referring now to the drawings wherein like reference numerals refer to like elements throughout the several views , fig1 shows a transverse cross - section of a left ventricle 10 and a right ventricle 12 of a human heart 14 . extending through the left ventricle is a splint 16 including a tension member 18 and oppositely disposed anchors 20 . splint 16 as shown in fig1 has been positioned to draw opposite walls of left ventricle 10 toward each other to reduce the “ radius ” of the left ventricular cross - section or the cross - sectional area thereof to reduce left ventricular wall stresses . it should be understood that although the splint 16 and the alternative devices disclosed herein are described in relation to the left ventricle of a human heart , these devices could also be used to reduce the radius or cross - sectional area of the other chambers of a human heart in transverse or vertical directions , or at an angle between the transverse and vertical . fig2 discloses an alternate embodiment of the present invention , wherein a balloon 200 is deployed adjacent the left ventricle . the size and degree of inflation of the balloon can be varied to reduce the radius or cross - sectional area of left ventricle 10 of heart 14 . fig3 shows yet another alternative embodiment of the present invention deployed with respect to left ventricle 10 of human heart 14 . here a compression frame structure 300 is engaged with heart 14 at atraumatic anchor pads 310 . a compression member 312 having an atraumatic surface 314 presses against a wall of left ventricle 10 to reduce the radius or cross - sectional area thereof . fig4 is a transverse cross - sectional view of human heart 14 showing yet another embodiment of the present invention . in this case a clamp 400 having atraumatic anchor pads 410 biased toward each other is shown disposed on a wall of left ventricle 10 . here the radius or cross - sectional area of left ventricle 10 is reduced by clamping off the portion of the wall between pads 410 . pads 410 can be biased toward each other and / or can be held together by a locking device . each of the various embodiments of the present invention disclosed in fig1 - 4 can be made from materials which can remain implanted in the human body indefinitely . such biocompatible materials are well - known to those skilled in the art of clinical medical devices . fig5 shows an alternate embodiment of the splint of fig1 referred to in fig5 by the numeral 116 . the embodiment 116 shown in fig5 includes three tension members 118 as opposed to a single tension member 18 as shown in fig1 . fig6 shows yet another embodiment of the splint 216 having four tension members 218 . it is anticipated that in some patients , the disease process of the failing heart may be so advanced that three , four or more tension members may be desirable to reduce the heart wall stresses more substantially than possible with a single tension member as shown in fig1 . fig7 is a partial vertical cross - section of human heart 14 showing left ventricle 10 and left atrium 22 . as shown in fig7 , heart 14 includes a region of scar tissue 24 associated with an aneurysm or ischemia . as shown in fig7 , the scar tissue 24 increases the radius or cross - sectional area of left ventricle 10 in the region affected by the scar tissue . such an increase in the radius or cross - sectional area of the left ventricle will result in greater wall stresses on the walls of the left ventricle . fig8 is a vertical cross - sectional view of the heart 14 as shown in fig7 , wherein a splint 16 has been placed to draw the scar tissue 24 toward an opposite wall of left ventricle 10 . as a consequence of placing splint 16 , the radius or cross - sectional area of the left ventricle affected by the scar tissue 24 is reduced . the reduction of this radius or cross - sectional area results in reduction in the wall stress in the left ventricular wall and thus improves heart pumping efficiency . fig9 is a vertical cross - sectional view of left ventricle 10 and left atrium 22 of heart 14 in which a splint 16 has been placed . as shown in fig9 , splint 16 includes an alternative anchor 26 . the anchor 26 is preferably an elongate member having a length as shown in fig9 substantially greater than its width ( not shown ). anchor bar 26 might be used to reduce the radius or cross - sectional area of the left ventricle in an instance where there is generalized enlargement of left ventricle 10 such as in idiopathic dilated cardiomyopathy . in such an instance , bar anchor 26 can distribute forces more widely than anchor 20 . fig1 and 11 are side views of a hinged anchor 28 which could be substituted for anchors 20 in undeployed and deployed positions respectively . anchor 28 as shown in fig1 includes two legs similar to bar anchor 26 . hinged anchor 28 could include additional legs and the length of those legs could be varied to distribute the force over the surface of the heart wall . in addition there could be webbing between each of the legs to give anchor 28 an umbrella - like appearance . preferably the webbing would be disposed on the surface of the legs which would be in contact with the heart wall . fig1 is a cross - sectional view of a capture ball anchor 30 . capture ball anchor 30 can be used in place of anchor 20 . capture ball anchor 30 includes a disk portion 32 to distribute the force of the anchor on the heart wall , and a recess 34 for receiving a ball 36 affixed to an end of tension member 18 . disk 32 and recess 34 include a side groove which allows tension member 38 to be passed from an outside edge of disk 32 into recess 34 . ball 36 can then be advanced into recess 34 by drawing tension member 18 through an opening 38 in recess 34 opposite disk 32 . fig1 is a perspective view of a cross bar anchor 40 . the cross bar anchor 40 can be used in place of anchors 20 . the anchor 40 preferably includes a disk or pad portion 42 having a cross bar 44 extending over an opening 46 in pad 42 . tension member 18 can be extended through opening 46 and tied to cross bar 42 as shown . in use , the various embodiments of the present invention are placed in or adjacent the human heart to reduce the radius or cross - section area of at least one chamber of the heart . this is done to reduce wall stress or tension in the heart or chamber wall to slow , stop or reverse failure of the heart . in the case of the splint 16 shown in fig1 , a canula can be used to pierce both walls of the heart and one end of the splint can be advanced through the canula from one side of the heart to the opposite side where an anchor can be affixed or deployed . likewise , an anchor is affixed or deployed at the opposite end of splint 16 . fig1 is a view of a cylinder or idealized heart chamber 48 which is used to illustrate the reduction of wall stress in a heart chamber as a result of deployment of the splint in accordance with the present invention . the model used herein and the calculations related to this model are intended merely to illustrate the mechanism by which wall stress is reduced in the heart chamber . no effort is made herein to quantify the actual reduction which would be realized in any particular in vivo application . fig1 is a view of the idealized heart chamber 48 of fig1 wherein the chamber has been splinted along its length l such that a “ figure eight ” cross - section has been formed along the length thereof . it should be noted that the perimeter of the circular transverse cross - section of the chamber in fig1 is equal to the perimeter of the figure eight transverse cross - section of fig1 . for purposes of this model , opposite lobes of the figure in cross - section are assumed to be mirror images . fig1 shows various parameters of the fig8 cross - section of the splinted idealized heart chamber of fig1 . where λ is the length of the splint between opposite walls of the chamber , r 2 is the radius of each lobe , ⊖ is the angle between the two radii of one lobe which extends to opposite ends of the portion of the splint within chamber 48 and h is the height of the triangle formed by the two radii and the portion of the splint within the chamber 48 ( r 1 is the radius of the cylinder of fig1 ). these various parameters are related as follows : from these relationships , the area of the figure eight cross - section can be calculated by : where chamber 48 is unsplinted as shown in fig1 a , the original cross - sectional area of the cylinder is equal to a 2 where 0 = 180 °, h = 0 and λ = 2r 2 . volume equals a 2 times length l and circumferential wall tension equals pressure within the chamber times r 2 times the length l of the chamber . thus , for example , with an original cylindrical radius of four centimeters and a pressure within the chamber of 140 mm of mercury , the wall tension t in the walls of the cylinder is 104 . 4 newtons . when a 3 . 84 cm splint is placed as shown in fig1 and 16 such that λ = 3 . 84 cm , the wall tension t is 77 . 33 newtons . fig1 and 18 show a hypothetical distribution of wall tension t and pressure p for the figure eight cross - section . as ⊖ goes from 180 ° to 0 °, tension t s in the splint goes from 0 to a 2 t load where the chamber walls carry a t load . it will be understood that this disclosure , in many respects , is only illustrative . changes may be made in details , particularly in matters of shape , size , material , and arrangement of parts without exceeding the scope of the invention . accordingly , the scope of the invention is as defined in the language of the appended claims .
an apparatus and method for treatment of a failing heart . in one embodiment , the apparatus and method includes a deploying a tension member for drawing at least two portions of the heart toward each other across a heart chamber .