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Principles of haemodynamic measurements: Pressure and flow measurements calculation of cardiac output Calculation of shunts valve area. DEEPAK NANDAN. Definition of Hemodynamics.

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slide1

Principles of haemodynamic measurements:Pressure and flow measurementscalculation of cardiac outputCalculation of shunts valve area

DEEPAK NANDAN

definition of hemodynamics
Definition of Hemodynamics

Hemodynamics is concerned with the physical and physiological principles governing the movement of blood through the circulatory system.

  • The forces involved with the movement of blood throughout the human circulatory system include:

1. Kinetic and potential energy provided by the cardiac pump

2. Gravity

3. Hydrostatic Pressure

4. Pressure gradients, or differences, between two any points

slide3

Properties of blood itself that affect its flow:

1. Viscosity

2. Inertial mass

3. Volume of blood to be moved

  • Factors that affect the motion of blood through the vascular conduits include:

1. Size of blood vessel

2. Condition of blood vessel

3. Smoothness of lumen

4. Elasticity of muscular layer (tunica media)

5. Destination of blood (distal vascular bed)

definition of physical concepts
Definition of Physical Concepts

PRESSURE: the ratio of a force acting on a surface to the area of the surface

(force per unit area).

Units : Newtons/m², pascal(Pa), atmospheres(atm), mmHg.

FLOW RATE: Amount of fluid passing a given point over a given period of time

Described as either flow volume or flow velocity.

Flow volume is measured in mI/mm or cm3/sec -defined by Poiseuille’s

law.

Flow velocity is measured in cm/sec or m/sec -described by Bernoulli’s principle.

VISCOSITY: The internal friction between adjacent layers of fluid.

Blood is 1.5 times as viscous as water and its viscosity is directly related to hct level

slide5

KINETIC ENERGY: active energy , the energy of motion.

In hemodynamics-described as the forward movement of blood.

POTENTIAL ENERGY: stored energy.

Kinetic energy is transferred into potential energy when it produces a lateral pressure or stretching of vessel walls during systole.

The potential energy is converted back into kinetic energy when the arterial walls rebound during diastole.

slide8

Energy in the blood stream exists in three interchangeable forms: 1)pressure arising from cardiac output and vascular resistance, 2)hydrostatic pressure from gravitational forces,

3)kinetic energy of blood flow

  • TE = (perpendicular pressure + gravitational pressure) + kinetic energy

TE = (P per + P grav) + ½ ρ V²

  • BP—lateral pressure, kinetic energy (also known as the impact pressure or the pressure required to cause flow to stop), and gravitational forces.
  • Kinetic energy- highest in aorta (< 5% contribution)
  • Gravitational forces - important in a standing person, minimal impact while supine
  • The intravascular pressure is responsible for transmural pressure(i.e. vessel distention) and for longitudinal transport of blood.
pressure
Pressure

PRESSURE IN STATIC FLUIDS

Rest- the pressure caused by liquid is α to the depth of the liquid & density

pressure is exerted equally in all directions in a static liquid

External pressure exerted on an enclosed liquid changes the overall pressure.

Pascal’s Principle states that any change of pressure in an enclosed fluid is transmitted undiminished to all parts of the fluid.

ΔP = ρg Δh

magnitude of the gravitational effect (ΔP) is the product of the specific gravity or density of the blood (ρ), the acceleration due to gravity (980 cm/s/s) (g), and the vertical distance above or below the heart (Δh) which is 0.77 mm Hg/cm at the density of normal blood.

HYDROSTATIC PRESSURE

The pressure at a given depth in a static liquid is a result of the weight of the liquid acting on a unit area at that depth plus any pressure acting on the surface of the liquid.

The pressure in any blood vessel below the level of the heart is increased, and the

pressure in any vessel above heart level is decreased by the effect of gravity.

Eg:-in the upright position, when the MAP 100

mm Hg, the mean pr in a large artery in the head (50 cm above ) is 62 mm Hg (100 - [0.77 x 50]) an

the pressure in a large artery in the foot (105 cm

below ) is 180 mm Hg (100 + [0.77 x 105]).

slide12

PRESSURE IN FLOWING FLUIDS

pressure in a flowing liquid depends on the details of the flow process, in contrast to the case of the static liquid

pressure gradient, which is defined as a pressure drop/ unit length.

For a uniform horizontal tube the pg will be the same at all points in the tube if a perfectly uniform flow pattern is maintained

Pressure gradient = P1 – P2 /L

( P1 = entry pressure,P2 = exit pressure, L = length of tubing)

Drops in pressure during flow represent losses in energy.

These losses are largely attributable to friction effects

Viscosity- force that oppose the flow

flow rate
Flow Rate

POISEUILLE’S LAW

The Bernoulli Effect

When fluid flows steadily (without acceleration or deceleration) from one point in a system to another further downstream, its total energy content along any given streamline remains constant, provided there are no frictional losses.

Bernoulli’s equation -rel between kinetic energy, gravitational potential energy, and pressure in a frictionless fluidsystem.

predicts flow velocity and explains the presence of high-velocity jets obtained with Doppler instruments

  • predicts the volume of flow in moving fluids.
  • Q= (P¹-P²)π r4

8ήl

(Q = volume flow P1 = entry pressure P2 = exit pressure l = length of tubing r = radius of tube ή = viscosity of fluid)

As pressure difference or diameter of vessel ↑, volume flow ↑

As length or viscosity ↑, volume↓

predicts volume flow under laminar flow conditions in straight tubes where wall friction is not a significant factor.

slide16

relationship bet bf , resistance, and pressure - modification of Ohm’s law for the flow of electrons in an electrical circuit:

Flow(Q) = pressure gradient (P)/resistance(R)

  • Blood is not an “ideal fluid” and energy (and pressure) is lost as flowing blood overcomes resistance.
  • Resistance to blood flow is a function of viscosity, vessel radius, and vessel length.

relationship is known as Poiseuille’s law

Resistance = 8 × viscosity × length/ π× radius4

Blood flow = π × radius4 × difference in pressure/8 × viscosity × length

Viscosity is also important in determining resistance. Exp relative to water.

  • plasma is 1.7 × viscosity of water and viscosity of blood is 3–4 × viscosity of water, the difference being due to blood cells and particularly hematocrit.
slide17

In the mammalian circulation, resistance is greatest at the level of the arterioles. effective area is much larger (capillaries)

  • arteriolar resistance can be regulated
slide19

Transition from laminar to turbulent flow can be predicted by calculatingtheReynold’s number, which is the ratio of inertial forces to viscous forces

R = diameter × velocity × density/viscosity

(viscosity (ή) of blood is 0.004 Pa s, density (ρ) of blood is approximately 1050 kg/m3, velocity (V) of blood is in m/s, and the diameter of the tube is in m. Reynold’s number is dimensionless.)

  • Aorta- laminar to turbulent flow occurs at Nr bet 2000 and 2500
  • In atherosclerotic arteries &/or branch points,the critical Nr is much lower
  • In severe stenoses, turbulence can be initiated at Reynold’s numbers an order of magnitude less than in the theoretical, straight pipe.
  • Vessel diameter is doubly important for not only is it a direct variable in the equation, it also influences velocity
  • both velocity and diameter decrease in the microcirculation- laminar flow
methods of measuring blood pressure
Methods of Measuring Blood Pressure
  • INTRAVASCULAR METHOD
  • AUSCULTATORY METHOD (Stethoscope and cuff)
  • PALPATION METHOD (Pulses)
  • Reverend stephen Hales measured blood pressure of a horse using a vertical glass tube - 1732
  • Landois ( 1872 ) used a needle in an artery to direct spraying blood onto a moving paper surface-Hemautogram
pressure wave
Pressure wave
  • A complex periodic fluctuation in force per unit area
  • A pressure wave is the cyclical force generated by cardiac muscle contraction
  • Its amplitude and duration are influenced by various mechanical and physiological parameters

1 .force of the contracting chamber

2.surrounding structures - contiguous chambers of the heart pericardium, lungs, vasculature

3.Physiological variables - heart rate, respiratory cycle

fourier analysis
FOURIER ANALYSIS

The complex waveform- (Fourier analysis)-

Mathematical summation of a series of simple sine waves of differing amplitude and frequency- harmonics

Fourier found that each pressure wave is a summation of a series of simple sine waves of differing amplitude and frequency

wiggers principle
Wiggers principle
  • The essential physiologic information is contained within the 1st 10 harmonics of the pressure wave’s Fourier series
  • HR-120/min
    • Fundamental frequency- 2 Hz,
    • 10th harmonic- 20 Hz
  • System with frequency response range upto 20 Hz suffice
slide24

To record pressure accurately, a system must respond with equal amplitude for a given input throughout the range of frequencies contained within the pressure wave

  • If components in a particular frequency range are either suppressed or exaggerated by the transducer system, the recorded signal will be a grossly distorted version of the original physiologic waveform
slide25

Transducer

  • Amplifier
  • Recorder
  • A pressure recording system is said to be adequate if the tenth harmonic of the fundamental frequency of a wave can be recorded with uniform sensitivity
slide26

Sensitivity-

ratio of the amplitude of the recorded signal to the amplitude of the input signal

  • Natural frequency-
    • Frequency at which the system oscillates when shock excited

or

    • The frequency of an input pressure wave at which the ratio of output/input amplitude of a system is maximal
    • Directly proportional to lumen radius
    • Inversely proportional to cath length, √cath compliance, √liquid density
  • Highest natural frequency- short, wide-bore, stiff cath, low-density fluid without air bubbles- overdamped
slide27

Damping- dissipation of the energy of oscillation of a pressure measurement system owing to friction

  • Optimal damping
pressure measurement systems
Pressure Measurement Systems
  • Fluid-filled Systems
  • Micromanometer Catheters
fluid filled systems
Fluid-filled Systems
  • fluid-filled catheter attached to a pressure transducer
  • pressure wave is transmitted by the fluid column within the catheter
  • Pressure measurement system should have the highest possible natural frequency and optimal damping
  • Data should be collected ,with the patient in steady state, in close proximity to one another and before introduction of radiographic contrast.
  • Accurate ‘zero’ reference is essential
  • Transducers must be caliberated frequently (before each rec)
slide32

The pressure transducer -calibrated against a known pressure, and the establishment of a zero reference undertaken at the start of the catheterization procedure

  • To “zero” the transducer, the transducer is placed at the level of the atria, which is approximately midchest
  • If the transducer is attached to the manifold and is therefore at variable positions during the procedure, a second fluid-filled catheter system should be attached to the transducer and positioned at the level of the midchest
phlebostatic axis
Phlebostatic Axis

Intersection of the 4th ICS and

½ the anterior-posterior diameter of the chest

error artifact
ERROR & ARTIFACT

DETERIORATION OF FREQUENCY RESPONSE

  • During the course of study deterioration fr response and damping
  • Air bubbles-> compliance- excessive damping and lower natural freq
  • High freq components of the wave sets the system in oscillation-pressure overshoot( early syst & diastole of ventr pressure curve)
  • flushing
artifacts
Artifacts
  • Movement artifact (WHIP Artifact)

Motion of tip of the catheter within the measured chamber→ Enhance the fluid oscillations of the transducer system

May produce superimposed waves of ±10 mm Hg

Particularly common in PA

    • Render systolic and to a lesser extent diastolic pressures unreliable
    • No way to fix it internally
    • Stabilize externally
    • If whip noted - should indicate that to the physician and consider using mean pressures which are usually not affected
slide38
End hole artifact

An end-hole catheter measures an artificially elevated pressure

because of streaming or high velocity of the pressure wave

Flowing bld- K.E- sudden halt- converted to pressure

This added pressure may range from 2-10 mm Hg

  • Catheter impact artifact

When the catheter is struck by the walls or valves of the cardiac chambers

Common with the pigtail cath in the LV, where the MV hits the cath as they open in early diastole

systolic p amplification in the periphery
Systolic P amplification in the periphery
  • Peak SBP in radial,brachial,femoral > peak SBP in central Ao---- -20-50 mmHg
  • Mean arterial P remains same
  • Largely as a consequence of reflected wave from Aobifurc, art branch, small perivessls
  • Reinforce the peak and trough of the anterograde P wave
micromanometer tipped catheters
Micromanometer –Tipped Catheters
  • Fluid filled system-distortion of wave forms- artifacts, amplification of syst pressure in periphery, damping or augmentation of frequency response system.
  • For precise undistorted high fidelity pressure recordings
  • Micromamometer chips at the end of catheters
  • Interposing fluid column is eliminated
  • Have higher natural frequencies and more optimal damping characteristics
  • To assess pressure waveform contours in a tachy situation, rate of ventricular pressure rise(dp/dt) etc
  • Limitation- additional cost, fragility , time needed for properly calibrating and using the system
techniques for determination of cardiac output
Techniques for determination of cardiac output
  • Fick Oxygen technique
  • Indicator dilution technique
  • Thermodilution technique
  • Angiographic technique
slide43

Adolph Fick 1870

  • The total uptake or release of any substance by an organ is the product of blood flow to the organ and arteriovenous oxygen difference of the substance
  • If no intracardiac shunt PBF=SBF
  • Pulmonary blood flow = oxygen consumption/ arteriovenous oxygen difference across the lungs
  • CO = O2 consumption (ml/min)

-------------------------------------------------------------

arterial O2 content - mixed venous (PA) O2 content

  • O2 consumption varies according to individual, by age and sex
cardiac output
Fick Method- (CONSERVATION OF MASS)cardiac output

rate of O2 consumption

250 ml/min

Flow =

=

= 5 litres/min

[O2] leaving – [O2] entering

190 – 140 ml/litre

rate of O2 consumption

O2 concentration of blood entering lung

O2 concentration of blood leaving lung

lung

assumptions made
Assumptions made
  • Uptake of oxygen by the lungs from the blood is measured instead of measuring the rate at which oxygen is taken up from the lungs by the blood
  • Left ventricular or systemic arterial blood is sampled instead of pulmonary venous blood
  • Due to bronchial venous and thebesian venous drainage oxygen content of systemic arterial blood is 2 to 5ml/l lower than pulmonary venous blood
slide47
Douglas bag method

Polarographic method

Metabolic rate meter by Waters instruments

Parts: oxygen hood /mask

Polarographic oxygen sensor cell

V o2=O2 content in the room air – O2 content in the air flowing past the polarographic cell

Respiratory quotient is assumed

Paramagnetic method

Paramagnetic sensor for measuring O2

Adjusts for temperature and partial pressure of water vapour

Calculates respiratory Q for each patient

Deltatrac II made by sensormedics

  • Older
  • A timed sample of patients expired air is collected in a Douglas bag & analyzed for O2 content and ( Beckman oxygen analyzer) and volume
  • O2 content of room air is also measured
  • Oxygen consumption per l per minute is calculated
slide48

Assumed

  • O2 consumption index – 125 ml / m2
  • BSA Dubois, nomograms
  • 0.007184 × wgt.425 (kg) × height .725 (cm)
  • Mosteller = √(HT cm x Wt Kg )/ 60

Kendrick AH.DirectFick CO: are assummed values of O2 consumption acceptable?Eur Heart J 1988;9:37

arteriovenous difference and extraction reserve
Arteriovenous difference and extraction reserve
  • The extraction of a given nutrient from the circulation is expressed as arteriovenous difference.
  • The factor by which arteriovenous diff can increase at constant flow -- extraction reserve
  • normal extraction reserve for oxygen - 3.
  • AV difference of O2 -30-40 ml/L
sources of error
SOURCES OF ERROR
  • Assumes prevalance of steady state
  • Reflectance oximetry accurate only for a range 45%-98%
  • Improper collection of the mixed venous sample
  • O2 con- error-6%. A-V O2 diff -error -5%
  • The total error Fick CO– about 10 %
  • Resting O2 consumption is 125 mL/m2, or 110 mL/m2 for older patients
  • 6% error by assumption in trials
  • Cardiac output age and BSA dependent
  • Age 7 to 70 yrs -4.5 to 2.5 litre /min /m2
indicator dilution methods
Indicator dilution methods
  • Merely a specific application of fick’s general principle

“An indicator mixed into a unit volume of constantly flowing blood can be used to identify that volume of blood in time, provided the indicator remains in the system between injection and measurement and mixes completely in the blood”

  • Indocyanine green is the indicator usually used
  • Continous infusion & single injection method
  • It is injected as a bolus in to the pulmonary artery and samples are taken from the peripheral systemic artery
  • Severe allergic reactions can occur
slide52
Amount of dye added = 5 mg

Average dye concentration = 2 mg/L

Therefore the volume that diluted the dye =

5mg/2mg per L = 2.5 L

Time it took to go past = 0.5 min

ie flow rate = 2.5 L /0.5 min = 5 L/min

General equation:

time of passage (t) = 0.5 min

~

average conc (X) = 2 mg/L

mass of dye (Q g)

Flow rate =

~

average dye conc (X g/L) x time of passage (t min)

thermodilution method
THERMODILUTION METHOD
  • Fegler 1954 (CONSERVATION OF ENERGY)
  • cold saline or 5% D
  • balloon-tipped flow-directed pvc catheter
  • thermistor at tip
  • opening 25 to 30 cm proximal to the tip
  • Via vein to PA (proximal opening –SVC or RA, thermistor –PA)
  • 5 to 10 mL to proximal port
  • change in temperature at the thermistor recorded
modification of stewart hamilton conservation of heat equation
Modification of Stewart-Hamilton conservation of heat equation

normal curve

  • sharp upstroke
  • smooth curve
  • mildly prolonged

downslope until baseline

slide55

area under the curve is inversely proportional to the flow rate in the pulmonary artery which equals the cardiac output in absence of intracardiac shunt

slide56
adv

Sources of error

Unreliable- TR,PR

Baseline temp fluctuation

Inaccurate in low flow- low output states (overestimation upto 35%)

Empirical correction factor to account for catheter warming may be inadequate

  • easy widely available
  • No withdrawl of blood
  • No arterial puncture
  • Inert and inexpensive indicator
  • No recirculation –analysis simple
  • Less measurement variability and correlation with Fick.
angiographic co
ANGIOGRAPHIC CO
  • Calculated by tracing end diastolic and end systolic images
  • SV= EDV-ESV
  • CO= ( EDV-ESV ) × HR
  • In regurgitation or AF- not accurate
  • But preferred over fick to measure co in calculation of valve areas in combined stenotic and regurgitant lesions
  • Erroneous in RWMA or structurally abnormal ventricles
vascular resistance
VASCULAR RESISTANCE
  • Q = ΔP OHM’S LAW (V=IR)

R

OVERSIMPLIFICATION- pulsatile flow in dynamic and diverse vascular beds

vascular impedence
VASCULAR IMPEDENCE
  • Vascimpedence –pulsatile pressure /pulsatile flow
  • Research use
  • Analogue is Vasc resistance
slide63

Principles of haemodynamic measurements:Pressure and flow measurementscalculation of cardiac outputCalculation of shunts valve area

cardiac catheterization shunt detection
Cardiac Catheterization: Shunt Detection
  • Oximetry Run (Dexter and his associates in 1947)
  • Early recirculation of indicator
  • Early appearance.of indicator in Rt heart
  • Angiography
  • Radio- nuclide techniques.
detection localization and quantification of intracardiac shunts
Detection, localization, andquantification of intracardiac shunts

several methods

  • indicator dilution method is of historical interest
  • Contrast angiography
  • Oximetry, or measurement of the oxygen saturations in various locations

goal of the oxygen saturation run is to measure differences in oxygen saturation in various chambers of the heart

oxygen saturation run
Oxygen saturation run
  • Performed as a catheter is passed through the venous system, right heart, and pulmonary circulation.
  • samples - acquired with the patient breathing room air or a gas mixture ≤ 30% oxygen
  • place the catheter - PA first and then obtain samples as the catheter is withdrawn.

(difficulty advancing the catheter into the pulmonary artery)

ASSUMPTIONS

  • Body is in a steady state during the collection of samples
  • Complete mixing of blood is assumed in all chambers.
  • Blood samples should not be withdrawn into the syringe too rapidly.

( Mattaet al. found that rapid aspiration increased oxygen saturations)

slide67

End-hole catheter (e.g., Swan-G) or with side holes close to tip (e.g., GL)

  • CO by Fick method
  • O2 consumption calculated
  • 2-ml samples under fluoroscopic + pressure wave
  • <7 minutes
  • VPCs, that site should be skipped until the rest of the run has been completed
slide72

EFFECTIVE BLOOD FLOW- fraction of the mixed venous return received by the lungs without contamination by the shunt flow

  • EBF= O2 CONSUMPTION(ml/min)

( PvO2 - MV O2)

1. SIZE OF L R SHUNT (NO R L SHUNT)

= PBF – SBF

2 . SIZE OF L R SHUNT (R L SHUNT ⁺)

= PBF – EBF

3. SIZE OF R L SHUNT

= SBF - EBF

limitations of oximetry run
Limitations of Oximetry Run
  • Sample collection errors.
  • Lack of sensitivity (L-R shunts <20% of PBF not detected)
  • influence of Hb concentration
  • Assumed oxygen saturations
  • Assumed pulmonary vein saturation
  • “Non-physiologic” state
  • Calculated PVRI (basal and post-pulmonary vasodilator) has not been adequatelystandardized .
oximetry run
Oximetry Run
  • Level Step-Up Q.P./Qs
  • Atrial >9% 1.5-1.9
  • ventricular >6% 1.3-1.5
  • Grt Vessel 5% 1.3
  • Any level 8% 1.5

( SVC - PA)

flow ratio
Flow Ratio
  • A ratio <1.5 → small L→R shunt
  • A ratio ≥2.0 → large L→R shunt
  • A ratio betw 1.5 and 2.0 →intermediate
  • A ratio <1.0 → net R→L shunt
    • (irrevpulmvasc D)
class llb
Class llb
  • Closure either percutaneously or surgically, may be considered :-

in the presence of net left-to-right shunting

pulmonary artery pressure less than two thirds systemic levels

PVR less than two thirds SVR

or

when responsive to either pulmonary vd therapy or

test occlusion of the defect

role of cardiac catheterization in assessment of operability
Role of cardiac catheterization in assessment of operability
  • The calculated parameters by catheterization PVR and ratio of PVR to SVR -caveats - should not be taken at their face value in isolation.
  • Vasodilator testing in catheterization lab using 100% oxygen or oxygen with no- has not been shown to be of proven value and does not add significantly to decision making.

( Lock JE, Einzig S, Bass JL, Moller JH. The pulmonary vascular response to supplemental oxygen and its influence on operative results in children with ventricular septal defect. PediatrCardiol. 1982;3:41–6.

Balzer DT, Kort HW, Day RW, et al. Inhaled nitric oxide as a preoperative test (INOP Test I): The INOP Test Study Group. Circulation 2002;1060)

  • Patient with a PVRI of 6 Wood units & PVR/SVR ratio of 0.25 is considered operable.
  • PVRI > 10 Wood units & PVR/SVR ratio of 0.5 is clearly beyond the operable range.
  • Patients with PVRI and PVR/SVR ratio between these values fall in the gray zone

(National Consensus Meeting on “Management of Congenital Heart Diseases in India” held on 26thAugust 2007)

slide79

Operability-determination of the severity of PAH and the degree of vasoreactivity of the pulmonary circulation.

  • Agents used to elicit such reaction should ideally have an effect on PVR but not on the systemic circulation
  • Inhaled 100% oxygen mc.
  • recomm- short-acting vasodil - inhaled no, iv epoprostenol, or adenosine
  • An acute reduction of the mean PAP of 10 mmHg or greater with a resultant mean PAP of 40 mmHg or less without a fall in CO is considered a positive response to acute vasodilator testing
  • In patients with evidence of vasoreactivity during acute testing but high pulmonary vascular resistance and bidirectional shunting

- balloon test occlusion

  • A drop in CO &/ increase in RV filling pressures-may suggest

1)a low likelihood to benefit from permanent repair 2)higher perioperative risk

slide80

On O2 adm- if diastolic pressures fall significantly (10mm Hg) & mean pressure by about 5mm Hg- reversible PAP and operability.

gorlin formula
Gorlin Formula
  • Torricelli's law

1st formula

2nd formula

Combining both

slide83
Geometry of valve – flat valves have greater contraction co-efficient (for similar CSA and volume flow)
slide84

Antegrade flow across MV & TV occur in diastole, AV & PV occur in systole

  • For MV & TV
    • DFP(sec/beat) × HR (bpm)
    • CO in ml/min divided by sec/min during which there is flow
    • → diastolic flow in cm3 /sec
  • For the AV & PV, SEP is substituted for DFP
slide85

DFP begins at MV opening(PCW-LV Crossover) & until end-diastole(peak of R in ECG)SEP begins with AV opening & until dicrotic notch/other evidence of AV closure

slide86

CO- ml/min DFP/SEP- sec/beat HR- beats/min C- empirical constant (0.85-MVA,1.0- AVA)P- mm Hg ( C- empirical constant - calculated valve area (by Gorlin) -actual valve area (at surgery) Mitral Valve = constant 0.7 (later changed 0.85, Aortic valve: assumed to be 1 )

aortic valve area
Aortic Valve Area

AVA= CO/(HR)(SEP)

44.3 √∆P

slide89

Pitfalls

Peak – peak gradient

alignment mismatch

Distortion of pulse -FA

Peripheral pulse amplification

Catheter in LVOT

Central aorta - pressure recovery

Carballo’s sign

slide91

Doppler derived gradients- using CW doppler @ vena contracta

  • Catheter derived gradients- downstream vena contracta- pressure recovery
  • Pressure recovery is more across aortic than at mitral
  • prosthetic valve> native valve.
  • Pressure recovery- exaggerated in

Smaller aorta

Stiffer aorta

Hypertension

  • GRADIENT DERIVED BY CATH IS LOWER THAN DOPPLER DERIVED GRADIENT
aortic stenosis carabello s sign
Aortic Stenosis: Carabello’s Sign
  • Carabello’s Sign: Increase in aortic pressure while withdrawing catheter from Ao V – critical AS
    • An augmentation in periphSBPof >5 mm Hg at the time of LV catheter pullback indicates – signi AS
    • > 80% of pts with an AVA ≤0.5 cm2
lv fa systolic gradient
LV-FA Systolic gradient
  • time delay/systamplific/widening
lvot ao systolic gradient
LVOT-Ao Systolic gradient
  • Catheter tip in LVOT will measure a typical LV-P tracing but can underestimate true LV-Ao gradient by 30 mm Hg
slide96

ideal location for measuring gradient

  • may better reflect the actual overload on the myocardium
mitral valve area
Mitral Valve Area

MVA= CO/(HR)(DFP)

37.7 √∆P

mva pitfalls
MVA-pitfalls

Calculation of cardiac output :

Fick’s method - presence of MR - overestimate MVA

Thermodilution method - not possible in presence of TR

Confounding factors like anemia, fever AF & thyrotoxicosis

Calibration errors

PCWP tracing - delay in transmission

over estimate LA pressure by 2 – 3 mmHg

difficult to obtain wedge position

confirm by noting mean Pr & oxymetry

simplified valve formula for calculation of stenotic cardiac valve areas
Simplified valve formula for calculation of stenotic cardiac valve areas

Based on observation- HR × SEP/DFP × C ≈ 1

Hakki et al

Differs from Gorlins by 18 ± 13% in HR

valve resistance
Valve Resistance

Mean Ao V Gradient/CO per sec of syst flow

slide103

V2 = (CV)2 X 2Gh

  • V= (CV) x √ 2Gh

(h = pressure gradientG = gravitational constant (980 cm/sec2) for conversion cmH2 to units pressure. Cv- coefficient velocity for correcting energy loss (pressure energy- kinetic energy)

  • A= F/V
  • Flow rate= cardiac output/ duration of systole or diastole (SEP/DFP X HR)

Valve area = cardiac output ÷ (HR X SEP)

44.3 X C X √ pressure gradient

( C- empirical constant calculated valve area (by Gorlin) actual valve area (at surgery)

Mitral Valve = constant 0.7 (later changed 0.85, Aortic valve: assumed to be 1 )

Modification: HAKKE

cardiac output (L/ min)

√ MPG

Heart rate: 60- 100/ min

slide104
AVA

Pull back hemodynamics :

Peak – peak gradient

alignment mismatch

Distortion of pulse - femoral artery

peripheral pulse amplification

catheter in LVOT

central aorta - pressure recovery

Carballo’s sign

reflected waves
Reflected waves
  • The forward P wave is modified by summation with a reflected P wave
  • Major effective reflection sites in humans- terminal abdAo (↑reflected W and hence peak Ao P in B/L femoral occlu)
factors affecting magnitude of reflected waves
Factors affecting magnitude of reflected waves
  • Augmenting reflected waves
    • Vasoconstriction
    • CCF
    • HTN
    • Ao/iliofemoral obstruct
    • Valsalva-after release
  • Diminishing reflected waves
    • Vasodilation-fever,NTG
    • Hypovolemia
    • Hypotension
    • Valsalva-strain phase
slide109

The current definition of PAH relies on the presence of a mean pulmonary arterial pressure exceeding 25 mmHg at rest or 30 mmHg during exercise, a left atrial pressure below 15 mmHg, and a normal resting cardiac output, suggesting a resting pulmonary vascular resistance above 3 Wood units.

  • 5% to 10% of patients with CHD (mostly those with late or no repair) develop PAH
  • Venice classification
  • approximately 4% of individuals with CHD followed in tertiary centers develop Eisenmenger syndrome, as opposed to 8% prior to the current operative era
  • VSDs are the most common simple defects causing PAH, with an estimated 10% of all VSDs and 50% of large VSDs-ES