal/page/portal30/lecture...

ENT 318/3

Artificial Organs

Modeling of cardiovascular

system and VAD

Lecturer

Ahmad Nasrul bin Norali

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What is modeling and why we need it? In designing product, sometimes we have to make sure that the

device we designed will works theoretically before applied to real situation.

Modeling is where we use a physical, mathematical or logical representation of a system of entities, phenomena or processes.

In case of modeling a VAD, we also need to model the cardiovascular system since VAD is designed to work with the heart.

Simulation is where we run our model to study how our model works and examine the result of any parameters that we desire.

For example, if we want to evaluate any closed-loop control system, we model our system with Simulink and run it to simulate the result.

Usually, mathematical and electrical analogy is used to model physiological system including our heart.

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Types of modeling

Three different types of preclinical models are used for

the evaluation and testing of VADs;

-numerical models

-mock circulations

-animal models

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Types of modeling

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Electrical Analogy

Kirchoff‟s law of current and potential can be applied:

1) Sum of currents entering any junction equal sum of currents leaving that junction (conservation of blood mass)

2) Sum of all voltages around a loop equals zero (pressure is potential difference)

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Electrical Analogy

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Electrical Analogy

Blood flowing from wider arteries into smaller arterioles encounters a

certain resistance.

Consider an ideal segment of a cylindrical vessel. The pressure

difference between its two ends and the flow through the vessel

depend on each other.

It can be accurately approximated by a linear relation.

If we indicate by Rc the proportionality constant between the

pressure difference P and the flow F then we can write

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Electrical Analogy

Similarly, a resistor is an electronic component that resists an

electric current by producing a potential difference between its end

points.

According to with Ohm‟s law, the electrical resistance Re is equal to

the potential difference V across the resistor divided by the current I

through the resistor.

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Electrical Analogy

The walls of the vessels are surrounded by muscles that can change the volume and pressure in the vessel.

Consider the blood flow into such an elastic (compliant) vessel.

We denote the flow into the vessel by Fi and the flow out of the vessel by Fo.

Then the difference F = Fi − Fo which corresponds to the rate of change of blood volume in the vessel is related to a change of pressure P inside the vessel.

Assuming a linear relation, we have that

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Electrical Analogy

A capacitor is an electrical device that can store energy between a pair of closely-spaced conductors.

When a potential difference is applied to the capacitor, electrical charges of equal magnitude but opposite polarity build up on each plate.

This process causes an electrical field to develop between the plates of the capacitor.

It gives rise to a growing potential difference across the plates.

This potential difference V is directly proportional to the amount of separated charge Q (e.g. Q = CeV ).

Since the current, I through the capacitor is the rate at which the charge Q is forced onto the capacitor (e.g. I = dQ/dt), this can be expressed mathematically as

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Electrical Analogy

Blood is inert, when a pressure difference is applied between the

two ends of a long vessel that is filled with blood, the mass of the

blood resists the tendency to move due to the pressure difference.

Once more assuming a linear relation between the change of the

blood flow (dF/dt ) and the pressure difference P we can write

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Electrical Analogy

The inertia of blood can be modeled by a coil (also known as an

‟inductor‟)

The current in a coil cannot change instantaneously.

This effect causes the relationship between the potential difference V across a coil with inductance Le and the current I passing through it, which can be modeled by the differential equation

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Electrical analog

(a) A segmented, arbitrary length of vessel.

(b) The equivalent RLC circuit.

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Modeling of Cardiovascular System and VAD

Windkessel Model

Models consist of ordinary differential equations that relate dynamics

of aortic pressure and blood flow to various parameters such as

arterial compliance, resistance to blood flow and inertia of blood.

2-Element Windkessel Model

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P and F represents aortic pressure and blood flow rate in aorta.

C is arterial compliance.

R corresponds to resistance to blood as it passes from aorta to

arterioles.

Rearranging we get,

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Solving the equation by considering diastole period where F=0, we

obtain,

Where P(td) is blood pressure in aorta at starting time of diastole, td


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Addition of Ra which represents resistance encountered by blood as

it enters aortic or pulmonary valve.

Applying Kirchoff law to the model we obtain,

Solving this equation when F=0 we get the same as previous model.


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Coil Lc is added to represent inertia of blood.

Again applying Kirchoff law to the model we obtain,

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Model 1

Electrical Analog Models

Reference :

Y.-C. Yu, J.R. Boston, M. Simaan, and J.F. Antaki, “Estimation of systemic vascular bed parameters for artificial heart control”,

IEEE Trans. Automat. Contr., vol. 43, pp. 765-778, 1998.

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Left ventricle as time varying capacitance.

Systemic circulation as four-element modified Windkessel model.

Pulmonary circulation and left atrium as single capacitance.

Heart valves as diode in series with resistors.

Ejection – DA on and DM off. Blood rapidly ejected to aorta.

Isovolumic Relaxation – DA and DM off. Ventricle relax and pressure

falls.

Passive Filling – DA off and DM on. Blood from venous circulation

returns to ventricle.

Isovolumic Contraction – DA and DM off. Ventricular increases

rapidly without change in volume.

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Model 2

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A time varying nonlinear circuit model of a combined cardiovascular

system and pump used to test feedback controller.

Pressure = v, flow = I.

Left ventricle is modeled as a time varying E (t). Mitral valve and

aortic valve modeled as pressure dependent diodes (or switches)

DM and DA.

Suction is modeled as a nonlinear resistor Rk and SVR as a linear

resistor Rs.

Other components are constant capacitors and inductors.

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Model 3


Reference :

Y. Wu, P. Allaire, G. Tao, and D. Olsen, “Modeling, Estimation and Control of Cardiovascular System with A Left

Ventricular Assist Device”, 2005 American Control Conference, pp. 3841-3846, June 8-10, 2005.

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Model Element Physiological Meaning

CLV Left ventricle

CA Aorta

CV Systemic vein and right atrium

D1 Aortic valve

D2 Mitral valve

TPR Total peripheral resistance

L Blood inertia

RLV Resistance of aortic valve

RV Resistance of vein and left atrium

δm Mean pressure disturbance generated by muscle

pump

δp

Pressure disturbance by pulmonary circulation

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Variables Physiological Meaning

PLV Left ventricular pressure

PA Aortic pressure

PV Central venous pressure

Q Pump flow rate

TPF Total peripheral flow rate

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Model 4


Reference :

J. Porter and Y.-C. Yu, “Pressure-Flow Modeling of A Rotary Ventricular Assist Device”, Bioengineering

Conference 2006 Proc. of the IEEE 32nd Annual Northeast , pp. 123-124.

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Electric circuit model of left heart with VAD.

CLV represents pumping action of heart.

RPin and LPin is VAD inflow resistance and inertance.

RPout and LPout is VAD outflow resistance and inertance.

Voltage source represents hydrostatic pressure generated by pump.

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Mock Circulation Loop (MCL)

In vitro tool for evaluation of cardiovascular device

design including the ventricular assist device.

Simulates human blood circulatory system.

Usually designed in form of hydraulic analogy of the

blood circulation system.

Comprehensive knowledge in cardiovascular anatomy

and hemodynamics is required to develop an accurate

MCL.

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Mock Circulation Loop (MCL)

The mock circulatory loop, including a modified Harvard Apparatus pump (1),

flow meter (2), compliance chamber (3), peripheral resistance valve (4),

reservoir tank (5), and centrifugal pump (6)

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The compliance chamber (3) simulates arterial compliance, which is

the volumetric expansion of cardiovascular tissue in response to

increased pressure. Arterial compliance is needed to dampen

pressure waves and maintain blood pressure as the heart refills with

blood.

The peripheral resistance valve (4) simulates the resistance to blood

flow produced by the transition of larger-diameter arteries to smaller-

diameter arterioles and capillaries.

32 Compliance chamber Peripheral resistance valve


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MCL contains heart and vascular components of systemic and pulmonary circulation.

Systemic and pulmonary loop are in series.

Easily variable vascular parameters to dictate natural hemodynamic values.

Functional parameters from natural cardiovascular system to reproduce expected hemodynamic characteristic for each physiological condition.

Pneumatically actuated ventricular chambers representing the heart.

Open-to-atmosphere atria to replicate atrial compliance.

Atrial chambers change fluid volume in response to venous return.

Compressed air applied to ventricular chambers during systole and vented during diastole.

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There is controller board to control ventricular contraction.

3/2 solenoid valve used in the air driveline.

When solenoid „on‟, compressed air allowed to the chamber for systole.

When solenoid „off‟, air pressure vented for diastole.

Solenoid switching determine heart rate.

Reference:

D. Timms, M. Hayne, K. McNeil and A. Galbraith, “A Complete Mock

Circulation Loop for the Evaluation of Left, Right, and Biventricular

Assist Devices”, Artificial Organs , Vol. 29 No. 7, pp. 564-572, 2005.

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Two cardiac simulators to simulate pulsatile functions of both ventrilces.

Two check valves to simulate mitral valve and aortic valve.

Pneumatic control box controlled air pressure inside the air chamber of cardiac simulator.

Pneumatic control box can be used to adjust heart rate and systolic ratio.

Three airtight tanks represents systemic arterial, systemic venous and pulmonary compliances.

Reference :

Y. Liu, P. Allaire, H. Wood and D. Olsen, “Design and Initial Testing of a Mock Human Circulatory Loop for Left Ventricular Assist Device Performance Testing”, Artificial Organs , Vol. 29 No. 4, pp. 341-345, 2005.

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Mock simulator of the left side of the cardiovascular system.

The ventricle pumps the saline solution in the aorta through the aortic valve (AV).

Aorta is connected to a thin tube, simulating the arterial resistance (APR) and then to the venous reservoir system and to the atrium.

This one is then linked to the mitral valve (MV) and to the ventricle.

Ventricular and aortic pressures (VP, AoP), aortic flow (AoF) are measured by dedicated transducers inserted in the simulator

Reference :

R. Zannoli, I. Corazza, and A. Branzi, “Mechanical simulator of the cardiovascular system”, Physica Medica , Vol. 25, pp. 94-100, 2009.

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Hybrid Mock circulation

Three main parts: A numerical model of the human blood circulation,

the VAD to be evaluated, and the numerical-hydraulic interface in-

between.

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Hybrid Mock circulation

Problems;

The main difficulty in developing such a full-hybrid mock

circulation is the implementation of the numerical-

hydraulic interface between the numerical model and the

VAD.

This interface requires sensors, actuators, and a control

system with a high bandwidth.

Piston actuator as mechanical valves introduces

undesirable hydraulic effects to control the pressure

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Part 1:Numerical circulation model

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Part 1:Numerical circulation model

The model includes a systemic and a pulmonary circulation.

Five-elementWindkesselmodels are used to simulate the arterial systems

Classic Windkessel models are used to simulate the venous systems.

The pressure in both arterial systems is regulated by a baroreflex, which

adapts the arterial resistance.

A cardiac output (CO) autoregulation adapts the unstressed volume of the

systemic veins.

The resistance of the systemic veins is adapted by an Rsv autoregulation.

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Part 2:Nonimplantable mixed-flow

blood pump

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Part 3:Numerical-hydraulic interface

The interaction between the numerical circulation model and the

VAD requires a choice of appropriate interface signals, which are

passed from the VAD to the model and vice versa.

Using the governing differential equation of a turbodynamic VAD

where qvad (t) is the instantaneous flow rate, pus(t) and pds(t) are

the pressures up- and downstream of the VAD, and ω(t) is the pump

speed.

The parameters L, k,R1 , and R2 denote the inertance, the pump

gain, the linear, and the quadratic resistance of the VAD,

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Thank you

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ent 318/3 artificial organsportal.unimap.edu.my/portal/page/portal30/lecture...

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