turning now to the drawing , where the purpose is to describe a preferred embodiment of the invention and not limit same , fig1 is a schematic representation of a mechanical device and power supply according to the invention . a device 10 according to the invention may be any mechanical device that is implanted into the body and that is susceptible to blood clotting on one or more of its surfaces to such a degree that interventional therapy is recommended to reduce or eliminate the clotting . device 10 is preferably a heart valve , such as an aortic , tricuspid or mitral valve . other examples of mechanical devices that may be used to practice the invention are pulmonary valves . in this embodiment , device 10 has a connective portion 11 ( for receiving a connection to a power source or otherwise connecting device 10 to a power source ), valve plates 12 and sewing ring 14 . device 10 can be made of any suitable materials that can be charged to prevent or alleviate blood clotting . to render device 10 non - thrombogenic , all or part of device 10 is electrically charged , either positively or negatively , by connecting device 10 to a power source 100 that generates electrical current to charge device 10 . power source 100 is any device or system capable of electrically charging device 10 ( or any part of device 10 ) sufficiently to alleviate or eliminate blood clotting on all or some of the surfaces of device 10 . power supply 100 is preferably a battery pack of a type already known and used with pacemakers . power supply 100 is preferably implanted into the body in a subcutaneous pocket . device 10 is connected to power source 100 via a connection system 120 , which is preferably a pair of wires 122 , 124 , and thus power source 100 electrically charges device 10 . in the preferred embodiment , insulated wires 122 , 124 are attached to the body of the heart valve annulus ( not shown ) and are then transferred out of the heart via , either the left atrium in the case of a mechanical mitral valve , the aorta in the case in a mechanical aortic valve , the right atrium in the case of a mechanical tricuspid valve implant , or the pulmonary artery in the case of a mechanical pulmonary valve , and into the pericardial space . via the pericardial space wires 122 , 124 are then brought over or under the clavical and are attached to power source 100 , which is preferably a battery pack . one difference between the functioning of power source 100 as compared to a pacemaker is that a mechanical device according to the invention should constantly be charged to prevent clotting . since power source 100 generates the charge it may deliver power continuously to device 10 to maintain the constant charge . so , instead of providing intermittent burst current and ekg tracking and sensing capabilities as a normal pacemaker does to stimulate a heart beat when attached to the myocardium , power source 100 preferably provides a constant current via the wires and apply that current to mechanical device 10 . when power source 100 is connected to a mechanical device 10 , such as a heart valve , device 10 will be rendered either positively or negatively charged with respect to the blood stream , and will electrically repel activated platelets and red blood cells thus making anticoagulants unnecessary . preferred power source 100 is a constant discharge pacemaker - style battery pack that includes two electrically separate battery compartments 102 , 104 and a casing , or cannister , 106 . cannister 106 should be laser welded and made to the same general specifications as pacemaker battery casings . the patient &# 39 ; s body , via the power source canister will preferably act as a ground for power source 100 . each battery ( not shown ) preferably is capable of lasting for the patient &# 39 ; s life . a first of the two batteries used in the preferred embodiment generates a current that charges the mechanical device and a second of the two batteries ( if two batteries are used ) automatically activates and generates a current that charges the mechanical device should the first battery fail or become exhausted . power source 100 is preferably capable of adjusting the charge output with a battery systems analyzer ( bsa ). a hyper - dense lithium iodide battery with up to eleven years of battery life or greater is preferred as a battery to be used in power source 100 . a kinetic energy recharging capability may be highly beneficial to increase battery life . power source 100 should be capable of supplying a current anywhere between about ± 100 ma and ± 300 ma to mechanical device 10 . power source 100 preferably has an anode and cathode component to complete the circuit and a connector system 120 that allows leads 107 from the mechanical device to be attached to power source 100 . power source 100 and connector system 120 need to be impervious to body fluids and current pacemaker technology suffices for this purpose . typically , connector system 120 ( in a standard pacemaker design ) is housed within a cylinder of silicone through which the connector wire pin is passed . the connector wire pin then is pressed into a metal coupling . the metal coupling has a screw accessed via the silicone covering with either a small phillips or a regular , bayonet - style screwdriver . once the valve wire is pressed into the housing the screw is tightened and the fitting is impervious to body fluids so that corrosion and current leakage will not occur . the first battery ( not shown ) should be interconnected with the ( redundant ) battery ( not shown ). the connection should have life - of - battery sensing capabilities , which would automatically activate and use the second battery when , for example , telemetrically 10 % or less of first battery life is sensed . if at any time the second battery is activated the first battery should preferably be changed to insure that there is back up to maintain a charge on device 10 . the second battery should have , for example , between 1 and 2 years of battery life , although any suitable life for a redundant battery is sufficient . the second battery should also have some telemetry capability . any time the second battery is activated the first battery should be replaced . the wires 122 , 124 should be thin , and perhaps thinner than those used in current pacemakers . if the wires are too thick , they could pose bleeding problems , for example , if they exited a cardiac vascular structure . the wires will be surgically implanted and do not need steering capabilities , thus , they do not need to be thick for that purpose . wires 122 , 124 should be permanently insulated from their resting external environment . it is estimated that the wires would be supplied as part of mechanical device 10 and would thus not require any additional connection other than connection to power source 100 . preferred mechanical device 10 is a heart valve , as previously described . current heart valves are usually made of pyrolytic carbon , which is generally a good electrical conductor , while the sewing ring is usually made of teflon . both exist in a wet ( blood ), turbulent , environment and will be able to accept and maintain an electrical charge . furthermore , existing heart valves could be modified to accept an electrical charge in a manner according to the invention . valve doors 12 may be identical to those in known valves , and the sewing annulus 14 is identical to known sewing annuluses . the only modification required is the connection for the two flexible , electrically insulated ( preferably plastic coated ) wires 122 , 124 , which would be connected to mechanical device 10 . if device 10 is a heart valve , the wires would preferably be connected to the valve annulus and exit from ring 15 of the valve annulus . in the preferred embodiment , the wires would need to be long enough to traverse the cardiac structure , the pericardial space and over or under the clavical and then descend down the anterior chest wall to be pressed into the receptors of power source 100 . the wire exiting from the valve could have breakable , equivalent to about a 4 - 0 needle thickness , 1 cm curved , round , needles ( not shown ) on their tips . in use , a valve according to the invention is implanted in the heart in the normal fashion . the needles on the wires are then passed outside the heart . once they are ready to be attached to the power source ( and thus preferably electrically connected to the first battery and second battery ) the needles are snapped off and the stump of the needles are inserted into the power source housing and are screw tightened to be retained . standard trial and error , done using techniques known to those skilled in the art , will indicate the necessary charge to repel platelets and passing red blood cells , but in general the current necessary can be expected to lie somewhere between ± 100 to 300 milliamps and / or a charge of ± 100 to 300 millivolts must be applied to device 10 . it might need to be higher than that charge depending upon the indexed mass of the individual . in the event that a multiple heart valve implantation is made all valves could be charged utilizing the invention . having now described preferred embodiments of the invention , modifications and variations to the present invention may be made by those skilled in the art . the invention is thus not limited to the preferred embodiments , but is instead set forth in the following claims and legal equivalents thereof .
a mechanical device for implantation into a patient &# 39 ; s body is designed or modified to be electrically charged to prevent coagulation on the device , thereby extending the life of the device and alleviating the need for the patient to utilize anticoagulant therapy . the device may be a heart valve and is electrically charged by being connected to a power source . the power source is preferably a battery pack implanted in the body and is connected to the device by connector wires . the charge applied to the device may be negative or positive , as long as it helps to repel platelets and / or red blood cells from the device in order to help prevent coagulation on one or more surfaces of the device .