Left ventricular mechanics of ejecting, postischemic hearts during left ventricular circulatory assistance.

We measured the effects of left ventricular circulatory assistance on ventricular mechanics of ejecting sheep hearts before and after global ischemia. Flows from left atrium to femoral artery ranged between 20 and 100 ml/kg/min during circulatory assistance. In preischemic, ejecting hearts increasing flow through the left ventricular assist device progressively decreased stroke volume, end-diastolic volume, and circumferential systolic wall stress, but only slightly decreased end-systolic volume. In postischemic, ejecting hearts left ventricular assistance progressively and substantially decreased both end-diastolic volume and end-systolic volume; at high flows, end-systolic volume returned to the normal range of preischemic hearts. High flows through the assist device also shifted end-systolic points of pressure-volume loops leftward and increased the stroke work/end-diastolic volume ratio in ejecting postischemic hearts; these observations raise the possibility that left ventricular circulatory assistance acutely improves myocardial contractility of postischemic hearts.

Repair of left ventricular aneurysm. Changes in ventricular mechanics, hemodynamics, and oxygen consumption.

Anteroapical left ventricular aneurysms were produced in 23 sheep by coronary arterial ligation. Plication of the aneurysm does not change stroke volume or cardiac output and does not significantly change left ventricular oxygen consumption from the preoperative value of 5.1 +/- 2.6 ml/100 gm per minute. Plication, however, does increase left ventricular end-systolic elastance from 3.2 +/- 0.9 to 4.4 +/- 1.5 mm Hg/mm (p = 0.005). In nine of these sheep the midsagittal plane of the left ventricle was imaged by means of an array of sonomicrometry crystals before and after plication of the aneurysm. Regional wall stresses at end-systole and end-diastole and changes in diastolic function were calculated for anterior and posterior ventricular walls in the border zone adjacent to the aneurysm and in more basilar myocardium remote from the infarct. Plication significantly reduced end-systolic wall stresses and systolic stress integrals in the posterior border zone and remote myocardium, but it did not significantly change anterior wall systolic stresses or stress integrals. Plication also decreased diastolic stretching of border zone myocardium. Plication of anteroapical left ventricular aneurysm produced a shorter, more spherical ventricle and removed the dyskinetic segments but altered deformation (strain) in both circumferential and longitudinal directions. The changes in ventricular wall geometry and deformation provide an explanation for the increased ventricular end-systolic elastance and unchanged stroke volume observed after aneurysm plication.

Myocardial oxygen utilization after reversible global ischemia.

We tested in 20 sheep the hypothesis that oxygen consumption increases after reversible, global myocardial ischemia. Left ventricular oxygen consumption before and after 25 minutes of warm (37 degrees C) global ischemia was linearly related to a function (integral) of left ventricular circumferential systolic wall stress, altered by changing afterload. The relation is expressed in the two regression equations: LVO2 (preischemic) = 1.06.SSI + 16.8 (n = 129; r = 0.79); LVO2 (postischemic) = 4.35.SSI + 5.6 (n = 89; r = 0.65). The fourfold increase in slope (4.35 versus 1.06) indicates (p = 0.0001) a massive increase of oxygen consumption in postischemic, globally "stunned" myocardium. The inferences are that globally stunned myocardium causes severe impairment of oxygen utilization efficiency, and increased vulnerability to further ischemia if coronary vessels are diseased.

The stretched ventricle. Myocardial creep and contractile dysfunction after acute nonischemic ventricular distention.

The hypothesis that nonischemic distention of the arrested, flaccid ventricle causes myocardial creep and reduces ventricular contractile force was tested in 16 sheep. Left ventricular volume was calculated from ultrasonic dimension transducers spanning left ventricular major and minor axes and left ventricular wall thickness. Changes in left ventricular volume were plotted against left ventricular pressure, with and without temporary occlusion of both venae cavae before and after nonischemic distention of the continuously perfused, flaccid nonbeating left ventricle arrested with oxygenated, normothermic blood-potassium perfusate. During 12 minutes of cardiac arrest, an apical balloon progressively distended the left ventricle to a peak pressure of 40 mm Hg in 11 sheep using a protocol designed to prevent subendocardial ischemia or mechanical injury. Coronary sinus lactate measurements and myocardial distribution of microspheres confirmed the absence of ischemia in 16 animals. In five control sheep the balloon was inserted but not inflated. Left ventricular volume at zero pressure increased from 5.9 +/- 3.5 to 9.5 +/- 4.4 ml (p < 0.05) after balloon inflation and did not change in the control animals. After maximum distention of the balloon, static left ventricular volumes at identical pressures were significantly greater. After passive distention, the slope of the end-systolic pressure-volume relationship, a measure of contractility, decreased significantly (p < 0.05) from 7.1 +/- 2.8 to 3.5 +/- 1.8 mm Hg/ml and did not change in the control group. Passive distention ("stretching") of the nonischemic flaccid left ventricle thus causes myocardial creep and reduces ventricular contractility.

Dynamic three-dimensional imaging of the mitral valve and left ventricle by rapid sonomicrometry array localization.

OBJECTIVES: The first objective was to develop a quantitative method for tracking the three-dimensional geometry of the mitral valve. The second was to determine the complex interrelationships of various components of the mitral valve in vivo. METHODS AND RESULTS: Sixteen sonomicrometry transducers were placed around the mitral vale anulus, at the tips and bases of both papillary muscles, at the ventricular apex, across the ventricular epicardial short axis, and on the anterior chest wall before and during cardiopulmonary bypass in eight anesthetized sheep. Animals were studied later on 17 occasions. Reproducibility of derived chord lengths and three-dimensional coordinates from sonomicrometry array localization, longevity of transducer signals, and the dynamics of the mitral valve and left ventricle were studied. Reproducibility of distance measurements averages 1.6%; Procrustes analysis of three-dimensional arrays of coordinate locations predicts an average error of 2.2 mm. Duration of serial sonomicrometry array localization signals ranges between 60 and 151 days (mean 114 days). Sonomicrometry array localization demonstrates the saddle-shaped mitral anulus, its minimal orifice area immediately before end-diastole, and uneven, apical descent during systole. Papillary muscles shorten only 3.0 to 3.5 mm. Sonomicrometry array localization demonstrates nonuniform torsion of papillary muscle transducers around a longitudinal axis and shows rotation of papillary muscular bases toward each other during systole. CONCLUSION: Tagging of ventricular structures in experimental animals by sonomicrometry array localization images is highly reproducible and suitable for serial observations. In sheep the method provides unique, quantitative information regarding the interrelationship of mitral valvular and left ventricular structures throughout the cardiac cycle.

Pathogenesis of acute ischemic mitral regurgitation in three dimensions.

Changes in the geometric and intravalvular relationships between subunits of the ovine mitral valve were measured before and after acute posterior wall myocardial infarction in three dimensions by means of sonomicrometry array localization. In 13 sheep, nine sonomicrometer transducers were attached around the mitral anulus and to the tip and base of each papillary muscle. Five additional transducers were placed on the epicardium. Snares were placed around three branches of the circumflex coronary artery. One to 2 weeks later, echocardiograms, dimension measurements, and left ventricular pressures were obtained before and after the coronary arteries were occluded. Data were obtained from seven sheep. Coronary occlusion infarcted 32% of the posterior left ventricle and produced 2 to 3+ mitral regurgitation by Doppler color flow mapping. Multidimensional scaling of dimension measurements obtained from sonomicrometry transducers produced three-dimensional spatial coordinates of each transducer location throughout the cardiac cycle before and after infarction and onset of mitral regurgitation. After posterior infarction, the mitral anulus enlarges asymmetrically along the posterior anulus, and the tip of the posterior papillary muscle moves 1.5 +/- 0.3 mm closer to the posterior commissure at end-systole. The posterior papillary muscle also elongates 1.9 +/- 0.3 mm at end-systole. The left ventricle enlarges asymmetrically and ventricular torsion along the long axis changes. The development of postinfarction mitral regurgitation appears to be the consequence of multiple small changes in ventricular shape and contractile deformation and in the spatial relationship of mitral valvular subunits.

Changes in left ventricular systolic wall stress during biventricular circulatory assistance.

Extracorporeal membrane oxygenation (ECMO) reduces the systolic stress integral (SSI) in the normal left ventricle. We tested the hypothesis that the SSI does not decrease in poorly contracting, dilated, ejecting hearts during ECMO. In 14 sheep, four pairs of ultrasonic crystals measured changes in left ventricular (LV) wall thickness and three LV diameters. Volume calculations were validated by balloon distention of the ventricles after death (slope = 0.85; r = 0.85). SSI was measured during ECMO flows of 20 to 100 ml/kg/min in both normal and dilated, poorly contracting hearts produced by 30 minutes of warm ischemia. After warm ischemia, end-systolic elastance, an index of contractility, decreased from 8.3 +/- 0.6 mm Hg/ml to 2.9 +/- 0.4 mm Hg/ml (p = 0.001) and peak systolic pressure decreased from 47.4 +/- 0.7 mm Hg to 37.5 +/- 0.08 mm Hg (p = 0.01). In normal hearts, as ECMO flow increased, SSI decreased from 10.5 +/- 2.2 mm Hg.sec to 7.7 +/- 0.8 mm Hg.sec at 60 ml/kg/min (p = 0.001). However, in postischemic hearts, SSI progressively increased from 6.6 +/- 0.3 mm Hg.sec before ECMO to 12.4 +/- 1.8 mm Hg.sec at ECMO = 100 ml/kg/min. These studies indicate that the initial effect of ECMO on the poorly contracting, dilated heart increases LV wall stress and that the increase in stress is proportional to ECMO flow. The increase in stress is primarily due to an increase in afterload, which more than offsets decreases in systolic and diastolic volumes.

Large animal model of left ventricular aneurysm.

In 28 Dorsett sheep, ligation of the distal homonymous (equivalent to human left anterior descending) and second diagonal coronary arteries produced a constant transmural infarct of 22.9% +/- 2.5% (mean +/- standard deviation) of the left ventricular mass. Serial left ventriculograms showed that within four hours the infarct segment expands, wall thickness decreases, and aneurysmal dilatation occurs and progresses over the next 60 days in all sheep. Epicardial ventricular point references indicated that adjacent noninfarcted myocardium participates in the formation of the aneurysm. Anatomy of the coronary vasculature was studied in 22 excised sheep hearts. In sheep, coronary arterial anatomy is remarkably constant. The left coronary artery provides all of the blood supply to the left ventricle and septum and only a small rim of both the anterior and posterior right ventricles. Cardiac veins from the left ventricle drain into the coronary sinus, which also receives the left azygos vein. Right ventricular veins drain separately. The essentially separate coronary circulations to the two ventricles, the paucity of coronary collateral circulation, and the consistent evolution of left ventricular infarcts into aneurysms are important advantages of the ovine model for both metabolic and ventricular mechanical studies of acute myocardial infarction and left ventricular aneurysm.

Large animal model of ischemic mitral regurgitation.

A large animal model of ischemic mitral regurgitation (MR) that resembles the multiple presentations of the human disease was developed in sheep. In 76 sheep hearts, the anatomy of the coronary arterial circulation was determined by observation and polymer casts. Two variations, types A and B, which differed by the vessel that supplied the left ventricular apex, were found. In all hearts, the circumflex coronary artery has three marginal branches and terminates in the posterior descending coronary artery. The amount and location of left ventricular (LV) mass supplied by each marginal circumflex branch was determined by dye injection and planimetry. In type A hearts, ligation of the first and second marginal branches infarcts 23% +/- 3.0% of the LV mass, does not infarct either papillary muscle, significantly (p < 0.001) increases LV cavity size 48% at the high papillary muscle level by 8 weeks, and does not cause MR. Ligation of the second and third marginal branches infarcts 21.4% +/- 4.0% of the LV mass, includes the posterior papillary muscle, significantly increases (p < 0.001) LV cavity size 75%, and causes severe MR by 8 weeks. Ligation of the second and third marginal branches and the posterior descending coronary artery infarcts 35% to 40% of the LV mass, increases LV cavity size 39% within 1 hour, and causes massive MR. After moderate (21% to 23%) LV infarction, development of ischemic MR requires both LV dilatation and posterior papillary muscle infarction; neither condition alone produces MR. Large posterior wall infarctions (35% to 40%) that include the posterior papillary muscle produce immediate, severe MR.(ABSTRACT TRUNCATED AT 250 WORDS)

A low-cost fiber-optic strain gage system for biological applications.

A new low-cost strain measurement system has been developed for the mechanical testing of biological soft tissues. The technique creates four spots of light on a tissue sample surface by piercing the tissue sample with two pairs of small light-conducting optical fibers (one pair for each axis of a biaxial stretch), terminated by high intensity infrared emitters. A large-area photodiode, located below the tissue sample, detects the light emitted from the two pairs of light-spots. Analog and digital circuitry analyze the current signal from the photodiode to determine the position of a light-spot in real time. Each infrared emitter is sequentially cycled "on" at a rate of 3 kHz and the resulting photodiode current signal, after being converted to a voltage signal, is held by an integrated circuit sample and hold amplifier. Analog differencing of pairs of light-spot voltage signals provides a final output proportional to the separation between coaxial light-spots.

Use of sonomicrometry and multidimensional scaling to determine the three-dimensional coordinates of multiple cardiac locations: feasibility and initial implementation.

We describe a new method which uses sonomicrometry and the statistical technique of multidimensional scaling (MDS) to measure the three-dimensional (3-D) coordinates of multiple cardiac locations. We refer to this new method as sonomicrometry array localization (SAL). The new method differs from standard sonomicrometry in that each piezoelectric transducer element is used as both transmitter and receiver and the set of intertransducer element distances is measured. MDS calculates the 3-D coordinates of each sonomicrometry transducer element from the set of intertransducer element distances. The feasibility of this new method was tested with mathematical simulations which demonstrated the ability of MDS to compensate for signal error and missing intertransducer element distances. We describe the design elements of a modified digitally controlled sonomicrometer in which a single transducer element can sequentially broadcast to as many as eight receiver elements. That design is used to validate SAL in a water bath and in ex vivo and living hearts. Correlation with caliper measurement in the water bath (y int. = 3.91 +/- 3.36 mm, slope = 1.04 +/- 0.05, r2 = 0.969 +/- 0.027) and with radiography in ex vivo (y int. = -0.87 +/- 0.92 mm, slope = 0.97 +/- 0.02, r2 = 0.960 +/- 0.023) and in vivo hearts (y int. = 2.98 +/- 2.59 mm, slope = 1.01 +/- 0.06, r2 = 0.953 +/- 0.031) was excellent. Sonomicrometry array localization is able to accurately measure the 3-D coordinates of multiple cardiac locations. It can potentially measure myocardial deformation and remodeling after ischemic or valvular injury.

Strain energy descriptions of biological swelling. I: Single fluid compartment models.

Strain energy functions are derived from biphasic soft tissue models in order to describe large-deformation, large-swelling, elastic behavior of nonlinear materials. The resulting analysis leads to calculations of stress-extension relations and tissue fluid pressure. Also explored are the elastic stability of the biphasic tissue models and the manner in which tissue pressure is altered by material deformation.

Strain energy descriptions of biological swelling. II: Multiple fluid compartment models.

A series of multicompartmental, biphasic elastic tissue models is developed. In its most general form, the models consist of multiple tubular networks, each with an internal spring network. In addition, another spring network occupies the extratubular compartment. Strain energy functions are derived for the models, as well as expressions for the fluid pressures in each compartment arising from volume expansion or swelling. Calculations also show that the distribution of fluid among compartments is a significant determinant of tissue elasticity.

Do cardiac aneurysms blow out?

The possibility is suggested that cardiac aneurysms are formed when an infarcted region of the ventricular wall becomes elastically unstable and "blows out". The consequence of such a blowout could be a large saccular aneurysm or even cardiac rupture. We use a nonlinear stress-strain relation capable of describing both the passive and active myocardial wall to examine this possibility in terms of large-deformation membrane theory. Ventricular infarcts made of a material having physical properties like rubber would be expected to blow out, but those made of passive myocardium would not.

An analysis of myocardial infarction. The effect of regional changes in contractility.

In a preceding paper, we employed an initially spherical, modified membrane model of the infarcted ventricle to investigate the relation between ventricular function and both infarct size and infarct stiffness. In the present paper, we have applied the same model to a set of different questions, namely, the consequences of enhanced or depressed inotropic state within the noninfarcted myocardium. When infarcted ventricles containing up to 41% infarction are examined, stroke volume appears to be relatively insensitive to increases in inotropic state. However, stroke volume falls rapidly when inotropic state is depressed below 80% of normal. For the case of a ventricle with a large, weakly contracting segment which is not totally infarcted, stroke volume is impaired only when the contractility of the weak region is diminished below 50% of normal. Finally, the stress concentration around a region of infarction appears to be dependent more strongly on the inotropic state of the noninfarcted tissue than on the infarct size.

Ventricular interaction is described by three coupling coefficients.

Previous studies of ventricular interaction have quantified interaction by making small pressure or volume changes in one ventricle and measuring the resulting pressure or volume changes in the opposite ventricle. The ratios between the pressure and volume changes in opposite ventricles have been used as coupling coefficients or measures of ventricular interaction. This method of calculating coupling coefficients implicitly uses mathematical relationships that have useful features not generally appreciated. Starting from the definition of coupling coefficients we show that, without making any assumptions about ventricular interaction, all 24 possible coupling coefficients can be derived from a smaller set of four coupling coefficients. Furthermore, by making the single assumption that the ventricles behave elastically, we show that the set of four coefficients can be reduced to a set of three. Thus only three indexes are required to describe interaction, but these may vary with changes in ventricular volumes and pressures around which the indexes are measured. Furthermore, when comparisons between experimental studies are made, it is necessary to normalize the indexes with respect to ventricular volume.