Prosthetic heart valve

Abstract: A bileaflet heart valve incorporates a pivot arrangement that minimizes resistance to downstream blood flow in the open position yet has prompt response and minimal regurgitation upon flow reversal. A valve body, having an axially curved preferably toroidal entrance that smoothly joins a generally cylindrical body of extended axial length, provides excellent fluid flow when combined with leaflets that can assume orientations aligned with the downstream flow of blood. A pyrocarbon valve body receives a suture ring that permits the tissue annulus to directly contact its exterior surface, e.g. in a concave toroidal surface region for an aortic valve. Identical flat leaflets can assume a parallel orientation in the fully open position or can assume other low energy positions. Flat ears extend laterally from the leaflets and interengage with cavities of unique design having upstream (57) and downstream (59) lobes separated by an intermediate throat (65) portion defined by inward and outward fulcrums. The downstream lobes locate leaflets in the parallel open orientation and can optionally cause prerotation. As soon as reverse flow begins, upstream displacement of the leaflets causes the ears to contact straight camming surfaces (67) located upstream of the outward fulcrums which, in combination with the fulcrums and a downwardly directed, concave surface at the upstream end of the upstream lobe, positively guide each leaflet through efficient closing which ends in substantially rotational movement.

Description: The present invention relates to mechanical heart valve prostheses and, in particular, to improved prosthetic heart valves having valve members or occluders which both pivot and translate in moving between their open and closed positions. A wide variety of heart valve prostheses have been developed which operate hemodynamically, in conjunction with the pumping action of the heart, to take the place of a defective natural valve. These valves have generally been designed to function with valve members in the form of a single occluder, a pair of occluders or leaflets or even three or more occluders; such occluders pivot along eccentric axes (or both pivot and translate) to open and close a central blood flow passageway through a generally annular valve body within which the occluders are usually appropriately supported. U.S. Patent No. 4,689,046 (August 25, 1987) discloses a bileaflet heart valve having a pair of flat leaflets with ears of generally trapezoidal configuration extending from the flat lateral surfaces thereof. The ears have flat end faces and are received in diametrically opposed recesses in the valve body having facing flat end surfaces; the recesses are shaped so that the ears are rockingly engaged therein by tapered recess guide wall surfaces of arcuate configuration. U.S. Patent No. 5,137,532 (August 11, 1992) discloses bileaflet heart valves having pivot arrangements which allow the leaflets to assume an orientation substantially parallel to the centerline through the valve in their open position in a valve body which is elongated in axial length relative to bileaflet valves of earlier design wherein designers generally attempted to minimize the length of the blood flow path through the valve body, because the valve was felt to be confining. In one embodiment, camming surfaces provided on the leaflets engage appropriately located projections extending radially inward from the valve body sidewall, and the upstream displacement of the leaflets which occurs upon the reversal of blood flow causes prompt pivoting of the leaflets toward the closed positions. U.S. Patent No. 5,314,467 (May 24, 1994) discloses a bileaflet heart valve wherein leaflets of composite curvature are supported by laterally extending elongated ears which are received in recesses formed in diametrically opposed flat wall sections of the interior surface of a valve body that is formed with a flared outflow seat region against which the leaflet downstream edges seat. The recesses each have a serpentine guide wall along the upstream edge thereof. The combination of it and a second downstream wall creates a sequence of rotational and then translational movement of the leaflets as they pivot from the open position to the closed position. More recently, attention has also begun to be given to trileaflet valves, and the study of blood flow through such multiple leaflet valves has convinced many investigators that it is very important that emphasis should be given to achieving designs with minimum turbulence and minimum pressure drop. It was generally believed that the shorter the axial length of a valve body was, the less would be the resistance to blood flow through the critical region of the valve, because the valve body was of course the region of greatest constriction. Many patented valve designs also concentrated on the shape and the placement of the occluders to minimize pressure drop and turbulence. A number of U.S. patents, such as Nos. 4,363,142, 4,328,592, 5,178,632 and 5,171,623 illustrate heart valves having relatively short valve bodies of generally circular cross-section, some of which have rounded or radially outwardly flared upstream and downstream ends. U.S. Patent No. 4,775,378 shows a heart valve having a single occluder with a shallow S-shaped curvature that is alleged to promote the formation of a stable closed vortex on the suction side of the occluder; it is employed in combination with a valve body having a circular cross-section passageway that is continuously and increasingly constricted, i.e. its diameter decreasing, in the downstream direction. U.S. Patent No. 4,846,830 discloses a bileaflet valve having a similar valve body wherein a pair of curved leaflets are employed which are arranged to create a venturi tube nozzle in the direction of downstream flow which is alleged to avoid vortex formation. U.S. Patent No. 4,995,881 shows a valve having a similarly sloping entrance in combination with a pair of leaflets that are curved in the downstream direction so as to define a nozzle-shaped passage centrally between the two leaflets when they are in their open position orientation. US Patent No. 4,363,142 discloses a bileaflet heart valve having a pair of curved occluders having diametrically opposed ears that are received in pockets formed in the side walls of the valve body. The pivoting motion is directed by sliding abutment against nodes of convex shape that protrude from opposite locations in the valve body side wall in some embodiments. Both the upstream and the downstream ends of the valve body are provided with a slight rounded outward flare. The more that such mechanical prosthetic valves have been studied, the more that investigators have concluded that the ideal prosthetic valve simply does not yet exist. From a materials standpoint, pyrolytic carbon has been presently felt to lie in preventing excess turbulence, high shear stresses and local regions of stasis. Blood is a very delicate tissue, and even minor abuses caused by turbulence and high shear stress can cause either thrombosis or emboli generation at local regions of stagnation. Therefore, it is felt that future improvement in the characteristic of thromboresistance in mechanical valves will likely be attained through the achievement of smooth, nonturbulent flow and the absence of stasis. The search continues for improved mechanical heart valve prostheses that provide passageways through which blood will flow freely and with a minimum of drag in the open position, which will close quickly upon the occurrence of backflow to minimize regurgitation of blood, and which can be efficiently manufactured and assembled. Accordingly, new valve designs incorporating such features have continued to be sought. The present invention provides bileaflet mechanical heart valve prostheses having the aforementioned desirable characteristics wherein leaflets can assume an orientation in the open position where they are parallel to the longitudinal axis of the valve passageway but will still promptly close, with guidance and control of the leaflets being accomplished solely by contact between laterally protruding ears and complementary-shaped cavities in the sidewalls of the valve body in which they are received which have straight camming edges that are angularly located to achieve prompt pivoting, thus easing manufacturing requirements because the most critical tolerances to be maintained are substantially confined to a single region of the valve body. Because turbulence in mechanical heart valves can damage blood and lead to clotting, such sources which exist both at the leading edges of leaflets that are inclined to the direction of blood flow and at the leading edge of the valve body orifice itself should be taken into consideration. When a liquid must pass around a corner, as when entering an orifice, separation occurs, and turbulence and elevated shear stresses are created in such zone of separation. By selecting a valve body of relatively extended axial length, by mounting leaflets therein so that, in their open orientation, the leaflets are individually free to generally follow blood flow and orient themselves so as to be parallel to the direction of downstream blood flow at any instant (to minimize the turbulence associated with the leaflets), and by also contouring the orifice inlet to eliminate that usual zone of separation that would otherwise be present, both head or pressure loss and the tendency for thrombosis generation are concomitantly decreased. The leaflets preferably have rectilinear surfaces that will assume an orientation in alignment with the instantaneous direction of blood flow in the full open position, such as substantially parallel to the centerline through the valve, e.g. about 2° or less therefrom, thereby minimizing resistance to the downstream flow of blood; such rectilinear leaflet surfaces can be flat or cylindrical. The leaflets should be parallel when blood flow is at its highest level; however when the velocity of the downstream blood flow slows near the end of the pumping stroke, they may undergo a prerotation toward their closed orientation from such parallel orientation. More specifically, it has been found that the entrance at the upstream end of the valve body should be essentially a section of a torus having a radius of curvature which is at least about 28% of the radius of the central passageway through the valve body and not greater than about 80%, that the valve body should have an average axial length at least about equal to the central passageway radius, and that the flaring toroidal entrance section should extend circumferentially about the opening but preferably does not extend axially a distance greater than about one-third of the average axial length of the valve body. Preferably the surface is at least about 30% of a quadrant of a torus which at its downstream end is preferably tangent to the remainder of the interior surface, which is preferably generally cylindrical. Because the flow through such a valve body has been found to be a function of the fourth power of its diameter, the diameter of the passageway through such a valve body is maximized by using the thinnest valve body wall that is structurally adequate, in addition having the average axial length of the valve body be equal to at least about the radius of the interior cross-section. The interior diameter is preferably advantageously maximized by allowing the exterior surface of the valve body to interface directly with the raw edge of the tissue annulus from which the natural valve has been excised, and suture rings are preferably employed which permit both mitral valves and aortic valves to be so located that the raw tissue annulus interfaces directly with the pyrocarbon outer surface of the valve body. The mitral valve suture ring may be a fairly straightforward design; however, for a replacement aortic valve, a suture ring is designed to permit the valve to be located above the aortic annulus in a location so that its upstream flared entrance will be slipped into the aortic orifice region so that its outer wall surface, which is concave and toroidal, interfaces directly with the raw edge of the tissue. FIG. 1 is a perspective view of a bileaflet heart valve embodying various features of the present invention, shown with the leaflets in the open position. FIG. 2 is a sectional view taken generally along the line 2-2 of FIG. 1 showing the leaflets in the full open position, and with a suture ring attached to the valve body. FIG. 2A is a sectional view taken generally along the line 2-2 of FIG. 1 showing the leaflets in the full open position, and with an alternative suture ring attached to the valve body. FIG. 3 is a view similar to FIG. 2 showing the leaflets in their prerotation orientation as they would be when the downstream flow of blood slows prior to reversal. FIG. 3A is a fragmentary sectional view taken along the lines 3A-3A of FIG. 3. .FIG. 4 is a view similar to FIG. 2, showing the leaflets in elevation and in their closed position, with the suture ring omitted. FIG. 5 is a plan view looking downward at the valve shown in FIGS. 1 and 2 with the leaflets in the full open position. FIG. 6 is a vertical sectional view through the valve taken generally along the line 6-6 of FIG. 2 with the leaflet in the full open position. FIG. 7' is a perspective view of a leaflet from the valve of FIG. 1. FIG. 8 is a side elevation view, reduced in size, of the leaflet of FIG. 7. FIG. 9 is a front view of the leaflet of FIG. 8. FIG. 10 is a fragmentary sectional view, enlarged in size, taken generally along the line 10-10 of FIGS. 5 and 6 with the sewing ring removed, showing the location of the ear in the cavity in the valve body sidewall when the leaflet is in its full open position. FIGS. 10A through 10D are full sectional views similar to FIG. 10 with the right-hand leaflet omitted and with the left-hand leaflet shown respectively (A) in the prerotation position, (B) at the beginning of closing movement, (C) in an intermediate position during closing movement and (D) in its full closed position. FIGS. 11 and 12 are fragmentary horizontal sectional views taken respectively along the lines 11-11 and 12-12 of FIG. 3, with the leaflets removed. FIG. 13 is a fragmentary sectional view taken generally along the line 13-13 of FIG. 2A. FIG. 14 is a fragmentary sectional view, enlarged in size, illustrating the valve body wall structure. FIG. 15 is a view similar to FIG. 14 showing the aortic sewing ring attached. FIG. 16 is a sectional view similar to FIG. 2 of an alternative embodiment of a bileaflet heart valve embodying various features of the invention shown with the leaflets in the open position and with a suture ring attached that is designed to facilitate mounting of the valve in the aortic position. FIG. 17 is a vertical sectional view taken through the valve and through one of the leaflets along the line 17-17 of FIG. 16. FIGS. 18A through 18D are sectional views similar to FIGS. 10A through 10D with the right-hand leaflet omitted to show the details of the cavities, which details are omitted from each left-hand cavity, and with the section through the leaflet ear showing the left-hand leaflet, respectively, (A) in the fully open position, (B) at the beginning of closing movement, (C) in an intermediate position during closing movement, and (D) in the fully closed position. Illustrated in FIG. 1 is a prosthetic heart valve 11 constructed so as to embody various features of the present invention. Very generally, heart valves having this construction have improved flow characteristics, particularly when the valve is in its fully open position, because the leaflets can align parallel to the valve centerline or can align at slight deviations thereto depending upon instantaneous variations in the blood flow path through the valve, whichever is the low energy orientation. As a result, these orientations minimize the resistance to blood flow and substantially reduce boundary layer separation along major surfaces of the leaflets. The valve design also provides good washing characteristics which guard against the occurrence of stagnation and potential clotting. Importantly, although heart valves of this design exhibit a rapid response to change in the direction of blood, both in respect of opening and closing, the final movement of the closing leaflets is one almost solely of rotation so that there is relatively low wear due to the leaflet rubbing against a fulcrum within the valve body at about the time of complete closing, thus eliminating potential problems which could result from the creation of regions of substantial wear on the leaflet and on the fulcrum by translation movement during the final closing phase when the pressure across the valve is building to the maximum value. Heart valve 11 includes a generally annular valve body 13 which carries a pair of pivoting occluders or leaflets 15 that alternately open and close either to allow the smooth flow of blood in the downstream direction, as indicated by the arrow A in FIG. 2, or to prevent any substantial backflow of blood, i.e. regurgitation. The valve body 13 defines a blood flow passageway in the form of its generally arcuate, mostly cylindrical interior wall surface 17. The valve body 13 has a curved entrance region 19 at its upstream end, which has been found to substantially increase streamlined flow characteristics through the valve with low turbulence and substantially no generation of thrombosis. The details of the curved entrance region 19 which extends axially for a distance not greater than about one-third of the average axial length of the valve body are discussed hereinafter along with the operation of the valve. A pair of diametrically opposed, thickened wall sections 21, as best seen in FIG. 5, protrude inward from an otherwise right circular cylindrical surface, creating what is referred to as a tabulated cylindrical surface as a result of the thickened sections 21 terminating in facing, parallel flat wall surfaces 23 in which pairs of cavities or recesses 25 are formed that function as one-half of the pivot arrangement which controls the opening and closing movements of the leaflets 15. Thus, the interior surface downstream of the curved entrance region 19 is generally rectilinear. The valve body 13 preferably has a scalloped downstream profile so that there are, in effect, a pair of shallow notches 27 formed in the contour of the valve body 13 in the regions just downstream of the thickened wall sections 21. In a bileaflet valve of this type, the side openings provided by these notches 27 are aligned with the central passageway between the leaflets 15 so that, upon reversal of blood flow, backflowing blood laterally enters the valve body through these side openings directing a surge of blood flow into the central passageway region and creating forces which impinge upon the leaflet outflow surfaces, the effect of which is to further enhance prompt pivoting of the eccentrically mounted leaflets toward their closed position orientations. This function is described in greater detail in U.S. Patent No. 5,308,361. The exterior surface of the relatively thin valve body 13 in the region downstream of the flared entrance section 19 is substantially that of a surface of a right circular cylinder except for a slightly thickened central portion wherein a shallow groove 29 is formed between a pair of raised bands 29a. A metal stiffening attachment ring 30 of unique design (FIG. 2) which is formed with a plurality of circumferentially spaced apart inwardly protruding fingers 30a is mated therewith to add stability and rigidity to the valve body. The valve body itself is preferably made of a suitable material, such as pyrocarbon or pyrocarbon-coated graphite, as is well known in this art, which has sufficient resiliency that it can be deformed so as to permit the insertion of the pair of leaflets 15 in their operative locations. The metal ring 30 is also used to support the sewing ring of appropriate design, as broadly known in this art. Detailed examples of sewing or suture rings which can be employed are described in U.S. Patents Nos. 4,535,483 and 5,178,633. The thickened exterior bands 29a are strategically located in the downstream cylindrical section of the valve body spaced from the flared entrance section 19. As explained hereinafter in detail, the shallow groove 29 is located to accommodate the inwardly protruding fingers 30a of the metal ring 30 in either orientation as explained hereinafter. The groove 29, which is of arcuate cross section and constitutes the narrowest diameter on the exterior surface is located so that it is completely downstream of the fulcrums which are formed in recesses 25. This arrangement permits the suture rings to be accommodated in a location where the remaining tissue annulus will be in contact with a portion of the right circular cylindrical exterior surface of the valve body. The leaflets 15 are preferably identical in shape and size. Each leaflet has two rectilinear, preferably flat, surfaces, i.e. an inflow surface 31 and an outflow surface 33, and the leaflet is preferably of substantially constant thickness such that the surfaces 31 and 33 are parallel to each other. The inflow surface 31 is arbitrarily defined as the surface which faces upstream with the leaflets in the closed position (see FIG. 4), whereas the outflow surface 33 faces downstream. Although the leaflets 15 are preferably flat, other configurations, such as sections of hollow cylinders of circular or elliptical cross section, can alternatively be employed, as discussed in more detail in U.S. Patent No. 5,246,453. The leaflets 15 each have a major arcuate edge surface 35, which is located at the downstream edge of the leaflet in the open position, and each has a minor mating edge surface 37 which is located at the opposite, upstream edge of the leaflet in the open position. The arcuate edge surface 35 preferably has a configuration such as to abut and seat closely against the cylindrical sidewall interior surface 17 of the valve body in the closed position. The minor edge surface 37 is preferably flat and formed at an angle so as to mate flush against the corresponding mating edge surface 37 of the opposing leaflet in the closed position, as best seen in FIG. 4. As a result, the minor edge surface 37 is accordingly oriented at an angle to the inflow surface 31 which is substantially the same as the downstream angle which the outflow surface 33 forms with the centerline plane in the closed position, and it is preferably an angle between about 30° and about 60°. The centerline plane is defined as a plane which includes the centerline of the passageway and which is parallel to the pivot axes of the leaflets; in the illustrated embodiment, it is perpendicular to the flat wall surfaces 23 of the valve body passageway. The angle in question defines the extent of the angular rotation that each leaflet 15 will undergo in moving from the fully open position to the fully closed position. This is taken into consideration because there may be an advantage in having a smaller angle, as opposed to a larger angle, because the leaflets need not rotate as great an angular distance in order to reach the fully closed position. As illustrated in FIG. 4, this angle is about 50° in the preferred embodiment. As best seen in FIG. 7, the leaflets 15 each have a pair of intermediate straight edge regions 39 located between the minor mating edge surface 37 and the major arcuate edge surface 35 wherein a pair of laterally extending ears or tabs 41 are located. As can be seen in FIG. 8, the ears 41 are the same thickness as the flat leaflets 15 from which they laterally extend. The ears 41 are elongated in an upstream-downstream direction when viewed in their open orientation. FIGS. 7 and 9 show that the ears 41 have lateral edge surfaces which are rectilinear surfaces of generally shallow curvature as viewed looking at the leaflet from the inflow surface 31. More specifically, as best seen in FIG. 7, they each have a shallow rounded upstream edge surface 43 and a generally similar downstream edge surface 45. The upstream edge surface 43 is the longer, extending generally laterally of the ear, and it meets and blends smoothly into the downstream surface 45. The major portion of the rectilinear upstream edge surface 43 is perpendicular to the flat inflow and outflow surfaces of the leaflets 15, which flat surfaces simply extend through the regions of the ears, so that the ears have inflow and outflow surfaces that are coplanar with the leaflet main body inflow and outflow surfaces 31, 33. A short arcuate transition edge section 47 is interposed between the major arcuate edge surface 35 and the flat section 39. As previously mentioned, the valve body 13 is formed with the thickened wall sections 21 in the regions where the cavities 25 are located, and preferably these thickened sections are formed with flaring transition surfaces, i.e. an upstream transition surface 49 and a downstream transition surface 51 which lead smoothly from the circular entrance region and the circular exit region of the valve body to the flat wall surfaces 23 wherein the cavities 25 are located. A surface such as the surface 49 may be referred to as a radial swept surface. As a result, the flow passageway through the valve body is generally circular in cross-section except for the two thickened sections 21 which extend inward to the flat wall surfaces 23. As previously indicated, the plane containing the centerline axis of the generally circular passageway that is oriented perpendicular to the flat surfaces 23 is referred to as the centerline plane and is frequently used for reference purposes throughout this specification. The arrangement is such that each thickened section includes two side-by-side cavities which are mirror images of each other and which are located on opposite sides of this centerline plane. As seen in FIGS. 12 and 13, the cavities 25 each have a curved sidewall region 53 surrounding a central flat rear section 54; however, the depth of the cavities 25 is such that the apex of the curved upstream edge surface 43 of the ear does not quite touch the rear walls 54 of the cavities, e.g. a clearance of about 0.0254 mm to 0.1016 mm [1-4 mils (0.001-0.004 inch)]. The flat wall surfaces 23 of the thickened regions serve as the primary bearing surfaces against which one or the other of the straight edge surfaces 39 of the leaflets will usually bear whenever the leaflet is moving between its open and the closed positions. The clearance between the shallow curved edge surface 43 of the ear and the rear wall of the cavity is such to facilitate a controlled cleansing spurt of blood flow, upstream through the cavity past the leaflet ears during the moment of complete closure of the valve as shown in FIG. 4; this guards against the possibility of the occurrence of clotting in the pivot region. The proportioning of the ears 41 and the cavities is such that this cleaning leak is not a high velocity jet that might cause hemolysis; instead, it is a controlled flow through a long narrow leak path that does not induce thrombosis. As best seen perhaps in FIG. 10, the cavities 25 are formed to have an upstream lobe 57 and a downstream lobe 59 on opposite sides of an intermediate throat section 61. The intermediate throat section is formed by a pair of curved fulcrums termed an outward fulcrum 63 and an inward fulcrum 65 with respect to their location having reference to the centerline plane. The outward fulcrum 63 is located substantially even with, but preferably slightly upstream of said inward fulcrum. The upstream lobe 57 is formed with an inclined, straight, camming wall section 67, which is oriented at an angle of between about 5° and about 30° to the centerline plane and preferably between about 15° and about 25°. Although the camming wall section 67 is part of the peripheral wall region 53 and thus has curvature in a radial direction, it is substantially rectilinear and is thus referred to as being straight. At its upstream end, the camming wall section joins a concavely curved wall section 69, which leads gradually downstream from this junction point and serves a guidance function that is described hereinafter. The downstream lobe 59 includes a flat locator wall section 71 immediately below the inward fulcrum, at the downstream end of which wall there is a downstream sloping section 73 leading from its junction point to the downstream end 75 of the cavity. The flat wall section 71 is oriented parallel to the centerline plane and thus provides a guide surface against which the outflow surfaces of the ears 41 bear in the full open position, as best seen in FIGS. 2 and 9. As best seen in FIG. 8, the leaflet ears 41 preferably have their rounded downstream edge surfaces 45 oriented so as to be at an acute angle to the outflow surface 33 of the leaflet, thus presenting essentially a line of contact between the ear downstream edge surface 45 and the sloping wall section 73, which tends to reduce friction and promote cleansing in this region. The leaflets 15 are installed in the valve body 13 by squeezing the body at diametrically opposite locations, as for example along a diameter which is perpendicular to the centerline plane. Such deformation of the heart valve body 13 can take place in accordance with the teachings of U.S. Patent No. 5,336,259, issued August 9, 1994. Squeezing causes the diametrically opposed flat wall sections 23 to separate farther from each other to permit the leaflets to be fitted into the valve body, with the ears 41 being received in the cavities 25. When the squeezing force is removed, the valve body 13 returns to its original annular configuration, leaving only the desired minimal clearance between the flat wall surfaces 23 of the valve body and the straight lateral edge surfaces 39 of the leaflets, in which positions the leaflets are slidably-pivotally mounted for travel between the open and closed positions. The metal stabilizing ring 30 can be appropriately installed, as by snapping into place or by shrink-fitting, in the exterior circumferential groove 29 following the installation of the leaflets; however, it may be preferred to install the metal stabilizing ring before installing the leaflets. Pyrocarbon is the preferred material of valve body construction, and compressive force applied to a pyrocarbon structure by such a metal ring can improve the structural properties of a pyrocarbon valve body. Such a metal ring will be chosen which will have sufficient resiliency to return to its perfectly annular shape following removal of such a squeezing force. By designing the thickened bands 29a so that an inclined ramp is formed at the downstream edge of the downstream one of the two bands, it is possible to install the metal ring 30 by sliding it upward from the downstream end of the valve body 13 and allowing the fingers 30a to snap into place; however, it should be understood that the ring could be installed by shrink-fitting if desired. The irregular ring 30 is shaped so that a section having an inwardly arcuate cross section is received in the arcuate cross section groove and the adjacent section having an inwardly cylindrical surface is seated snugly upon one of the two raised bands 29a that flank the groove 29, depending upon whether a mitral or an aortic sewing ring is to be installed. The unique stiffening ring 30 is designed to facilitate the installation of either an aortic sewing ring or a mitral sewing ring exterior of the valve body 13, as best seen by comparing FIGS. 2 and 2A. In FIG. 2, an aortic sewing ring 81 is illustrated which is designed to leave the upstream exterior surface of the valve body free and clear to permit its insertion into the aortic annulus from which the defective natural valve was excised. For this installation, the irregular stiffening ring 30 is slid onto the valve body 13 from the downstream end with the smaller section having the arcuate, radially inward projections leading. Each of the projections are connected by a thin neck section to the main portion of the stiffening ring as best seen in FIGS. 3 and 3A, which has a cylindrical radially interior face. When the leading projections reach the downstream band 29a flanking the groove 29, sufficient deflection occurs for the ring to continue its upstream travel until the groove is reached, into which the projections then snap in place, as seen in FIG. 6, with the main portion of the stiffening ring tightly surrounding the downstream cylindrical band 29a of the valve body and preferably placing it in at least slight compression. When the valve body is to be equipped with a mitral sewing ring 83 as depicted in FIG. 2A, such sewing ring is positioned so as to occupy a major portion of the exterior wall surface of the valve body 13 upstream of the groove 29, leaving the downstream section free for insertion into the tissue annulus from which the defective natural valve was excised. For this sewing ring, the stiffening ring 30 is installed with the opposite orientation, being slid upward from the downstream end of the valve body 13 with the larger section of the ring 30 having the cylindrical radially interior surface leading. When it reaches the downstream band 29a, it can be forced upstream therepast, and the arcuate inward-facing surfaces of the projections again slide over the downstream band 29a as a result of the combined deflection which occurs. The projections again snap in place in the groove 29, but in this instance the major section of the ring 30 is seated tightly about the upstream band 29a, as shown in FIGS. 2A and 13. The depth of the shallow groove 29 is such that the thickness T 2 (FIG. 14) at the location of the groove is equal to at least about 85% of the thickness T 1 of the major cylindrical section of the valve body. The thickness T 3 at the location of the bands 29a need not be greater than about 120% of the thickness T 1 . This strategic spacing and proportioning in a valve body 13 of the present design allows the wall thickness of the major portion of the valve body to be minimized, thus allowing a larger diameter opening for the passageway through the valve body. Generally, it is now felt that this interior diameter of the valve should be as large as tolerable (while still providing adequate structural strength) because the pressure loss through the valve increases relative to the fourth power of the diameter. Of course, each heart valve excised from the heart of a particular patient will vary with each patient, and therefore a surgeon should have available a set of prosthetic valves of different sizes generally ranging in exterior diameter from about 19 millimeters to 33 millimeters in diameter for fully grown adults. The reference measurement is that of the tissue annulus remaining after the defective natural valve has been excised. The present valve design is such that it can be effectively installed so that the tissue annulus is in direct contact with the outer surface of the valve body 13 for valves that are installed both in the aortic position and in the mitral position. In this respect, it should be understood that, when installed, the raw edge of the tissue annulus will be in contact with the exterior surface of the valve body in the regions marked "A" in FIGS. 2 and 2A. One result of this arrangement is evident from FIG. 2A where it can be seen that the diameter of the substantially circular passageway through the valve is a very large percentage of the diameter of the tissue annulus, which is made possible because of the relative thinness of the major portion of the valve body wall, particularly in the region of the tissue annulus. Alternatively, as indicated above the ring can be heated and shrink-fit onto the valve body so that the main body of the ring 30 is in contact with the desired band 29a. Such shrink-fitting allows greater compressive force to be applied to a pyrocarbon structure by such a metal ring and can improve the structural properties of the pyrocarbon which, as indicated above, is the preferred material of construction. Of course, if the ring is to be installed prior to the installation of the leaflets, a metal is chosen which has sufficient resiliency to return to its perfectly annular shape following removal of the squeezing force. With the heart valve operatively installed in a patient, when it is in the open position, the two leaflets 15 assume an open equilibrium position with respect to the high flow and the direction of blood downstream through the passageway, which may be an orientation where they are substantially parallel to the centerline plane, as illustrated in FIGS. 2 and 2A. The location of the ear 41 within the cavity is illustrated in FIG. 10, from which it should be apparent that, should the dynamic blood forces within the valve body passageway change, the left-hand leaflet which is shown can rotate slightly clockwise so as to maintain such a low energy position either with or without some slight translation. In such an equilibrium position, the leaflets 15 provide very low obstruction to the downstream flow of blood. Yet, despite even such a substantially parallel, full open position, the pivot construction is such that any translational movement either downstream or upstream from this substantially parallel position causes the leaflets to rotate in the direction of closing. Furthermore, in the fully open position as shown in FIG. 2, the leaflets 15 are mounted so as to divide the valve body passageway into 3 sections, a center section located between the two leaflets 15 and two flanking sections. As best seen in FIG. 5, the arrangement is such that the cross-sectional area of each of the two flanking passageway sections is preferably at least as large as the cross-sectional area of the center flow passageway section. As previously indicated, the combination of this particular support of the leaflets 15, together with the shape and proportioning of the valve body 13 contributes to the achievement of smooth nonturbulent flow and the absence of stasis. The toroidal curvature of the curved entrance end 19 leading to a generally cylindrical valve body of substantial overall axial length has been found to achieve this desired end. More specifically, the construction of a valve body to have a curved entrance transition to a tabulated cylindrical, elongated passageway has been found to provide very low pressure drop for a passageway of a particular diameter, which is substantially lower than present commercial mechanical heart valves of the same size. The average axial length of the valve is preferably at least 50% of the interior diameter thereof. The entrance section should constitute not more than about one-third of the average axial length of the valve body, and it should smoothly join with the downstream section, preferably being tangent thereto. . The entrance section is preferably essentially a section of the surface of a torus. The torus is selected so that the interior diameter of the torus is between 80% and 120% of the diameter of the interior circular cross-section of the passageway through the valve body, and preferably between about 90% and 100%. Most preferably it is about 100% so that it will be substantially tangent to the right circular cylindrical downstream interior surface; if not, a short transition section is included. Because the thickness of the valve body is uniform, the exterior surface is a concave toroidal section. The radius of curvature of the circle that is revolved to create the torus is between about 28% and about 80% of the radius of the valve body and preferably between about 40% and about 65%. In FIG. 14, the interior radius of the valve body is marked "R 1 ", and the radius of curvature of the torus is marked "R 2 ". To facilitate aortic installation, the exterior diameter D at the entrance end 19 should not be more than about 10% greater than the exterior diameter D v of the major cylindrical outer surface; it should be at least about 6% greater, preferably, about 6-7%. By locating the stiffening ring at a location along the valve body that is downstream of the leaflet pivot axes, i.e. downstream of the fulcrums where the contact for pivoting is defined, it can accommodate suture rings designed to have the raw edge of the tissue annulus directly lie in contact with the exterior surface of the valve body either upstream or downstream of such suture ring in the regions A in FIGS. 2 and 2A. Such an arrangement contributes to a thinner wall thickness and a larger interior diameter for the passageway. During conditions of high rate of flow of blood downstream through the valve body, both leaflets 15 can be oriented substantially parallel to the centerline of the valve with the outflow surfaces of the ears 41 in contact with the flat wall sections 71 of the downstream lobes of the cavities 25 and with the ear upstream edge in juxtaposition with the camming wall 67 so that rotation past the parallel orientation is prohibited. The flow rate of blood through the valve during the pumping stroke of the associated chamber of the heart will generally exert sufficient force upon the inflow surfaces 31 of the leaflets such as to maintain the leaflets in this substantially parallel alignment. However, when the peak downstream flow of blood has passed so that it slows in its approach to zero flow, prior to the beginning of the reverse flow cycle, the forces of the flowing bloodstream tending to orient the leaflets in such a parallel position lessen, and as a result, the drag of the bloodstream against all of the surfaces of the leaflet becomes the predominant force. This net force tends to move the leaflets and the ears 41 slightly farther downstream, which is permitted by the contour of the downstream lobes 59. However, such further downstream leaflet movement is guided by the engagement of the outflow surface edges of the downstream ear surfaces 45 along the sloping sections 73 of the cavity and the inward fulcrums 65. The result of the ears 41 shifting to such downstream positions, as shown in FIG. 10A, is that the leaflets are no longer parallel to the centerline; instead, they have rotated slightly toward the closed orientation, i.e. so that they are now preferably at an angle to the centerline of about 2° to about 5°, and preferably 3° or greater, as depicted in FIG. 3. This prerotation of the leaflets 15 occurs near the end of pumping stroke and reduces the amount of regurgitation, i.e. the volume of blood which will pass upstream through such prosthetic heart valve prior to the occluders next reaching their fully closed position orientations, on the next closing. This reduction occurs for the following two reasons: (a) the leaflets now need to pivot a fewer number of angular degrees to reach the closed position by reason of the headstart they have from the substantially parallel orientation and (b) the backflowing blood has the immediate opportunity to preferentially contact the leaflet outflow surfaces 33, as opposed to the inflow surfaces 31, so that this component of the overall forces being applied to the leaflets during closing is increased. More specifically, as the reverse flow of blood upstream through the valve begins, the leaflets 15 and the ears 41 immediately translate upstream. This upstream translation of the ears causes immediate camming engagement of the inflow surface edge of each upstream edge surface 43 against the adjacent straight camming wall section 67 of each cavity, while the outflow surfaces of the ears may slide along the rounded inward fulcrums 65. By camming engagement is meant contact wherein there is relative sliding movement along a surface which is inclined to the direction in which the net forces are attempting to move an object, i.e. upstream and parallel to the centerline of the valve body; this camming action causes the leaflet to very promptly pivot or swing toward its closed position while the translation movement continues. Accordingly, upstream translational movement of the ear in the cavity 25 assures that the pivoting of each leaflet toward its closed position orientation occurs promptly at the very beginning of reverse flow and continues, driven by these forces, until the upstream edges of the leaflet ears reach the top of the upstream lobes 57, as illustrated in FIG. 10B. Such initial pivoting is guided by the movement of the inflow surface edge of the ear upstream surface 43 along the camming surface 67 while the outflow ear surface generally slides along the inward fulcrum 65, causing such pivoting or rotation to take place about a center of rotation of pivot that is remote, i.e. which is located substantially past the centerline plane of the valve body; as a result, the length of the moment arm acts to accelerate the initial rotational closing movement. Very low friction is encountered because there is no engagement between the ears and the walls of the cavities such as would create a significant frictional force that would resist closing. When the force of the backflowing blood against the outflow surface 33 of each leaflet has become significant, it causes the inflow surfaces of the ears to contact the outward fulcrums 63, as shown in FIG. 10C, and pivoting thereafter continues guided in part by sliding contact with the outward fulcrum 63. The leaflet has thus pivoted a significant amount as a result of the upstream translation and the shifting to contact with the outward fulcrum 63. Thereafter, the upstream edge surfaces of the ears are guided by movement along the arcuate wall section 69 while the ears simultaneously engage the outward fulcrums 63. Contact with the concave wall sections 69 and the fulcrums 63 remains substantially continuous for about the final one-half of the angular rotation of the ears, and the curvature of the wall 69 is designed so that substantially only rotational motion occurs as the upstream edge surfaces 43 slide therealong as the leaflets thereafter swing to the fully-closed position, illustrated in FIG. 10D and in FIG. 4. In such position, mating edge surfaces 37 of the leaflets abut each other, and the downstream arcuate edge surfaces 35 of the leaflets abut and seat against the cylindrical interior surface 17 of the valve body. During a major portion of the closing movement and specifically during the final stages, this motion is almost pure rotational motion to avoid sliding of the ears along the fulcrums at this time when the upstream edges of the ears move slightly downstream as a result of this rotation. When the mating edges 37 of the two leaflets meet, the contact between the upstream edge of each ear and the arcuate wall 69 is broken, as seen in FIG. 10D, thus avoiding the possibility of localized wear when the pressure across the valve is very high. When the leaflet reaches its nearly closed position, the liquid between the edge 35 of the leaflet and the orifice wall acts like a cushion, and the leaflet further decelerates just before it impacts the wall, reducing the noise and any propensity for cavitation. In the fully closed valve with the leaflets 15 oriented as illustrated in FIG. 4 wherein they are shown in elevation, the force of the blood against the outflow surface 33 of each leaflet is borne mainly by the downstream arcuate edge surfaces 35 seating against the interior valve body surface and by the ears 41 bearing against the outward fulcrums 63. At the instant complete closure is achieved, the pressure of the blood against the outflow surfaces of the leaflets is at its highest and results in controlled leakage through the cavities 25 in an upstream direction. Such leakage is around and past the ears 41 in each cavity as can be seen from FIG. 10D and is controlled in part by the depth and the length of the ears 41. The dimensioning of the ears and the cavities creates a pathway for controlled backflow laterally past the edges of the leaflet ears and thus tends to concentrate such leakage backflow in the regions of the pivot arrangements where such cleansing flow serves to positively guard against the occurrence of clotting. In this respect, the average clearance between the edges of the ears 41 and the walls of the cavities 25 is preferably at least about 50 microns or about 0.002 inch, with the clearance being the least at the region of the apex of the curved upstream edge surface 43. There may be slightly greater clearance adjacent the edge surfaces 45 (FIG. 7) of the ears because of the translating design of the leaflets. When blood flow again reverses, as for example when the pumping stroke of the associated chamber begins again, downstream displacement, i.e. translation, of the leaflets 15 initially occurs as a result of the force of the blood against the inflow surfaces 31. As is evident from FIG. 10D, the outflow surfaces of the ears 41 will quickly come in contact with the inward fulcrums 65, causing opening pivoting motion to quickly begin with the major arcuate edge surface 35 swinging downstream. The downstream edge surfaces 45 of the ears will likely reach the lower arcuate ends 75 of the downstream lobes 59 prior to the ears rotating completely about their pivot points on the fulcrums 65; however, when the blood flow through the valve approaches maximum, the net forces on the inflow surfaces 31 of the leaflets are such that the ears will be ramped upstream along the sloping wall sections 73, causing the leaflets to be displaced just slightly upstream until the substantially parallel position shown in FIG. 10 is reached, with the ears abutting the flat wall section 71 in each downstream lobe. Illustrated in FIGS. 16, 17 and 18A-18D is an alternative embodiment of a prosthetic heart valve 111 which is constructed so as to facilitate the leaflets aligning parallel to the valve centerline or at slight deviations thereto depending upon instantaneous variations in the blood flow path, whichever is the low energy orientation. The cavities are particularly shaped so that the leaflet ears can reach such a parallel orientation initially and can move slightly away from and return to such an orientation during blood flow through the valve for a single pumping stroke. The heart valve 111 includes a generally annular valve body 113 which is generally similar to that previously described. It is designed to function with a pair of leaflets that are exactly the same as those previously described. Thus, the reference numerals 15 are used, and the description of the leaflets is not repeated. The valve body 113 has an interior wall surface which includes two arcuate sections 117 that respectively flank two diametrically opposed flat wall sections 123, and it is likewise formed with the smoothly curved entrance region 119 at its upstream end. A pair of cavities 125 is formed in each flat wall section 123, and shallow notches 127 formed in the downstream wall portion of the valve body provide side openings into the passageways and create a scalloped profile for the valve body 113. The generally right circular cylindrical surface of the major portion of the exterior of the valve body 113 is interrupted by a thickened band 129 which facilitates the installation of a suture ring 130. In the embodiment illustrated in FIG. 16, a suture ring 130 is schematically depicted of a type that would be used to mount the heart valve 111 in the aortic position. When the valve 111 is so mounted, the raw tissue annulus remaining where the defective valve was excised lies in direct contact with the exterior surface of the valve body in the region marked A in FIG. 16 which constitutes a concave surface section of the interior of a torus. It can be seen that this arrangement maximizes the opening of the valve passageway relative to the patient's tissue annulus, promoting high flow rate of blood with very low pressure drop thereacross, oftentimes lower than a commercial mechanical valve which is two sizes larger. Moreover, the outward surface curvature directs tissue regrowth or panus outward away from the entrance of the aortic valve. The valve body 113 fairly closely resembles that hereinbefore described; it has a pair of thickened wall sections wherein the cavities 125 are located that are formed with flaring transition surfaces, i.e. an upstream transition surface 149 and a downstream transition surface 151. Each thickened section includes two side-by-side cavities 125 which are mirror images of each other and which are located on opposite sides of the centerline plane perpendicular to the flat wall sections 123. The cavities are best seen in FIGS. 18A through 18D wherein the details of curvature are shown in each right-hand cavity, and omitted from each left-hand cavity so as not to detract from the description of the movement of the leaflet ears 41 within the cavities. As best seen perhaps in FIG. 17, each of the cavities 125 has a curved sidewall region 153 which is peripheral to a central flat rear section 155. The cavities are each formed with an upstream lobe 157 and a downstream lobe 159 located on opposite sides of an intermediate throat section 161, which is formed by a curved outward fulcrum 163 and a curved inward fulcrum 165. The upstream lobe 157 is formed with an inclined, straight, camming wall section 167 which is oriented at an angle of between about 5° and about 30° to the centerline plane, and preferably between about 15° and about 25° thereto. At its upstream end, the camming wall section 167 joins a concavely curved wall section 169 which leads gradually downstream from this junction point and serves to guide the final swinging movement of the leaflets to the closed position. The downstream lobe 159 includes a flat locator wall section 171 which is located immediately below the inward fulcrum 165. A flat bottom wall 173 extends at right angles from the downstream end of the locator wall 171 in a direction outward and away from the centerline plane of the valve body. The flat wall section 171 is oriented parallel to the centerline plane and provides a guide surface against which the outflow surfaces of the leaflet ears 41 abut in the full open position, as best seen in FIGS. 16 and 18A. In this position as can be seen from FIG. 18A, the downstream edge 45 of the leaflet ear abuts the flat bottom wall 173 of the cavity. The leaflets 15 are installed in the valve body 113 and the suture ring 130 thereupon as generally hereinbefore described. With the heart valve 111 operatively installed for example as a replacement aortic valve in a patient, when the ventricle with which it is associated is pumping, it will be in the open position with the two leaflets 15 assuming an equilibrium open position with respect to the high flow of blood downstream through the passageway, as shown in FIG. 16. As soon as reverse flow of blood upstream through the valve begins, the leaflets 15 immediately translate upstream causing the upstream edges 43 of the ears to slide along the camming wall sections 167, as previously described with respect to the valve 11. This causes each leaflet to very promptly begin to swing toward its closed position as the upstream translation proceeds. Once the ears 41 reach the top of the upper lobes 157, as illustrated in FIG. 18B, the leaflets will have swung away from the parallel orientation and have become significantly cocked or canted to the direction of downstream blood flow, so that the force of the backflowing blood against the outflow surface of each leaflet causes the ears to shift away from the inward fulcrums 163 and abut the outward fulcrums 163 as depicted in FIG. 18C. Thereafter, the upstream edge surfaces of the ears 41 are guided by movement along the arcuate wall section 169 while the inflow surfaces of the ears remain in contact with the outward fulcrums 163 as shown in FIG. 18C. Contact of the ears 41 with the concave wall sections 169 and with the outward fulcrums 163 remains substantially continuous throughout about the final one-half of the angular closing movement, and the curvature of the wall 169 is designed so that substantially only rotational movement of the ears occurs as the upstream edge surfaces 43 slide therealong during the completion of the leaflets swinging to the fully-closed position illustrated in FIG. 18D. In such position, the mating edge surfaces 37 of the leaflets abut each other, and the downstream arcuate edge surfaces 35 of the leaflets are seated against the cylindrical interior surface 117 of the valve body 113, as previously described with respect to the closing movement in the heart valve 11. When downstream blood flow again begins with the next pumping stroke of the associated ventricle, downstream translation of the leaflets 15 initially occurs as a result of the force of the blood against the inflow surfaces 31. As will be evident from FIG. 18D, the outflow surfaces of the ears 41 will quickly contact the inward fulcrums 165, causing opening pivoting motion to quickly begin, with the major arcuate edge surfaces 35 swinging downstream with some translation as the ears also slide along the inward fulcrums 165. As a result of this translation, the downstream edge surfaces 45 of the ears will likely reach the bottom flat walls 173 of the downstream lobes prior to the ears rotating completely about their pivot points on the fulcrums 165; however, the flat bottom wall surfaces 173 allow the downstream edges to easily slide therealong and move smoothly and quickly to the full open position, where the outflow surfaces of the ears are in abutting contact with the locator surfaces 171. If instantaneous blood flow thereafter is such that a substantially parallel orientation is not the low energy position, either or both of the leaflets can easily shift slightly because the upstream portions of the tabs are relatively loosely constrained within the throat of the cavities between the facing fulcrums and the downstream edge is free to slide along the bottom flat wall 173. However, once such an instantaneous condition ends and straight downstream flow again occurs, because of the flat transverse downstream bottom surface, a leaflet that was momentarily displaced can quickly return to the low energy parallel position as the downstream edge 45 of the ear slides along the flat perpendicular bottom surface 173. By confining substantially all of the functionally engaging surfaces that define the paths of opening and closing movement of the leaflets to the regions of the cavities and the ears, many of the regions where it is necessary to hold very close tolerance are concentrated, thereby facilitating both manufacturing processes and quality-control fitting-up procedures. These advantageous results are felt to grow out of the illustrated upstream-downstream lobe design where the lobes are separated by a narrow throat that is formed by the flanking fulcrums which confine the associated leaflet ear and assure smooth movement and positive resistance to jamming. Such a design can effectively function by the use of ears which have cross sections that are generally elongated rectangles or trapezoids, i.e. quadrilaterals having 2 parallel walls of a length at least about 3 times its thickness, in such double-lobed cavities. Moreover, by limiting at least the final about one-third of the closing movement of the leaflets to one of substantially rotation only, the likelihood of severe wear occurring at such points of contact, when force on the leaflet ears is at about its maximum, is greatly diminished. The overall design of the valve is such that gross hemodynamics in terms of energy loss per cardiac cycle are completely acceptable and are superior to mechanical heart valves that are presently commercially available, often exhibiting a pressure drop lower than that of the next larger size and sometimes equal to that of such a valve 2 sizes larger. Because blood is a very delicate tissue and even minor abuses caused by turbulence and high shear can result in thrombosis or emboli generation at local regions of stagnation, it is very important that excessive turbulence coupled with high shear stresses and local regions of stasis be avoided. The foregoing valve design has been found to excellently fulfill such requirements. The employment of leaflets with rectilinear surfaces that are free to follow and easily orient themselves substantially parallel to straight downstream blood flow minimizes the turbulence associated with the leaflets themselves. A desired cavity design which can effect prerotation of the leaflets after the downstream flow through the valve has peaked and nears the end of its cycle can often further reduce regurgitation; however, the pivot arrangement itself and the location of the side notches 27 in the valve body that focus the inflowing blood against the outflow surfaces 33 where the initial closing rotation forces are amplified are significantly instrumental in achieving this desired end result. Although the invention has been described with respect to certain preferred embodiments, which include what the inventors presently consider to be the best mode for carrying out the invention, it should be understood that various changes and modifications that would be obvious to one having the ordinary skill in this art may be made without departing from the scope of the invention which is defined by the claims appended hereto. For example, as earlier indicated, the invention is not limited to occluders in the form of leaflets having flat body sections but is considered to be also applicable to leaflets having curved body sections with substantially rectilinear surfaces. In this respect, it may be desirable to facilitate the creation of a central passageway of greater area through such a bileaflet valve by employing a pair of such curved leaflets to achieve a different distribution of the downstream blood flow through the valve body.

Claims: A prosthetic heart valve (11) which comprises a generally tubular valve body (13) having an upstream end, a downstream end and an interior sidewall which defines a central passageway therethrough for blood flow in a downstream direction, said passageway having an axial centerline and being generally circular in cross section, means (29, 30) associated with the exterior of said tubular valve body for mounting said valve in association with a human heart, at least one occluder (15) having an inflow surface (31) and an outflow surface (33), said occluder being mounted within said valve body (13) to open and close so as to alternately permit flow of blood therethrough in a downstream direction when in an open orientation and to block reverse flow of blood in an upstream direction when in a closed orientation, and a pivot arrangement (41, 25) by which said occluder (15) is associated with the interior of said valve body and by which said occluder is guided in movement between said open and closed orientations, said valve body having an upstream entrance end section (19) characterized in that said end section is formed with an interior surface that has a radius of curvature in a plane which contains said axial centerline between 28% and 80% of said central passageway radius, which entrance end section connects to a downstream cylindrical section (17), whereby downstream blood flow through said valve central passageway in said open orientation is of a streamlined nature. The prosthetic heart valve of claim 1 wherein said downstream cylindrical section (17) has a cylindrical exterior surface of exterior diameter D v extending to said downstream end, and wherein said upstream entrance end section has an exterior diameter that is at least 6% greater than D v . The prosthetic heart valve according to either claim 1 or 2 wherein said occluder (15) has rectilinear outflow and inflow surfaces and wherein said pivot arrangement permits said occluder to assume an alignment so that said inflow and outflow surfaces are substantially parallel to said valve passageway axial centerline when said occluder is in said open orientation. The prosthetic heart valve according to any one of claims 1 to 3 wherein said at least one occluder comprises two leaflets (15), wherein said valve body (13) is formed with a pair of diametrically opposed flat interior sidewall surfaces and wherein said downstream cylindrical section of said valve body terminates in a pair of diametrically opposed shallow notches (27) which provide openings for the reverse flow of blood laterally into a central portion of the valve passageway, said lateral openings being aligned with said valve body flat interior sidewall surfaces. The prosthetic heart valve according to any one of claims 1 to 4 wherein said curved upstream entrance end section (19) is essentially a section of a torus having an interior diameter generally equal to between 80% and 120% of a diameter of said generally circular central passageway. The prosthetic heart valve according to any one of claims 1 to 5 wherein said curved upstream entrance end section (19) comprises a section of a torus extending axially for a distance between 10% and 33% of an average axial length of said tubular valve body. The prosthetic heart valve according to either claim 5 or 6 wherein said torus has an interior diameter equal to a diameter of said generally circular central passageway and wherein said diameter of the upstream edge of said entrance end section is not more than 10% greater than the exterior diameter of said downstream cylindrical section. The prosthetic heart valve of any one of claims 5 to 7 wherein said mounting means includes a suture ring (81) which is so located axially along said exterior surface of said valve body that a tissue annulus raw edge lies in direct contact with a concave exterior circumferential surface of said toroidal upstream entrance end section (19), when said heart valve is implanted in a patient. The prosthetic heart valve according to any one of claims 5 - 7 wherein a major portion of said upstream entrance end section (19) of said valve body is of substantially constant thickness and wherein both said interior surface and said exterior surface of said entrance end section are in the form of at least 30% of a quadrant of a torus. The prosthetic heart valve according to any one of claims 1 to 9 wherein said valve body (13) is axially elongated so that its average axial length is at least equal to 50% of the diameter of said generally circular central passageway.

Inventors: BOKROS JACK C, STUPKA JONATHAN C, WAITS THOMAS C, BOKROS, JACK C., STUPKA, JONATHAN C., WAITS, THOMAS C.
Applicants: VALVE SPECIAL PURPOSE CO LLC, VALVE SPECIAL PURPOSE CO.,LLC.
Application year: 1996
Main classification: A61F2
IPC codes: A61F2