Hemodynamic factors that affect calculated orifice areas in the mitral hancock xenograft valve

Transcatheter "valve-in-valve" mitral valve replacement for patient-prosthesis mismatch: Chronicle of a death foretold

Severe mitral annular calcification (MAC) may represent a challenging issue which can lead to poor outcomes and serious issues such as patient-prosthesis mismatch (PPM). The potential harmful effect of PPM must be prevented through the use of alternative techniques that allow mitral valve replacement with adequately sized bioprostheses in patients with MAC. PPM should be recognized as a contraindication for transcatheter valve-in-valve replacement as it leads to poor outcomes and early prosthetic degeneration.

The relation between transaortic pressure difference and flow during dobutamine stress echocardiography in patients with aortic stenosis

OBJECTIVE

To investigate the relation between transaortic pressure difference and flow in patients with aortic stenosis.

METHODS

50 asymptomatic patients with all grades of aortic stenosis were studied using dobutamine stress echocardiography. Individual plots of mean pressure drop against flow were drawn. Comparisons were made between grades of aortic stenosis as defined by the continuity equation.

RESULTS

A significant linear relation between pressure difference and flow was found in 34 patients (68%). There was a significant curvilinear relation in four (8%), while no significant regression line could be fitted in 12 (24%). In the 34 patients with linear fits, the slopes (mean (SD)) were 0.08 (0.07) in mild, 0.10 (0.04) in moderate, and 0.22 (0.16) in severe aortic stenosis (p = 0. 0055).

CONCLUSIONS

Transaortic pressure difference can be related directly to flow in many patients with all grades of aortic stenosis. However, there are individual differences in slope and intercept suggesting that resistance calculated at rest may not always be representative. Raw pressure drop/flow plots may be an alternative method of describing valve function.

Choosing a prosthetic heart valve

Although most of the available prosthetic heart valves function remarkably well, the variety of available choices attests to the inability of any single one to fulfill the requirements of the ideal valve substitute. The mechanical prostheses include the caged-ball, tilting-disc, and bileaflet valves. Tissue valves available in the United States are the Carpentier-Edwards and Hancock porcine heterograft valves and the Carpentier-Edwards pericardial valve. Review of several large comparative studies on valve performance reveals that the overall results with tissue and mechanical valves are about equal at the end of 10 years. The characteristics of each type of valve substitute dictate the selection of one prosthesis in preference to others for a particular patient. Mechanical prostheses are recommended for patients without contraindications for anticoagulants. Tissue valves are reserved for patients over 65 years of age or for patients in whom anticoagulation is contraindicated. Multiple other patient-related factors need to be considered in selecting the appropriate valve, including the psychosocial situation and patient preference.

Flow dependence of valve area in aortic stenosis: relation to valve morphology

OBJECTIVES

We sought to develop an index of flow dependence of valve area in aortic valve (AoV) stenosis and to determine whether this index is related to structural characteristics of the diseased valve.

BACKGROUND

Many studies of AoV stenosis using Gorlin or continuity equation methods have demonstrated flow dependence (an increase in valve area with increased flow). Variation in flow dependence between patients despite similar flow rates remains unexplained.

METHODS

Dobutamine Doppler echocardiography was used to calculate flow rate and valve area by the continuity equation in 27 patients with aortic stenosis. For each patient the slope of the regression line of valve area to flow rate was determined (slope of flow dependence). Transesophageal echocardiography was used to evaluate features of valve morphology potentially related to the etiology of AoV stenosis and the mechanism of flow dependence.

RESULTS

Mean slope of flow dependence was 0.28 cm2/100 ml per s (range -0.06 to 0.53); flow dependence was significantly >0 in 21 patients and was lower for bicuspid valves (slope 0.21 cm2/100 ml per s) than for tricuspid valves with <10% commissural fusion (slope 0.35, p < 0.01). Off-center/ovoid orifices demonstrated the least flow dependence (slope 0.19), whereas star-shaped orifices showed the most (slope 0.36, p < 0.01). Greater flow dependence was related to a lower percentage of commissural fusion (r = -0.46, p = 0.02) as well as diffuse sclerosis, primarily involving the cusp bodies, rather than localized sclerosis, with involvement of cusp margins.

CONCLUSIONS

The slope of flow dependence of valve area in AoV stenosis differs markedly between patients. More flow dependence was associated with tricuspid valves and the morphologic features characteristic of calcific AoV stenosis, whereas less flow dependence was associated with bicuspid valves and the features of rheumatic disease.

Improved Doppler assessment of the Bjork-Shiley mitral prosthesis using the continuity equation

To assess whether derivation of an effective mitral prosthetic valve area using the continuity equation provides an improved functional assessment of the Bjork-Shiley mitral prosthesis over the pressure half-time method, Doppler echocardiographic studies were performed in 43 patients 12 +/- 7 months following the valve replacement. Effective valve orifice area used as the standard for comparison was determined by a hydraulic formula validated in vitro over a wide range of flow rates. All patients were clinically stable, without evidence of prosthetic dysfunction or aortic regurgitation. Prosthetic mitral valve orifice area determined by the hydraulic formula, by the continuity equation and by pressure half-time method for all prostheses sizes averaged 1.6 +/- 0.46 cm2, 1.83 +/- 0.56 cm2 and 2.34 +/- 0.48 cm2, respectively. Effective valve orifice area by the hydraulic formula had a strong correlation with that derived by the continuity equation (r = 0.86; P < 0.0001; standard error of estimate (S.E.E.), 0.12 cm2), but an insignificant correlation with the area calculated by the pressure half-time method (r = 0.24). Prosthetic mitral valve areas determined by the continuity equation and by pressure half-time method also correlated poorly (r = 0.24). Pressure half-time was affected by heart rate, diastolic filling period, left ventricular fractional shortening and presence of atrial fibrillation (P < 0.001). Thus, using the standard continuity equation to determine the orifice area of the Bjork-Shiley prosthesis in the mitral position provides improved assessment compared with the pressure half-time method.

Simplified method for calculating aortic valve resistance: correlation with valve area and standard formula

Aortic valve resistance (AVR) is a useful index to assess the severity of aortic stenosis. This study compared the standard method to calculate AVR with a simplified method based on the conventional approach for measuring vascular resistance: AVR = (peak-to-peak transaortic pressure gradient/(cardiac output*2.5))*80, where 80 is a conversion factor and 2.5 assumes that the systolic ejection period comprises 40% of the R-R cycle. We compared the standard AVR, the simplified AVR, and the Gorlin-derived value area in 118 patients with pure or dominant aortic stenosis. There was a strong linear correlation between the standard and simplified AVR (r = 0.96, p < .0001). There was a curvilinear relation between the aortic valve area and AVR (r = 0.92, p < .001). In 48 patients with aortic valve area > or = 0.7 cm2, the AVR was < 300 dynes-sec-cm-5 in 45 patients (94%) by the standard method and in 42 patients (88%) by the simplified method (p = NS). In conclusion, our method for measuring AVR is accurate and simpler than the standard method.

Hemodynamic assessment of aortic stenosis

The decision to operate in patients with aortic stenosis is based on the presence of symptoms and hemodynamically significant valvular obstruction. The strengths and limitations of cardiac catheterization and Doppler echocardiography are compared, and the concept of "critical" aortic stenosis is discussed. The recommendation of aortic valve replacement must take into account the symptom status, the hemodynamic significance of the lesion, and the size and type of valve to be implanted.

Mitral valve resistance as a hemodynamic indicator in mitral stenosis

Variability of the valve area calculated by the Gorlin formula has been noted in bioprosthetic and aortic valves, but few data are available for native stenotic mitral valves. Valve resistance has been proposed as an alternative hemodynamic indicator; however, its value in mitral stenosis has not been assessed. Thirty-four patients had simultaneous recordings of left atrial and ventricular pressures, 26 after percutaneous balloon mitral dilatation (PBMD). Patients with shunt or mitral regurgitation were excluded. Mitral valve resistance correlated exponentially with Gorlin mitral area (y = 133*[area]-1.5; p less than 0.0001). Both Gorlin mitral area and mitral resistance improved after PBMD (0.89 +/- 0.07 cm2 to 2.22 +/- 0.15 cm2; p less than 0.001; and 166 +/- 20 to 40 +/- 8 dynes.s.cm-5; p less than 0.001). Gorlin area and mitral resistance correlated with New York Heart Association functional class. After infusion of isoproterenol in 17 patients, there was an increase in Gorlin area (baseline 1.77 +/- 0.22 cm2, change 0.23 +/- 0.10; p less than 0.03), whereas mitral resistance did not change (baseline 96 +/- 16 dynes.s.cm-5, change 2 +/- 5; p = not significant). Mitral resistance is valuable in the assessment of mitral stenosis. It varies less than Gorlin mitral area under changing hemodynamic conditions.

Demonstration of postvalvuloplasty hemodynamic improvement in aortic stenosis based on Doppler measurement of valvular resistance

It was recently suggested that valvular resistance, defined as the pressure gradient/flow rate ratio, may better depict the hemodynamic impairment in aortic stenosis than does valve area. The relation between aortic valve resistance and left ventricular mechanics was studied with Doppler echocardiography in 13 patients (mean age 85 years) with severe aortic stenosis who underwent percutaneous balloon valvuloplasty. The Doppler-estimated peak valvular resistance, defined as the ratio of peak transvalvular pressure gradient to peak valvular flow rate, decreased from 510 +/- 190 dynes.s.cm-5 before valvuloplasty to 300 +/- 110 dynes.s.cm-5 after the procedure (p = 0.0001). There was a close linear relation between valvular resistance measured at catheterization and Doppler-derived peak valvular resistance (r = 0.91). After valvuloplasty, left ventricular ejection fraction increased from 53 +/- 13% to 62 +/- 11% (p = 0.0001). The percent increase in ejection fraction was linearly related to the percent decrease in end-systolic wall stress (r = 0.56), which was in turn related to the percent decrease in peak valvular resistance (r = 0.75). No such linear relation existed between the percent changes in valve area and those in end-systolic wall stress. In conclusion, hemodynamic improvement after valvuloplasty is more closely related to changes in valvular resistance than to changes in valvular area. It is suggested that valvular resistance can be estimated accurately by Doppler echocardiography with use of a simple method and should be a primary consideration in assessing the hemodynamics of aortic stenosis.

Theoretical and practical differences between the Gorlin formula and the continuity equation for calculating aortic and mitral valve areas

Although the Gorlin formula and the continuity equation are both used to calculate valvular areas in the clinical situation, there have been few comparisons of the 2 methods. Mathematically, it can be shown that both formulas are derived from similar hydrodynamic principles which basically give a measure of the physiologic or effective area occupied by flow. However, the Gorlin formula contains errors in formulation and incorporates a constant that purports to give a measure of the anatomic rather than of the effective area of the valve. If both formulas are applied to the same hemodynamic data from aortic and mitral bioprostheses studied in a pulse duplicator system, the Gorlin formula constantly yields results 1 to 2% higher than the continuity equation for aortic valves and 12 to 13% higher for mitral valves. For any given type and size of prosthesis, the areas calculated by either formula increase linearly in relation to increasing pressure and flow (up to 20% for aortic valves and up to 35% for mitral valves). It is concluded that the Gorlin formula and the continuity equation are both pressure- and flow-dependent and are primarily related to the effective area occupied by flow rather than to the anatomic area of the valve. The 2 methods yield consistently different results due to differences in mathematical formulation. Such factors are important to consider when interpreting valve area calculations clinically.

Respective timing of maximal color Doppler jet areas and of peak velocity of jets in left-sided valvular lesions: clinical implications

Time intervals between the R wave of the electrocardiogram and maximal dimension of jet areas of color Doppler and the R wave of the electrocardiogram and peak velocity of valvular jets of continuous-wave Doppler were compared by use of paired and correlative studies for a group of 55 patients with a total of 71 left-sided lesions. Mean values of both time intervals, mean difference, and its standard error were equal to zero for stenoses. Time intervals of 71% for mitral stenosis and 52% for aortic stenosis did not differ by more than 0.01 second; correlation coefficients were 0.96 for mitral stenosis and 0.85 for aortic stenosis. For regurgitations, differences in mean values and a mean difference with a standard error were found but remained unsignificant. However, the percentage of differences in time intervals below or equal to 0.01 second decreased to 35 for aortic regurgitation and 13 for mitral regurgitation, which showed the widest 95% range of differences. Correlation coefficients were 0.84 for the aortic regurgitation and 0.33 for mitral regurgitation. Thus the close relationship of time intervals suggests that standardized timing of area measurements at peak velocity is feasible for stenoses and remains under consideration for aortic regurgitation. Timing of measurements should remain empiric for mitral regurgitation.

Doppler echocardiography versus cardiac catheterization in the evaluation of valvular heart disease: do we have a gold standard?

Definitive evaluation of valvular heart disease is traditionally accomplished by cardiac catheterization. Recent advances in Doppler echocardiography allow noninvasive assessment of valvular heart disease with a high degree of accuracy compared to the cardiac catheterization gold standard. Doppler echocardiography may occasionally yield erroneous results due to technical difficulties in the performance of the study. A number of patient related and echo-machine related factors may also affect the Doppler measurements independent of the severity of the lesion. Thus, a discrepancy between Doppler and catheterization data is generally considered to be a failure of Doppler methods. However, catheterization data may also be flawed due to errors in the measurement of pressure and cardiac output, as well as the known shortcomings of qualitative angiography. The Gorlin equation itself suffers from several limitations, including the substitution of pressure gradient for velocity in the basic hydrodynamic equation, and the use of a constant which may not be appropriate in all circumstances. Therefore, when Doppler echocardiography and cardiac catheterization yield discordant results, both studies should be carefully reviewed and correlated with other clinical data in order to elucidate the sources of the discrepancy and ascertain the actual severity of the valvular lesion.

Validation of the orifice formula for estimating effective heart valve opening area

Interest in the Gorlin formula for estimating heart valve effective orifice area (EOA) has recently been rekindled and the formula itself has been challenged. In this validation study, explanted native heart valves, unimplanted mechanical prostheses, unimplanted bioprostheses and explanted bioprostheses have been tested in vitro in a pulsatile flow simulator. Pressures have been measured 30 mm upstream and 100 mm downstream from the plane of the valve sewing ring (to give pressure drop, pd in kPa). Flow (Q in 1 min-1) has been measured directly by electromagnetic flowmeter and orifice areas have either been taken from manufacturer supplied data (mechanical valves) or have been digitised from video images at maximum orifice (biological valves). The formula EOA = Q/(6.96 x pd 1/2) - 0.7 fitted the data with good correlation, r = 0.96 (n = 179). The orifice assumption on which this formula is based (cf. Gorlin formula) is confirmed though it is recommended that the formula should be modified to account for (i) the pressure recovery phenomenon and (ii) the fact that forward flow through a valve only occurs over a portion of the cycle in pulsatile flow. Heart rates used in the study ranged from 40 to 140 min-1, stroke volumes ranged from 20 to 114.3 ml, cardiac outputs from 2.0 to 8.0 1 min-1 and peripheral resistance from 0.1 to 1.6 kPa 1-1 min (1 - 12 mmHg l-1 min). Application of the formula was independent of the flow conditions.

Flow characteristics of bioprosthetic heart valves

A review of the in vivo and in vitro fluid dynamic performance of three bioprosthetic heart valves is presented. Data on Hancock porcine valves (standard models 242 aortic and 342 mitral and modified orifice model 250 aortic), Carpentier-Edwards porcine valves (model 2625 aortic and 6625 mitral), and the Ionescu-Shiley pericardial valve are reviewed. These valves were chosen because of their past or present popularity in clinical use and because of the variation in fluid dynamic performance reported by different investigators. The flow parameters that are reported include in vivo and in vitro mean pressure drop, cardiac output or cardiac index, regurgitant volume, effective orifice area, and performance index. These data provide a framework for differentiation of normal and abnormal bioprosthetic valve function.

The determination of aortic valve area by the Gorlin formula: what the cardiac sonographer should know

The application of the Gorlin formula in the cardiac catheterization laboratory is the standard of reference for the determination of aortic valve area. The continuity equation now enables the cardiac sonographer to determine aortic valve area noninvasively in the echocardiography laboratory. The comparison of the results obtained by the two methods is inevitable. The cardiac sonographer should have a basic understanding of the theory and pitfalls of the Gorlin formula so that when conflicting results are obtained, the possible reasons why will be clear.

Determination of aortic valve area by two-dimensional and Doppler echocardiography in patients with normal and stenotic bioprosthetic valves

To assess the feasibility and accuracy of determining bioprosthetic aortic valve area from two-dimensional and Doppler echocardiographic measurements, three partially overlapping groups were selected from 55 patients with such bioprosthetic valves and adequate Doppler studies. These were Group 1, 37 patients with recent aortic valve replacement surgery and no clinical or echocardiographic evidence of valve dysfunction; Group 2, 12 patients with prosthetic valve stenosis documented by cardiac catheterization; and Group 3, 22 patients with both Doppler and catheterization studies in whom noninvasive and invasive determinations of aortic valve area could be directly compared. Left ventricular outflow tract diameter was measured from two-dimensional still frame images. Flow velocity proximal to the aortic valve, transvalvular velocity and acceleration time were determined from pulsed and continuous wave Doppler spectra. Aortic valve gradient was calculated with the modified Bernoulli equation and valve area by the continuity equation. In the 37 patients with a normally functioning valve, the calculated mean gradient ranged from 5 to 25 mm Hg (average 13.6 +/- 5.2) and valve area from 1.0 to 2.3 cm2 (mean 1.6 +/- 0.31). Linear regression analysis of prosthetic aortic valve area determined by Doppler imaging and cardiac catheterization demonstrated a high correlation (r = 0.93) between the two techniques. Comparison of the patients with and without prosthetic valve stenosis revealed statistically significant differences in mean gradient (42.8 +/- 12.3 versus 13.6 +/- 5.2 mm Hg; p = 0.0001), acceleration time (116 +/- 15 versus 80 +/- 13 ms; p = 0.0001) and valve area by the continuity equation (0.80 +/- 0.16 versus 1.6 +/- 0.31 cm2; p = 0.0001).(ABSTRACT TRUNCATED AT 250 WORDS)

Doppler color flow mapping in the evaluation of prosthetic mitral and aortic valve function

Doppler color flow mapping and color-guided conventional Doppler studies were performed on 119 patients with 126 prosthetic valves (mitral alone in 60, aortic alone in 52 and both mitral and aortic in 7 patients) within 2 weeks of the catheterization study or surgery, or both. The mean pressure gradients derived by color-guided continuous wave Doppler ultrasound correlated well with those obtained at catheterization for both the tissue and mechanical mitral and aortic prostheses (r = 0.85 to 0.87). For the effective prosthetic orifice areas, better correlation with catheterization results were obtained with the tissue mitral (r = 0.94) and tissue aortic (r = 0.87) prostheses than with the mechanical mitral (r = 0.79) and mechanical aortic (r = 0.76) prostheses. The maximal width of the color flow signals at their origin from the tissue mitral prostheses also correlated well with the effective prosthetic orifice area at catheterization (r = 0.81). Doppler color flow mapping identified prosthetic valvular regurgitation with a sensitivity and specificity of 89% and 100%, respectively, for the mitral and 92% and 83% for the aortic prostheses. There was complete agreement between the Doppler color flow mapping and angiographic grading of the severity of prosthetic valvular regurgitation in 90% of mitral and 73.5% of the aortic regurgitant prostheses with under- or overestimation by greater than 1 grade in only two cases. Valvular and paravalvular regurgitation was correctly categorized by Doppler color flow mapping in relation to the surgical findings in 94% of the mitral and 80.5% of the aortic prostheses.

Experimental fluid dynamics of aortic stenosis in a model of the human aorta

Aortic stenosis has been modelled in an in vitro, pulsatile mock circulatory system (MCS) using a porcine valvular prosthesis, and studied with a laser Doppler anemometer (LDA). The MCS incorporated an acrylic model of the human aorta made from a cadaveric casting in situ. A Carpentier-Edwards aortic valve prosthesis was placed in the MCS after being rendered stenotic by suturing of the valve cusps. Flow velocity profiles across the lumen of the aorta in the presence of aortic stenosis were determined using LDA at two preselected sites in the ascending aorta, and at one preselected site in the brachiocephalic artery. Results indicate that a strong systolic jet bordered by transient vortices with intensely reversed flows is produced distal to severely stenotic aortic valves, becoming less intense with a lesser degree of stenosis. Peak fluid velocities in the systolic jet were determined by LDA at distances of 2.6 and 5.6 cm from the valve inlet for a mean flow rate of 5.2 l min-1. Peak systolic pressure gradients and peak turbulent axial stresses were also determined and found to increase dramatically with stenosis. Furthermore, increasing degrees of stenosis also resulted in more severely disturbed flows in the brachiocephalic artery. Peak fluid velocities and their associated turbulent axial stresses in the systolic jets produced by aortic valvular stenosis are remarkably sensitive to even small changes in the calculated valve orifice areas, and can therefore be very useful in assessing the severity and progression of valvular disease. In addition, increasing degrees of aortic stenosis cause more turbulence to be transported into the brachiocephalic artery.

The Gorlin formula validated against directly observed orifice area in porcine mitral bioprostheses

To assess the effect of fluid flow on orifice area and to test the Gorlin formula, six Carpentier-Edwards mitral valve prostheses were studied in a positive displacement pulse duplicator at 20 different rate-stroke volume combinations. Peak transvalvular velocity (V max) was measured by continuous wave Doppler ultrasound, and orifice area was determined from hard copy of video images. Orifice area was directly related to mean flow (Q), although cusp opening behavior was asymmetric and complex and varied among the individual valves. There was a strong correlation between measured orifice area (OA) and the modified Gorlin relation, Q/V max (r = 0.88; p less than 0.00001) given by the regression formula OA = 0.18 x Q/V max - 0.15. There was also a good correlation between measured orifice area and the conventional Gorlin relation, Q/root mean pressure drop. The derived empiric Gorlin constant did not vary significantly with flow.

Use of the valvular resistance in the separation of normal and stenotic Hancock mitral valves

Recent data suggests that the pressure-flow relationship for normal bioprosthetic mitral valves is linear. If this is correct, the valve resistance may provide a better indicator of normal mitral function than the Gorlin valve area. We compared the Gorlin valve area to the valve resistance (calculated as flow/pressure) in order to determine which better separated normal and stenotic Hancock mitral valves. Measurements were made using left atrial and left ventricular catheters in 42 patients undergoing Hancock mitral valve replacement. Patients were studied during pacing and isoproterenol infusion for a total of 141 measurements. Stenotic Hancock mitral valve hemodynamics were obtained at cardiac catheterization from eight patients who were studied at rest and during atrial pacing and from an additional eight patients culled from the literature (a total of 23 stenotic measurements). The Gorlin valve area ranged from 1.1 to 4.4 cm2 for the normally functioning Hancock valves and from 0.4 to 1.54 cm2 for the stenotic valves. Six measurements in patients with confirmed stenotic valves yielded Gorlin areas larger than the lowest area found in the normal valves and no value of the Gorlin valve area correctly classified all of the normal and the stenotic valves.(ABSTRACT TRUNCATED AT 250 WORDS)

Inadequacy of the Gorlin formula for predicting prosthetic valve area

A total of 135 patients with normally functioning prosthetic aortic valves who were catheterized 6 months after placement of Hancock, modified Hancock or Bjork-Shiley prostheses were studied to determine the magnitude of error in Gorlin formula estimates of prosthetic aortic valve area. All patients were male, selected from 13 participating hospitals and routinely followed after valve replacement for 5 years. Hemodynamically determined Gorlin valve areas were compared with independently verified actual valve areas. Actual Hancock areas were measured from videotapes of valves exercised in a pulse duplicator flow model. Actual Bjork-Shiley areas were calculated directly from the valves' inner ring radius. Gorlin valve areas correlated poorly with actual valve areas (r = 0.39). The mean Gorlin formula error was 0.36 cm2 (standard deviation = 0.32). Gorlin areas overestimated actual areas by greater than 0.25 cm2 in 43 patients (32%) and underestimated actual areas by greater than 0.25 cm2 in 29 (21%). It was concluded that the Gorlin formula inaccurately predicts prosthetic valve area in the aortic position. Overreliance on this formula in assessing aortic stenosis could lead to errant clinical decisions.

Six month postoperative hemodynamics of the Hancock heterograft and the Björk-Shiley prosthesis: results of a Veterans Administration cooperative prospective randomized trial

In a Veterans Administration Cooperative Study involving 13 medical centers, 575 patients undergoing single valve replacement were prospectively randomized to receive either the standard Björk-Shiley prosthesis or the Hancock porcine heterograft (with a modified orifice for sizes 23 and smaller). The hemodynamic data in the 268 patients who underwent cardiac catheterization an average of 6 months (range 3 to 12) postoperatively are reported. Statistical analyses were performed on valve sizes 23, 25 and 27 in the aortic position, and 29, 31 and 33 in the mitral position. A wide variation was observed in mean pressure gradient and calculated orifice area in both valve types within all sizes in both the aortic and the mitral positions. In the aortic position, the Björk-Shiley prosthesis tended to have a lower pressure gradient and larger calculated orifice area than the Hancock heterograft, but the differences in gradient between the two valve types were significant only in the larger-sized valves. The difference in calculated area between the two valve types was not significant within each valve size. In the mitral position, there were no differences in gradient and calculated orifice area between the two types of prostheses. The postoperative cardiac index, regurgitant volume, pulmonary artery systolic and mean pressures, left ventricular end-diastolic pressure, left ventricular ejection fraction and left ventricular end-diastolic volume index did not differ in patients receiving the Björk-Shiley prosthesis from values in patients receiving the Hancock heterograft. Hence, the overall hemodynamic performance of both types of valves is remarkably similar. The choice between these two prostheses should, therefore, be governed not by the hemodynamic performance, but by other factors such as valve durability, risk of anticoagulation and incidence of valve-related complications.

The Ross operation: the autologous pulmonary valve in the aortic position

Aortic valve replacement (AVR) with a pulmonary valve autograft (PVA) was first reported by Donald N. Ross (DNR) in 1967. The expectation of this procedure was to avoid degenerative changes seen in other biological tissue valves such as calcification, attenuation, and rupture of the leaflets. Recent reports by the original investigator's group have confirmed the lack of degenerative changes in PVA. To corroborate their conclusions, the fate of 12 patients undergoing AVR with PVA by one of us (LGL) has been ascertained. From March 1969 to June 1971, 12 patients underwent AVR with PVA. The right ventricular outflow tract (RVOT) was reconstructed with an aortic homograft valved conduit. The mean age was 42.7 years (range 21 to 52 years). The mean follow-up for 11 hospital survivors is 12.4 years. Three PVA have been replaced; one following infective endocarditis at 13 years, and two at 15 and 73 months due to technical malalignment. There was no evidence of PVA degeneration during histological examination of these explanted PVAs. Six patients are alive and retain the original PVA at 12 years (55%). This analysis corroborates the conclusions of the DNR report and strongly suggests an immunological mechanism in the process of calcification of other biological tissue valves. The Ross operation is advocated for AVR in young patients as valve durability is of paramount importance especially in this group.

Advances in the hemodynamic assessment of stenotic cardiac valves

In 1951 Gorlin and Gorlin (Am Heart J 1951;41:1-29) published their formula for calculating the area of a stenotic cardiac valve from hemodynamic data. The important concept implicit in this formula is that the hemodynamic evaluation of a stenotic valve requires that the pressure gradient across that valve be examined in light of the cardiac output passing through the orifice. The concept asserts that if an accurately obtained pressure gradient can be related to an accurate cardiac output by an accurate formula, valve area can be determined. However, recent studies have demonstrated flaws in current practices for obtaining transvalvular gradients and cardiac outputs. Further, new data are available regarding the validation and possible changes in the Gorlin formula, validation and changes that the Gorlins noted might be necessary to make. These new data concerning the three basic requirements of an accurate valve area determination are the subject of this review.

When should Doppler-determined valve area be better than the Gorlin formula?: Variation in hydraulic constants in low flow states

In low flow states, underestimation errors occur when the Gorlin formula is used to calculate valve area. A model of valvular stenosis designed to examine changes in the hydraulic discharge coefficient (Cd) and coefficient of orifice contraction (Cc) may explain these errors. Unsteady flow was examined in a pulsatile pump model and in a dog model. Valve areas were calculated from pressure and flow data using: a modified form of the Gorlin formula (assuming constant values for Cd and Cc) and a corrected formula (with values of Cd and Cc obtained from steady state data). Valve area was also calculated using the continuity equation with velocity and flow data (constant Cc). Flow velocities were measured using a newly designed ultrasound Doppler catheter capable of resolving flow velocities of up to 5.5 m/s. Both the corrected formula and continuity equation were highly predictive of actual valve area (r = 0.99, slope or M = 0.96 and r = 0.99, M = 1.06, respectively). The modified Gorlin equation was less accurate and tended to underestimate valve areas (r = 0.87, M = 0.83). This underestimation was most notable at low rates of flow (Gorlin: r = 0.94, M = 0.53; continuity: r = 0.93, M = 0.81 and r = 0.94, M = 0.89, respectively) more accurately than the modified Gorlin formula (r = 0.69, M = 0.49). In patients with low cardiac output, hemodynamic formulas, such as the Gorlin formula, which assume a constant value for the hydraulic discharge coefficient (Cd), may be less accurate than formulas using either a corrected value of Cd or Doppler-determined flow velocity and mean systolic flow.

Valve replacement in narrow aortic roots: serial hemodynamics and long-term clinical outcome

No long-term data are available that correlate clinical outcome with serial hemodynamic studies for small-diameter (17-mm or 19-mm) aortic prostheses implanted without enlargement of the annulus. After insertion of these valves without annuloplasty, 52 patients underwent resting catheterization and were followed up at the Surgery Clinic of the National Heart, Lung, and Blood Institute for 295 patient-years (mean, 5.7 years per patient). At similar flow rates, peak systolic gradients across 17-mm Björk-Shiley aortic prostheses (N = 6) tended to exceed those of the 19-mm Björk-Shiley model (N = 38); these gradients averaged 30 +/- 6 mm Hg (mean +/- standard error of the mean) and 20 +/- 2 mm Hg, respectively (p = .053). Those patients with 19-mm Hancock (N = 4) and St. Jude Medical valves (N = 4) were studied, and the lowest prosthetic gradients were found with the St. Jude Medical prosthesis (mean, 3 +/- 2 mm Hg). Aortic gradient was independent of flow for 17-mm but not for 19-mm Björk-Shiley valves. There was no difference in calculated effective orifice area with respect to valve size. Effective orifice area and prosthetic gradients were stable during intervals of 2 to 12 years in 10 patients who underwent additional catheterizations. No association was found between prosthetic gradients, flows, or calculated orifice areas and early or late functional class. Actuarial survival was 86 +/- 5% at 5 years, 83 +/- 5% at 8 years, 71 +/- 9% at 10 years, and 60 +/- 12% at 12 years of complete follow-up. It is concluded that small aortic prostheses provide acceptable palliation for long periods and that resting hemodynamic studies have a limited predictive value for long-term prognosis.

Hemodynamic differentiation of pathologic and physiologic stenosis in mitral porcine bioprostheses

Porcine bioprostheses are physiologically stenotic valves. Degenerative calcification leading to pathologic stenosis is an increasingly recognized serious late complication of mitral valve replacement with a porcine bioprosthesis. Hemodynamic differentiation of pathologic from physiologic stenosis is important for identification of porcine bioprosthetic valve dysfunction. In 42 patients with a normal Hancock porcine bioprosthesis (standard model, sizes 27 to 33 mm), mean diastolic flow (65 to 461 ml/s), mean gradient (2.0 to 13.4 mm Hg) and effective orifice area (1.1 to 4.4 cm2) were determined at rest, during epicardial pacing (90, 110 and 130/min) and with isoproterenol infusion. A statistically significant increase in mean gradient occurred with increases in flow and decreases in valve size (p less than 0.05). Effective orifice area increased significantly as flow rate increased and as valve size increased (p less than 0.05). These measurements were compared with those in 16 patients with pathologically confirmed porcine bioprosthetic valve stenosis: 8 patients with reoperation (1.1% per patient-year) 3 to 8.5 years after mitral valve replacement and 8 previously reported abnormal cases. Stenotic failure rate was inversely related to valve size (2.1, 1.4, 0.5 and 0% per patient-year for sizes 27 to 33 mm). Stenotic and normal bioprostheses were not accurately differentiated on the basis of a single value for gradient or effective orifice area. A mathematical model that related flow to the square root of the mean gradient allowed complete separation of stenotic from normal prosthetic valve function, after valve size was accounted for and normal confidence limits were established (r = 0.74 to 0.94, sizes 27 to 33, p less than 0.0001). The effective orifice area-flow relation did not provide accurate differentiation of abnormal from normal function. Thus, normal mitral bioprostheses have significant transvalvular gradients whose magnitude depends on flow. Risk of stenotic failure is increased in the smaller valves, which have a larger gradient at implantation. Differentiation of pathologic from physiologic stenosis cannot be made on the basis of a single value for gradient or effective orifice area. Accurate hemodynamic differentiation is achieved by relating mean gradient to mean diastolic flow rate and valve size.

Doppler hemodynamic evaluation of prosthetic (Starr-Edwards and Björk-Shiley) and bioprosthetic (Hancock and Carpentier-Edwards) cardiac valves

One hundred thirty-four patients with prosthetic or bioprosthetic heart valves were investigated with Doppler echocardiography to determine normal values for commonly used prosthetic valves and to test the specificity of abnormal Doppler findings. In 70 patients the aortic valves had been replaced and in 64 the mitral valves had been replaced. Gradients across prostheses in the aortic position were calculated from maximal velocity. Peak calculated aortic transvalvular gradients in normal subjects were 22 +/- 10 mm Hg in 33 Björk-Shiley valves, 23 +/- 10 mm Hg in 27 porcine valves and 29 +/- 13 mm Hg in 6 Starr-Edwards valves. Mild aortic regurgitation was seen in 42% of Björk-Shiley valves, 26% of porcine valves and 2 of 6 Starr-Edwards valves. Mitral valve orifice was calculated by the pressure half-time method. In clinically normal patients with mitral valve prostheses, the effective mitral valve orifice was 2.5 +/- 0.8 cm2 in 35 Björk-Shiley valves, 2.1 +/- 0.7 cm2 in 17 porcine valves, and 2.0 +/- 0.3 cm2 in 10 Starr-Edwards valves. Mitral regurgitation was found in 11% of Björk-Shiley valves, 19% of porcine valves and 30% of Starr-Edwards valves. Repeat studies at 2 weeks to 14 months revealed no difference in 8 aortic and 14 mitral prostheses. Seven aortic and 4 mitral valves functioned abnormally as determined by Doppler, and the abnormal function was confirmed in each at surgery or at cardiac catheterization.(ABSTRACT TRUNCATED AT 250 WORDS)

In vivo hemodynamics of prosthetic St. Jude Medical and Ionescu-Shiley heart valves analyzed by computer

Using a method of our own design, we evaluated intraoperatively the function of prosthetic heart valves. The changing hemodynamics induced by a stress test were assessed by simultaneously measuring the mean transvalvular pressure gradient and the stroke volume. The effective orifice area (EOA) of the valves was determined for each stroke by computer analysis, and this value was compared with the actual orifice area. Data were collected from 19 patients undergoing aortic or mitral valve replacement or both with 17 St. Jude Medical and 12 Ionescu-Shiley valves. The mean pressure gradient increased with tachycardia and an increase in mean left atrial pressure in the mitral position, but decreased with a decrease in cardiac output and peak left ventricular pressure in the aortic position. The St. Jude Medical valve had a smaller mean pressure gradient than the Ionescu-Shiley bioprosthesis. For both valves, the EOA increased with valve size. The St. Jude Medical valve had a greater EOA than the Ionescu-Shiley bioprosthesis, regardless of the valve size (p less than 0.005). However, the performance of prosthetic leaflets was better with the Ionescu-Shiley bioprosthesis than with the St. Jude Medical mechanical valve (p less than 0.001). This method involving computer analysis of each cardiac cycle proved to be useful for evaluating prosthetic heart valve function in the presence of changing hemodynamics.

Thromboembolism and bleeding after mitral valve replacement with porcine valves: influence of thromboembolic risk factors

The risk of postoperative thromboembolism (PTE), anticoagulant related hemorrhage (ARH), and the influence of thromboembolic risk factors ( TERF ) were assessed retrospectively in 206 unselected patients undergoing mitral valve replacement (MVR) with porcine xenobioprotheses ( PXBP ). Other aims were to identify the "high-risk" group with respect to PTE and to assess the effectiveness of long-term anticoagulant therapy (AT) in this subset, as well as to elucidate the most adequate method of AT and ascertain if AT is strictly necessary in patients undergoing MVR with PXBP . Patients were divided in two groups: Group I (N = 115) received long-term AT; there were 22 PTE. Group II (N = 91) with only 8 weeks of AT had 2 PTE (P less than 0.01). ARH was the same in both groups. Actuarially , 71.7% of the patients in group I and 96.3% of the patients in group II were free of PTE at 6 years. Long-term AT proved ineffective in preventing PTE and carried a significant incidence of ARH. ARH surpassed PTE (3.5:1) in patients on short-term AT. Patients without TERF have a low incidence of PTE, and AT is not indicated. The "high-risk" group were patients in postoperative atrial fibrillation and left atrial enlargement. One week heparin therapy and 3 months oral AT is suggested for patients with TERF . PXBP for MVR in patients with TERF is significantly thrombogenic. Early operation is advocated to avoid development of TERF that will affect patient outlook after MVR with PXBP due to the significantly increased risks of PTE and (if placed on AT) ARH.

Isolated mitral valve replacement with the Hancock porcine bioprosthesis in rheumatic heart disease: analysis of 213 operative survivors followed up 4.5 to 8.5 years

An analysis is presented of 236 patients aged greater than or equal to 20 years who underwent isolated mitral valve replacement for rheumatic heart disease with a glutaraldehyde Hancock bioprosthesis from June 1974 through June 1978. Of 213 patients discharged from the hospital, 3 were lost to follow-up study and are excluded from the analysis. The range of follow-up of the surviving patients was 54 to 102 months. There were 17 late deaths, an incidence of 1.3% per patient-year. The actuarial probability of survival of all patients at 102 months, excluding hospital mortality, is 88 +/- 6%. There were 24 thromboembolic events in 22 patients (1.8% per patient-year); none was fatal, and 3 patients were receiving coagulant therapy at the time. The probability of freedom from thromboembolism at 8.5 years is 84 +/- 9%. Primary tissue failure occurred in 17 patients (1.3% per patient-year). Average duration of the explanted valves was 70 months (range 55 to 90). Reoperation was undertaken in the 17 patients 2 days to 63 months (mean 9 months) after the appearance of a new murmur and 2 days to 23 months (average 4 months) after the onset of worsening symptoms. The probability of being free from primary tissue valve failure at 8.5 years of follow-up is 87 +/- 7%. Currently, 14 patients have valve dysfunction on the basis of the appearance of a new murmur 20 to 89 months after operation (average 5.2 years).(ABSTRACT TRUNCATED AT 250 WORDS)

Five-year experience with the Ionescu-Shiley bovine pericardial valve in the aortic position

Between February, 1977, and April, 1982, 168 patients underwent aortic valve replacement (AVR) with an Ionescu-Shiley bovine pericardial valve. Concomitant procedures were performed in 71 patients. There were 12 hospital deaths (7.1%). Among patients having AVR only, there were 5 deaths (5.2%). Assessment included valve durability, incidence of thromboembolism, clinical improvement, and patient survival. There was 100% follow-up. Actuarial freedom from intrinsic valve failure at 5 years was 96.3 +/- 3.6%. Intrinsic valve failure occurred only once, 0.3 episodes per 100 patient-years. Four patients had thromboembolic complications. As for clinical status, 99.3% of surviving patients are in New York Heart Association Functional Class I or II, including 79 patients with valve sizes 17, 19, or 21 mm (56%). Among 13 late deaths, 9 were related to the cardiovascular system. Overall patient survival is 84.9 +/- 4.7%. Among the 92 patients with isolated AVR, 87.8 +/- 5.9% are alive at the 5-year follow-up. If the incidence of valve failure is not altered in years to come, the durability of the Ionescu-Shiley bovine pericardial valve will surpass that of previous bioprostheses.