this invention is herein described in detail , as a non - limiting model and as the preferred way to develop it at present . it is also illustrated in the pictures attached hereto . at present , the specific and preferred way to build the orthotopic total artificial heart , according to this invention , is the one illustrated as a model in the pictures attached hereto . notwithstanding , the present invention may be subject to different shape and size modifications and the present specifications are not intended to limit the invention to the particular shapes and / or sizes herein described . on the contrary , the intention is to cover all modifications and alternative executions that are within the spirit and the purpose of the invention in accordance with the claims attached hereto . moreover , as there shall be several modifications and changes that shall be analyzed by the technicians in this field , we do not wish to limit the invention to the exact construction or operation described herein . therefore , any and all equivalent modifications shall be considered as included within the scope of the instant invention . the electro - hydraulic preferred embodiment of the orthotopic total artificial heart , as shown in the schematic representation of fig2 comprises an outer compressing chamber 4 , a compressing fluid 3 , two blood chambers , right 1 and left 2 , and a mechanism for independently varying their discharging volumes . the outside wall of the instant invention is an outer compressing chamber 4 , the external shape of which has an anatomy which agrees with the mediastinal space that it shall occupy , as shown in fig3 . a , 3 . b , 6 , 6 . a , 6 . b , 7 , 7 . a and 7 . b , with an oval or kidney or pyramidal shape , with a upper vertex and a lower and left base . it will occupy the space called anterior mediastinum . the outer compressing chamber 4 of the preferred embodiment of instant invention is constituted by different sectors , as observed in fig3 and 3 . a : a mid sector 14 , which is placed in front of the right auricle 17 and left auricle 18 ; an upper sector or vertex 15 , which is raised up to a horizontal plane crossing at the right pulmonary artery &# 39 ; s lower border level 12 , and is extended in the front up to the breastbone 24 ( see fig7 . a and 7 . b ); a lower sector or base 16 which is extended up to the diaphragm 21 and the area of the native heart end , occupying the supradiaphragmatic free space 33 ( see fig8 . b ) created by removing the 2 native ventricles . in all these figures of the preferred embodiment , fig3 a , 3 b , 4 , 5 , 5 a , the initial sector of both great vessels has been surgically removed , as seen in fig8 b . the outer compressing chamber 4 , as shown in a frontal view in fig3 . a and 3 . b , has its left edge 22 moving from left to right as it ascends distancing itself from the diaphragm 21 and reaches close to the left edge of the aorta artery at its upper part . the right edge 23 of said outer compressing chamber 4 travels up more or less vertically from the diaphragm level 21 . the outer compressing chamber 4 &# 39 ; s depth is extended from the right 8 and left 9 auricular - ventricular inlet ports to the breastbone 24 , as shown in fig7 . a and 7 . b . the rear side , in its upper and right sector , above the right inlet port 8 of the right blood chamber 1 , as shown in fig6 . a , 6 . b , 7 , 7 . a and 7 . b , presents a geometric structure , a cone trunk 25 , which creates a growing and oblique protuberance , to the upper and to the rear parts . in the upper edge of this cone trunk 25 , the posterior outlet port 10 of the right blood chamber 1 is located and connected directly to the pulmonary circulatory circuit . the outer compressing chamber 4 , as shown in the fig2 outline , has four holes , two inlets and two outlets , for the connection of blood chambers to the patient &# 39 ; s circulatory systems ,. the inlet ports 8 and 9 are placed on the rear side of the present invention , as shown in fig5 . a , 6 , 6 . a , 6 . b , 7 , 7 . a and 7 . b . the right inlet port 8 of the right blood chamber 1 receives blood from the right auricle 17 . the left inlet port 9 of the left blood chamber 2 , receives blood from the left auricle 18 , as shown in fig3 . a and 8 b . the outlet ports 7 and 10 are located in the upper side of outer compressing chamber 4 , as shown in fig3 . a , 3 . b , 6 , 6 . a , 6 . b , 7 , 7 . a and 7 . b . the anterior outlet port 7 of the left blood chamber 2 , connects through the neoentrance 26 ( see fig8 . a and 8 . b ) to the systemic circulatory circuit . the posterior outlet port 10 of the blood chamber 1 , is located in the upper part vertex of the cone trunk structure 25 , which creates a protuberance in the rear side of the outer compressing chamber 4 , and is connected through the neoentrance 27 with the pulmonary circulatory circuit , as shown in fig8 . a and 8 . b . after removing the initial sector of the great vessels , neoentrance 26 and neoentrance 27 are in a higher position than that of the aortic valve 28 and the pulmonary valve 29 , as shown in fig8 and 8 . a . as shown in fig3 . a , 3 . b , 4 , 5 and 5 . a , posterior outlet port 10 of the instant invention is behind the anterior outlet port 7 , that is they are in an inverted position compared to the outlet valves of the native ventricles . inside the outer compressing chamber 4 of the preferred embodiment of the instant invention , as shown in the outline represented in fig2 there are the compressing fluid 3 , and two structures with the shape , size , walls and connections of the instant invention , the right blood chamber 1 and the left blood chamber 2 . they occupy the whole inner volume of this outer compressing chamber 4 , which is sealed . the compressing fluid 3 ( for example glycerin ), as shown in the schematic representation of fig2 occupies the volume defined by the inner side of outer compressing chamber 4 , the moving surface 5 , and the external walls 31 of both blood chambers . this compressing fluid 3 is used to transfer the driving force of the moving surface 5 to the external walls 31 of both blood chambers . the compressing fluid contained inside the outer compressing chamber 4 , acts in such a way that when the moving surface 5 is in a filling or diastolic position , as shown in fig3 . a , 5 and 5 . a , it allows the right 1 and the left 2 blood chambers to reach each of them a volume of 90 cc , when the blood enters through the right inlet port 8 of the right blood chamber 1 and through the left inlet port 9 of the left blood chamber 2 . both blood chambers shall have their respective outlet ports 10 and 7 closed . while the moving surface 5 moves 3 centimeters forward inside the outer compressing chamber 4 , reaching its maximum blood ejection or systolic position , as shown in fig3 . b and 4 , it transfers the forces received from the driving mechanism to the compressing fluid 3 , which shall compress the external wall 31 of the right 1 and left 2 blood chambers producing the emptying effect of their inner volume , obtaining in such a way the expulsion or ejection of the blood contained inside them , through the posterior outlet port 10 of the right blood chamber 1 , and the anterior outlet port 7 of the left blood chamber 2 . both blood chambers shall have their respective inlet ports closed . the right blood chamber 1 is a soft and flexible sac created to pump the blood , and is placed in front and above the position of the right auricle , to the right in the outer compressing chamber 4 , as shown in fig3 a , 3 b , 4 , 5 and 5 a . it is composed of two soft and flexible walls , its inner cavity has no corners , stitches or boundaries between the different materials , as its inner biological membrane 32 shall be totally constituted by a single - piece pig pericardium . its external wall 31 is a synthetic one , made of pebax 3533 , for example . this right blood chamber 1 is connected through its right inlet port 8 to the right auricle 17 and through its posterior outlet port 10 to the pulmonary circulatory . said right blood chamber 1 , when fully expanded , reaches the anterior thoracic wall and has an elongated shape essentially directed up and back . as shown in fig3 a , 3 b , 4 , 5 and 5 a , this right blood chamber 1 shall have a significant difference with the anatomic structure of the native right ventricle . its blood flow pathway goes up and back from the right inlet port 8 , almost in a straight line as shown in fig3 . a , 3 . b , 4 , 5 and 5 a , until reaching and connecting directly to the neoentrance 27 of the pulmonary circulatory system , which occupies a posterior position inside the mediastinum , as shown in the schematic comparison of fig8 and 8 . a . therefore , we avoid the loop originated in the embryonic circulatory tube , or downward path that the blood makes inside the native right ventricle , by entering through the tricuspid valve and descending to the diaphragm 21 . the supradiaphragmatic space 33 of the anterior mediastinum shown in fig8 . b , is reserved to place the driving mechanism 6 located in the base sector 16 of the preferred embodiment of the instant invention , as shown in fig3 . a and 3 . b . the left blood chamber 2 is also a soft and flexible sac created to pump blood , and is placed in front and above the position of the left auricle located to the left in the outer compressing chamber 4 . as shown in fig3 a , 3 b , 4 , 5 and 5 a , it is composed by two soft and flexible walls , its inner cavity has no corners , stitches or boundaries between different materials since the inner biological membrane 32 is totally composed by a single - piece pig pericardium . its external wall 31 is a synthetic one , made of pebax 3533 , for example . from its left inlet port 9 or mitral valve , which connects it to the left auricle 18 as shown in fig3 . a , 3 . b , 4 , 5 and 5 . a . said left blood chamber 2 , when fully expanded reaches the anterior thoracic wall and has an elongated shape essentially directed up and to the right in the anterior mediastinum , having its outflow pathway in front of the right outflow pathway . the position of the anterior outlet port 7 is shown in fig3 . a , 4 , 5 and 5 . a and is placed in front of the posterior outlet port 10 . in this way , the left blood chamber 2 also allows the blood flow to be almost straight and in an anterior , upward and right direction , to the systemic circulatory system . these two blood chambers of the instant invention , right 1 and left 2 , soft and flexible , have a double membrane wall , as shown in the schematic representation of fig2 and have an inner cavity the volume of 90 cc each . however , the discharging volume of each blood chamber can be independently varied . to decrease or increase the final diastolic volume of each blood chamber independently , the preferred embodiment of the instant invention has a mechanism for independently varying discharging volumes . in the interstitial space between the inner walls 32 and the external ones 31 of each blood chamber a fluid , called interstitial fluid 13 , is introduced through a catheter 34 of the mechanism for independently varying discharging volumes , as shown in the outline of fig2 . when the space between the inner wall 32 and the external wall 31 is filled with the interstitial fluid 13 , the inner volume of each blood chamber is reduced . when the intersticial liquid 13 is removed by means of the catheter 34 of the mechanism for independently varying discharging volumes , the final diastolic volume of each blood chamber is increased independently . the interstitial fluid 13 may be , for example , glycerin . this mechanism for independently varying discharging volumes is handled through the catheter 34 as shown in the schematic representation of fig2 and inserted , for example , via a central vein . this catheter 34 is introduced into the outer compressing chamber 4 , next to the inlets 8 and 9 of the blood chamber , from the neck veins and it is connected to the external wall 31 . in this way , during the implantation period and the postoperative period , the physician can vary the interstitial volume of each blood chamber , being able to independently vary their final diastolic volume , to achieve a blood flow in the systemic circuit and in the pulmonary circuit , according to the physiological needs of each patient and the specific operation of each device . an electro - hydraulic variant in the design of the outer compressing chamber 4 of the instant invention , having two lateral moving surfaces 39 to produce the compressing effect on the two blood chambers , is shown in fig3 c . in this outer compressing chamber 4 , the lateral moving surfaces 39 are shown in a diastolic position . these two lateral moving surfaces 39 when displaced to the center of the outer compressing chamber 4 increase the pressure of compressing fluid 3 , which effects the compressing action of the blood chambers , right 1 and left 2 . another variation in the design of the outer compressing chamber 4 of the instant invention is shown in fig3 d . to produce the compressing effect on both blood chambers , a variation of the volume of the compressing fluid 0 a inside the outer compressing chamber 4 is produced . a variation on the volume of the compressing fluid 40 a is produced , for example , by gas injection and extraction within the outer compressing chamber 4 ; this outer compressing chamber 4 is characterized by its low volume change upon changes in the internal pressure upon gas injection and extraction . fig3 d shows a schematic representation of the outer compressing chamber 4 with the same layout for the right 1 and the left 2 blood chambers and with one connection for a tube 40 which connects to a source that introduces and extracts gas . fig3 d shows the compressing fluid 40 a in the outer compressing chamber 4 which , in this case , is a gas . an electro - mechanic variation of the instant invention is that in which the blood pumping function is effected by a different driving mechanism as shown in fig1 , 11 , 12 and 13 . the right blood chamber 1 , is connected on the back to its respective right inlet port 8 through which it receives the blood from the right auricle . the left blood chamber 2 is connected on the back to its left inlet port 9 through which it receives the blood from the left auricle . in the front of inlet ports 8 and 9 , as shown in fig1 and 13 , both blood chambers are extended up to the breastbone 24 , and this part of both blood chambers are placed parallel , in a somewhat oblique direction to the left . in fig1 , we can see the simultaneous , joint and direct compressing action produced by two lateral moving surfaces 41 , on the right lateral wall of the right blood chamber 1 , and on the left lateral wall of the left blood chamber 2 , moved by the driving mechanism 6 . fig1 is a cross - sectional view a - a 1 of fig1 , which is at the level of inlet ports 8 and 9 of the right 1 and left 2 blood chambers . here we can see that their front sectors , close to the breastbone 24 , are placed with their inner lateral sides in a parallel position and together , and are supported by each other to receive the joint lateral compressing effect of the two lateral moving surfaces 41 . an electro - mechanic variation of said compressing mechanism is shown in fig1 and fig1 , in which the direct compressing action is produced by one pair of lateral moving surfaces 42 for each blood chamber , each pair acting independently on the lateral walls of said blood chambers . said moving surfaces 42 are moved by the driving mechanism 6 . yet another variation of the instant invention consists on an arrangement comprising two outer compressing chambers , each one enclosing its respective blood chamber , said outer compressing chambers having one or more moving surfaces . said outer compressing chambers can be separate from each other or share a common wall , said common wall becoming then a septum dividing the inner spaces of each outer compressing chamber . each said outer compressing chamber has at least two openings ; one of the openings coincides with the inlet port and another opening coincides with the outlet port through which blood comes in an out respectively . the space enclosed between each outer compressing chamber and its respective blood chamber is filled with a compressing fluid . said compressing fluid &# 39 ; s function is to transmit the forces exerted on the movable surfaces of the outer compressing chamber into the blood chamber which is soft and flexible . hence , a reduction in the volume effected on the outer compressing chamber by the compressing mechanism results on a concomitant reduction in the inner volume of the blood chamber . said compressing mechanism is driven by at least one power source , also located inside the mediastinum . said reduction in the inner volume of each blood chamber ejects the blood contained by it . this assembly enables the independent management of systemic and pulmonary flow rates with all the advantages outlined above . still another variation of the instant invention consists on an arrangement comprising two outer compressing chambers . said outer compressing chambers can be separate from each other or share a common wall , said common wall becoming then a septum dividing the inner spaces of each outer compressing chamber . each said outer compressing chamber encloses its respective blood chamber , said outer compressing chambers being characterized by their low volume change upon changes in internal pressure occurring during use . each said outer compressing chamber has at least three openings ; one of the openings coincides with the inlet port and another opening coincides with the outlet port through which blood comes in an out respectively . the space enclosed between each outer compressing chamber and its respective blood chamber is filled with a compressing fluid . each said outer compressing chamber has at least one opening through which compressing fluid is added or withdrawn into each outer compressing chamber . the cyclic addition and withdrawal of compressing fluid in and out of each outer compressing chamber effects the compression and expansion of the enclosed blood chambers , which are soft and flexible . the preferred compressing fluid is a gas , more preferably an inert gas . the reduction in the inner volume of each blood chamber ejects the blood contained by it . this assembly enables the independent management of systemic and pulmonary flow rates with all the advantages outlined above . another variation of the instant invention refers to a variation of the independently varying discharging volumes mechanism . this mechanism has been designed in order to be able to vary independently the volume ejected by each blood chamber . this variation consists on blood chambers with different volumes . for example , the right blood chamber 1 has an inner volume of 85 cc , and the left blood chamber 2 has an inner volume of 95 cc . the right blood chamber 1 ejects blood to the pulmonary circuit , which pumps against an average pressure of 50 to 25 mm of hg . this pressure is lower than the pressure at which the left blood chamber 2 ejects to the systemic circuit , which has an average arterial pressure of 120 to 80 mm hg . due to the different pressures at which each of the blood chambers ejects , being the pressure of the right blood chamber 1 lower , when the variable displacement of the moving surfaces displaces a volume lower than 170 cc , for example 160 cc , the right blood chamber 1 is totally emptied and ejects 85 cc and the left blood chamber 2 ejects only 75 cc . when there is a compressing displacement of 170 cc , both blood chambers eject 85 cc each . when there is a compressing displacement of 180 cc , the left blood chamber 2 ejects 10 cc more than the right blood chamber . [ 0088 ] moving surface displacement rbs ejection lbs ejection 160 cc . 85 cc . 75 cc . 170 cc . 85 cc . 85 cc . 180 cc . 85 cc . 95 cc . this improvement of the independently varying discharging volumes is also applied to the variant of the instant invention effecting the blood pumping using a direct compressing action of the blood chambers as shown in fig1 and fig1 where the pressure is produced jointly by the lateral moving surfaces 41 . it first empties the right blood chamber 1 , which ejects against a lower pulmonary circuit pressure and the lateral moving surfaces displacement is regulated to vary the blood flow in each circuit according to the physiological needs . in the variant in which each blood chamber has two separate lateral moving surfaces 42 , the displacement of each pair of them is adjusted in order to independently handle the volumes ejected . those skilled in the art will recognize , or be able to ascertain using no more than routine experimentation , many equivalents to the specific embodiments of the invention specifically described herein . such equivalents are intended to be encompassed in the scope of the following claims .
an orthotopic total artificial heart for replacing the human heart comprising a new design of two assembled blood chambers with an original layout between themselves and between their inlet and outlet ports . such design enables a significantly better space utilization inside the anterior mediastinum than the prior art ; realizing the required anatomical fit .