various embodiments of a cardiac device comprise an elastic structure that it introduced into a left ventricle of a heart and assists diastolic function by gently trying to expand the left ventricle . the elastic force is a small fraction of the force during systolic contraction , thus the device has little effect on the systolic pressure or ejected volume . it is well known that diastolic dysfunction is a major cause of cardiovascular failure , as it is far more common than systolic dysfunction . after some time ( weeks to months ) scar tissue permanently binds the elastic structure of the device to the ventricular wall . at this point the device also prevents ventricular enlargement , acting as reinforcement to the ventricular wall and limiting the maximum size of the left ventricle . since the enlargement of the left ventricle as a result of congestive heart failure or infarct is gradual , scar tissue will have a chance to form before full bond strength is required between the elastic structure of the device and the ventricular wall . fig1 shows a typical deployment of a cardiac device 4 according to one illustrated embodiment of the invention . deployment is performed via a catheter 1 inserted through the aorta into a left ventricle 2 of a heart 3 . any method of accessing the left ventricle can be used , such as trans - septal or via the apex of the left ventricle . the catheter size is in the same range as other percutaneous cardiac procedures , using sizes in the range of 18 fr to 28 fr ( about 6 to 9 mm ). the cross section also shows the papillary muscles 5 and device 4 . fig2 - a shows the device 4 still inside catheter 1 . device 4 is held by flexible cable 7 which is used to push the device 4 through the catheter 1 , typically via a hemostatic seal outside the body ( not shown ). typically a guide wire 11 is used to guide the catheter 1 into the left ventricle 2 . fig2 - b shows the device 4 after deployment in the left ventricle 2 of a heart 3 . the device 4 expands elastically to fill the left ventricle 2 . ventricular contractions help embed a number of barbs 8 into a ventricular wall 6 . over time , scar tissue 6 ′ forms a permanent bond between the device 4 and the ventricular wall 6 . the maximum opening of the device 4 is limited not only by the ventricular wall 6 but by flexible cross - members 9 and 10 . it is desired to connect members 9 across the device 4 rather than between adjacent arms ( as shown by reference numeral 10 ) as this allows the cross member to clear the papillary muscles , allowing the device 4 to cover a larger part o the left ventricle 2 . as seen in fig2 b , the papillary muscles 5 can fit between two elastic members of device 4 . fig3 provides a more detailed view of the device of fig1 , 2 - a and 2 - b . the cardiac device 4 has two pairs of elastic arms 4 ′ and 4 ″. the arms 4 ′ and 4 ″ are equipped with barbs 8 and cross members 9 and 10 . the arms 4 ′ and 4 ″ can be made from any durable elastic material such nitinol , spring tempered stainless steel , plated beryllium copper or polymeric material . for added elasticity small loops 12 can be added . at an apex of the device 4 a connector 14 , such as a thread , is used for temporary attachment to the flexible cable 7 via a thread 13 . cross members 9 and 10 can be flexible steel cables , polymeric cables , flexible ribbons or similar flexible members . the purpose of members 9 and 10 is to limit the maximum dilation of the ventricle 2 and stop ventricular enlargement ( after members 4 ′ and 4 ″ bond to ventricle wall 6 by scar tissue 6 ′). the number of flexible members 4 ′ and 4 ″ of device 4 and number of cross members 9 , 10 can vary , the preferred embodiment having from three to twelve elastic members 9 , 10 . cross members 9 , 10 can connect adjacent elastic members 4 ′ and 4 ″ as members 10 do , or connect opposing members 4 ′ and 4 ″ as members 9 do . the arrangement shown in fig3 is desired in order to allow elastic members 4 ′ and 4 ″ to extend beyond the papillary muscles 5 without cross members 9 touching the papillary muscles 5 or mitral valve cords ( also known as chordae tendineae ). like any spring , the force that elastic members 4 ′ and 4 ″ exert on ventricle wall 6 is f = k ( x + a ), “ k ” being the spring constant , “ a ” the preload ( amount of spring preload beyond the fully dilated position ) and “ x ” the ventricular wall movement . the spring constant k is selected not to interfere with systolic function while still helping diastolic filling . by the way of example , a total force the ventricular wall 6 is capable of exerting on each one of the elastic members 4 ′ and 4 ″ is about 20 - 30 nt ( about 2 - 3 kg ) and the average movement during contraction is about 1 - 2 cm . in order to limit the effect on systolic operation the total force is chosen to be below 10 % of systolic force , or about 2 nt . if a preload of 2 cm is chosen , the spring constant can be calculated from the equation : 2 nt = k ( 0 . 02 m + 0 . 02 m ), k = 50 nt / m . the size ( i . e ., diameter ) of wire forming elastic members 4 ′ and 4 ″ is determined by the spring constant k . the size is typically in the range of 0 . 5 - 1 mm . in order to place the device 4 correctly relative to the papillary muscles 5 the orientation of the device 4 inside the left ventricle 6 needs to be known . this can be done by fluoroscopy , ultrasound or by other location methods such as magnetizing elastic members 4 ′ but not 4 ″. this creates a north and south pole 15 which can be detected from outside the body by a magnetometer ( or even a very sensitive magnetic compass ). the design of the device 4 allows aborting the deployment at any stage and retrieving the device 4 . this is illustrated in fig4 . a flexible cable 7 terminating in a hook 16 is introduced via a catheter 1 . cross members 9 are snagged by the hook 16 and the device 4 is pulled back into the catheter 1 . if retrieval is desirable the two cross members 9 should be permanently joined at a cross - over point 18 . this allows the hook 16 to self - center regardless of the point at which the hook 16 snagged cross members 9 and regardless whether the hook 16 has snagged one or both cross members 9 . obviously the retrieval is much more difficult once scar tissue 6 ′ has developed . fig5 - a through 5 - d offer a more detailed close - up view of the construction of the device 4 . fig5 - a shows the elastic elements 4 ′ and 4 ″ of the device 4 made of spring wire , cross members 10 made of thin stainless steel cable and barb 8 made of steel wire spot welded to the remainder of the device 4 . if needed , a load spreading structure 17 can be added . the load spreading structure 17 can be made of bent wire , spot welded to remainder of the device 4 as shown , or can take the form of a polymeric strip . the complete device 4 can be coated with an anti - coagulant coating , drug eluting coating or any beneficial coating well known from the art of stents . fig5 - b shows an alternate illustrated embodiment , cut out from a single sheet of elastic material and bent to shape . this mode of construction particularly advantageous when device 4 is made of nitinol , as nitinol is difficult to join . as before , an optional load spreading structure 17 can be added . fig5 - c shows an embodiment of a device 4 that does not use discrete barbs but providing elastic members 4 with a special surface finish to promote rapid bonding with ventricular wall 6 . some examples of such finishes are : porous surfaces , surfaces coated with biological adhesives , surfaces coated with miniature barbs similar to the well known velcro ® fastener ( generically termed hook and loop fastener ), growth - promoting drug coating etc . it is known in the art that velour - like finishes promote tissue infiltration and greatly increase bonding strength . test results are listed in u . s . pat . no . 4 , 164 , 046 hereby incorporated by reference . fig5 - d shows an embodiment in which the cross members are replaced with a continuous layer of a flexible mesh or flexible hemostatic material 18 , such as dacron fabric . when the layer 18 is hemostatic the device 4 can also seal an aneurysm or puncture in the ventricular wall 6 , while still providing the other stated benefits . this is particularly desirable when the ventricular wall 6 is already significantly thinned by enlargement . while the examples shown use a catheter 1 to enter the left ventricle 6 via the mitral valve , it is obvious that various other techniques may be employed to deploy the device 4 . the device 4 can be installed in the left ventricle 6 also via the aortic valve , by piercing an apex of the left ventricle 6 or by an incision at any convenient point . it can be used percutaneously or during conventional cardiac surgery .
an elastic structure is introduced percutaneously into the left ventricle and attached to the walls of the ventricle . over time the structure bonds firmly to the walls via scar tissue formation . the structure helps the ventricle expand and fill with blood during the diastolic period while having little affect on systolic performance . the structure also strengthens the ventricular walls and limits the effects of congestive heart failure , as the maximum expansion of the support structure is limited by flexible or elastic members .