a system and method which provides flow rates suitable for hemodialysis applications and provides other beneficial features in accordance with the presently preferred exemplary embodiment of the invention will be described below with reference to fig1 - 12 . those skilled in the art will readily appreciate that the description given herein with respect to those figures is for explanatory purposes only and is not intended in any way to limit the scope of the invention . all questions regarding the scope of the invention should be resolved by referring to the appended claims . fig1 - 12 illustrate a triple lumen critical care catheter 110 in accordance with the invention . catheter 110 has an elongated cylindrical body portion 112 preferably made of silicone , although cylindrical body portion 112 may alternatively be made of polyurethane or cross - linked polyethylene if so desired . the tubular body portion 112 contains three parallel lumens 114 , 116 , and 118 , as will be described in more detail below with respect to fig1 and 12 . a polyester cuff 120 is adhered to the silicon tube 112 using a medical adhesive . polyester cuff 120 secures the catheter to the patient &# 39 ; s skin in a known manner to prevent the opening in the patient &# 39 ; s skin from weeping during use of the catheter 110 . in a presently preferred embodiment of catheter 110 , the catheter is provided with a blunt tip . thus , prior to hemodialysis use , the catheter 110 is cut to length , and the arterial lumen is cut back approximately 1 inch from the end using a razor blade or other sharp instrument so that the blood intake in the exposed arterial lumen will occur approximately 1 inch upstream from the point where the venous lumen returns the treated blood into the patient &# 39 ; s blood vessel . this is desired to prevent the mixing of the treated and untreated blood . of course , other types of tips may be used as well , such as the conical tips described in the afore - mentioned mahurkar patents . at the proximal end of the catheter 110 , the three lumens 114 , 116 , and 118 open up into a y - shaped connector or hub 122 which forms three internal , separate passageways which communicate with the proximal ends of the lumens 114 , 116 , and 118 . the proximal ends of the catheter lumens 114 , 116 , and 118 are generally expanded slightly to fit over mating sections at the distal end of the hub 122 , and the inside walls of the catheter lumens 114 , 116 , and 118 are bonded to the mating walls of the hub 122 by conventional techniques such as vulcanization or thermal plastic welding . alternatively , the hub 122 may be molded in place on the end of the catheter 110 using mold inserts to form the passageways of the hub 122 . the hub passageways 122 diverge from each other as they extend towards the proximal end of the hub 122 and also increase in cross - sectional area . to facilitate connection of the catheter hub 122 to the conventional tubes leading to a dialysis unit , injection syringes , or other extracorporeal equipment , extension tubes 124 , 126 , and 128 extend from the proximal end of the hub 122 . clamps 130 , 132 , and 134 are also placed on the extension tubes 124 , 126 , and 128 , respectively , to permit opening and closing of the respective fluid passageways , thereby controlling the flow of blood between the catheter 110 and the dialysis unit ( not shown ). extension tubes 124 , 126 , and 128 are soft and flexible and are easily manipulated and easily closed by the pressure of the clamps 130 , 132 , and 134 . the proximal ends of the extension tubes 124 , 126 , and 128 receive respective ferrules 136 , 138 , and 140 formed as integral parts of female luer connectors 142 , 144 , and 146 . the luer connectors 142 , 144 , and 146 couple the proximal ends of the respective extension tubes 124 , 126 , and 128 to the flexible tubes leading to the extracorporeal equipment ( not shown ). of course , extension tubes 124 , 126 , and 128 may also be u - shaped in order to reduce the risk of accidental dislodgement of the catheter 110 from the patient during hemodialysis . fig1 illustrates the cross - sectional view along line 10 -- 10 of fig1 in accordance with a first embodiment of the invention . as shown , a relatively small lumen 114 with a circular cross - section is provided for accepting a guide wire , for injecting therapeutics into the patient &# 39 ; s bloodstream , for withdrawing blood samples from the patient , for measuring the pressure in the blood vessel of the patient , and the like . a venous return lumen 116 with a substantially circular cross - section provides a venous return path for returning the treated blood to the patient . a circular cross - section is generally preferred since it is smooth in profile and thus provides the least flow disturbance and hence the best flow rates for the blood . also , since the venous lumen 116 is smooth in profile , no slow moving currents form within the venous lumen 116 which may lead to the formation of platelets or blood clots . an arterial intake lumen 118 with a substantially smooth ellipsoidal cross - section is provided for creating a vacuum pressure used to remove blood from the patient through capillary action . as shown in fig1 , the arterial lumen 118 may preferably have an ellipsoidal cross - section in the shape of a football , or , as shown in fig1 , the arterial lumen 148 may also have an ellipsoidal cross - section in the shape of an ellipse . as with the venous lumen 116 , the arterial lumen 118 is smooth in profile to avoid slow moving currents within the arterial lumen 118 which may lead to the formation of platelets or blood clots . also , in accordance with the invention , it is desired that the cross - sectional areas of the arterial intake lumens 118 or 148 be at least 10 %. larger than the cross - sectional area of the venous return lumen 116 for a catheter 110 of a particular french size in order to better balance the flows within the respective lumens 116 and 118 . in a presently preferred commercial embodiment , the arterial intake lumen 118 has a cross - sectional area which is approximately 25 % greater than the cross - sectional area of the venous return lumen 116 ; however , optimum flow characteristics are also achievable if the arterial intake lumen 118 has a cross - sectional area which is anywhere from approximately 10 % to approximately 30 % greater than the cross - sectional area of the venous return lumen 116 . to provide a measure of the flow rates and resulting pressures in the arterial and venous lumens of a catheter having the cross - section illustrated in fig1 with respect to the &# 34 ; longhorn &# 34 ; catheter with the cross - section illustrated in fig9 the following test arrangement was created . first , so that testing could be performed without human subjects , a test fluid with the same viscosity as blood was created ( human blood has a viscosity of 3 . 5 - 4 . 0 centipose ). in particular , 1000 ml of water was mixed with 317 . 5 ml of glycerol to obtain a mixture of 40 % by weight of glycerol . the resulting &# 34 ; syn - blood &# 34 ; had a viscosity of 3 . 646 centipose . the &# 34 ; syn - blood &# 34 ; was then run through a test stand using a 4509 extracorporeal module pressure and vacuum unit and a 4533 accessories module blood pump and flow meter unit made by drake willock . the test stand was set up by first attaching an appropriate blood line to the extracorporeal module . the pre - pump monitor line was then attached to the arterial vacuum gauge module , and the post pump monitor line was attached to the venous pressure gauge on the accessories module . the intake and return lines were then placed into a 1000 ml beaker half full of &# 34 ; syn - blood .&# 34 ; the pump was run to fill the lines of the catheter and to displace all of the air bubbles . the arterial ( intake ) line on the pump was then attached to the arterial intake leg of the catheter . the venous ( return ) line on the pump was then attached to the venous ( return ) leg on the catheter . the pump was run again to displace any air bubbles . then , with the catheter tip completely submerged in the syn - blood , the pump was run at 50 ml / min and the venous pressure and arterial vacuum were recorded . the flow rate of the pump was then increased to 100 ml / min and the venous pressure and arterial vacuum again were recorded . since the pressure and vacuum pulsated slightly , the high values were recorded . this process was repeated for each flow rate until the venous pressure or arterial vacuum went off of the scale of the gauge ( 160 mm hg vacuum ; 310 mm hg pressure ). this process was repeated for each catheter . table 1 illustrates the flow rates determined using the experimental set - up for the catheter with the cross - section illustrated in fig1 ( the outer diameter of the catheter tested was , on average , 0 . 165 inch ), while table 2 illustrates the flow rates using the experimental set - up for the &# 34 ; longhorn &# 34 ; catheter with the cross - section illustrated in fig9 and an average outer diameter of 0 . 164 inch for the actual catheter tested . in each case , a * means that the pressures were beyond the range of the measuring instrument . the cross - sectional area of the arterial lumen on the fig1 catheter was 0 . 00425 square inch , while the cross - sectional area of the venous lumen on the fig1 catheter was 0 . 00336 square inch , for a difference in cross - sectional area of 26 percent . the cross - sectional areas of the arterial and venous lumens of the fig9 catheter were both approximately 0 . 00327 square inch . both catheters could fit through a 13 french spreadable sheath with an inner diameter of 0 . 170 inch . table 1______________________________________triple lumen catheter flow data for fig1 design______________________________________flow rate 50 100 150 200 250 300ml / min . arterial 20 70 100 145 160 *( vac ) mm hgvenous 45 110 180 270 310 *( pres .) mm hg______________________________________ table 2______________________________________triple lumen catheter flow data for fig9 design______________________________________flow rate 50 100 150 200 250 300ml / min . arterial 70 130 160 * * *( vac ) mm hgvenous 40 95 150 210 * *( pres .) mm hg______________________________________ as known by those skilled in the art , a screw extruder may be used to manufacture bulk extruded silicone tubing and strapping , and such a device together with a hot air vulcanizer are preferably used to manufacture the catheter 110 of the invention . the procedures for operating a conventional screw extruder , such as a model # 72587 large screw extruder , and completing the manufacture of a catheter 110 in accordance with the invention will now be described . first , the milled or softened silicone is stripped into sheets that are 3 / 8 to 5 / 8 inch thick and is laid onto clean polyethylene sheeting . techniques for milling and softening silicone rubber elastomers are believed to be known to those skilled in the art and will not be discussed in further detail herein . the sheet of silicone is then cut into strips approximately 1 / 2 to 2 inches wide . the extruder is then started . the rheostat of the preheating unit of the extruder is then set by increasing the setting until the surface markings of the tube 112 caused by the belt in the hot air vulcanizer are removed . alternatively , the rheostat may be set to a value appropriate to the material being run on the extruder by referencing previous manufacturing runs . the face plate located at the exit end of the extruder screw barrel is then removed . the mesh screen on the inside of the face plate is also removed and replaced with a clean # 60 mesh screen . if the same tubing construction from a previous run is being repeated , the reference die and mandrel from the previous manufacturing run is selected . alternatively , the manufacturing information on the log sheets for the tubing which fits the general parameters of dimensions and density are referenced . similar die / mandrel combinations for new structures are used . a mandrel with the cross - section illustrated in fig1 is then inserted onto the open end of the mandrel holder on the face plate with the flat end of the mandrel facing the set screws . the mandrel is secured by tightening the set screws . the die is placed onto the die holder and secured into place with cap screws . the extruder head is then screwed into position on the threaded sections of the face plate . next , the screw extruder is started at low speeds with the die head facing upward . if the silicone flow is not &# 34 ; on - center &# 34 ; ( i . e ., the silicone will form a column of silicone 1 to 11 / 2 inches straight up from the die head ), the cap screws are adjusted until the flow from the die head is straightened . once the silicone flow is centered , the die head is re - positioned to feed material into the preheater of the hot air vulcanizer . a high temperature thermometer is then preheated to 200 ° f . and placed on the conveyor belt of the hot air vulcanizer . the thermometer is sent through the hot air vulcanizer , and the temperature setting is adjusted until the thermometer reads 385 ° f .± 5 ° f . the extruder is positioned so that the tubing passes through the middle of the static eliminator preheating station elements and onto the hot air vulcanizer belt . twenty - five to thirty feet of tubing are then extruded and allowed to go through the hot air vulcanizer . the tubing is then inspected visually for air bubbles , discoloration , unacceptable extrusion markings , and the like . the tubing so manufactured is then measured and cut using a guillotine cutter , and the cross - section of the tubing is inspected . if the tubing is within tolerance , the extruder is ready for a production run . otherwise , the extruder settings are adjusted as appropriate . if the silicone used during the production run is a peroxide cured rubber , the tubing is wound around curing drums , and the curing drums are placed into an oven and cured at 400 ° f . for four hours . all cured tubing is then in - process tested for stretch cracking by stretching it and checking for damage . once the tubing is formed , the hub 122 is formed about the proximal end of the tubing as described above . extension tubes 124 , 126 , and 128 , clamps 130 , 132 , and 134 , and luer connectors 142 , 144 , and 146 are then added as described above . the polyester cuff 120 is then placed around the tubing 112 . finally , if the catheter 110 is to have a tip , the tip is formed in a conventional manner . on the other hand , if the catheter has a blunt tip as described above , then at some time prior to use a portion of the distal end of the arterial lumen 118 is cut away to expose the arterial lumen at a point upstream of the venous lumen 116 to prevent mixing of the treated and untreated blood . the catheter 110 is then ready for insertion into the patient . as noted above , the lumens of the catheter 110 of the invention have been designed to have equal or better flows to the known triple lumen critical care catheters without sacrificing the structural integrity of the catheter . it has been discovered that equal or greater flow characteristics could be obtained without the outer walls of the catheter collapsing during use by making the catheter lumens smooth in profile ( i . e ., circular or ellipsoidal ) and by providing unbalanced lumen areas . in particular , it has been found that by allowing the arterial lumen to have a 10 - 30 % size advantage over the venous lumen that lower pressures and vacuums could be achieved at higher flow rates , as depicted in tables 1 and 2 . those skilled in the art will appreciate that there is a limit to the size of the lumens within a given outer diameter of the catheter because the outer walls will become too thin to extrude and the lumens will be prone to collapse . during extrusion , the wall thickness and consistency is the most difficult variable to control . as the walls become too thick , a lack of lumen area exists , while as the walls become too thin , the rubber has more difficulty filling the wall area , which leads to unfilled portions of the wall . on the other hand , the wall may be thin in one area and thick in another . in fact , for the 13 french size tested to provide the data in table 2 , it was not possible with the given machinery to extrude the tubing of the &# 34 ; longhorn &# 34 ; catheter with lumens any larger than approximately 0 . 00327 square inch in cross - section because as the lumen sizes were increased the outer walls of the catheter became too thin to extrude . by contrast , the geometry of the design of fig1 and 12 permitted extrusion of tubing with greater internal lumen cross - sectional areas without compromising the wall structure . as reflected in tables 1 and 2 , the larger cross - sectional areas and smoother contours of the lumens of the design of the invention permitted greater flow rates to be achieved for a given outer diameter . thus , the catheter of the invention provides suitable flow rates for hemodialysis and other critical care uses by providing unique geometries and size relationships between the venous and arterial lumens . such designs are counter to the conventional wisdom which suggests that maximum flow rates are achieved by strictly maximizing the cross - sectional area of each lumen within the catheter with less regard for geometry . the catheter 110 of the invention is thus believed to provide a substantial unanticipated improvement in flow rates for triple lumen catheters of a particular french size . it will be appreciated by those skilled in the art that the foregoing has set forth the presently preferred embodiments of the invention but that numerous alternative embodiments are possible without departing from the novel teachings and advantages of the invention . for example , the venous lumen 116 may also have an ellipsoidal cross - section so long as the size relationship with the arterial lumen 118 is maintained . accordingly , all such modifications are intended to be included within the scope of the appended claims .
a multi - lumen intravenous catheter for use in treating a patient &# 39 ; s blood comprising an elongated cylindrical tube with at least first , second and third lumens formed inside . the first lumen is adapted to accept a guide wire for guiding the catheter during insertion into a blood vessel of the patient or therapeutics for introduction into the patient &# 39 ; s bloodstream . the second lumen is adapted to return treated blood to the patient &# 39 ; s blood vessel and has a smooth , circular or ellipsoidal cross - section . the third lumen is adapted to extract blood from the patient &# 39 ; s blood vessel for treatment and has a substantially elliptical or football - shaped cross - section and a cross - sectional area which is 10 to 30 percent larger than a cross - sectional area of the second lumen . despite such unbalanced cross - sections , the second and third lumens have substantially equal blood flow rates during treatment of the patient &# 39 ; s blood . also , the intake and return flow rates are improved for a given cross - sectional area of the catheter while the hydrostatic pressures within the lumens stay within maximum acceptable hydrostatic pressure limits for the patient .