with reference to fig1 and 2 , a living human host patient 10 with an open chest is shown in fragmentary front elevational view , and with parts of the patient &# 39 ; s anatomy shown in phantom or removed solely for better illustration of the salient features of the present invention . surgically implanted into the patient is the pumping portion 20 of a ventricular assist device , generally referenced with the numeral 30 . ventricular assist device 30 includes an inflow conduit 40 which further includes a substantially non - porous conduit 50 for communicating blood from the patient &# 39 ; s left ventricle into the pumping portion 20 . as shown in fig2 , conduit 50 comprises a flexible , porous tubular substrate to which a substantially non - porous thermoplastic elastomer is substantially non - delaminably bonded in accordance with a method of the invention . an end of inflow conduit 40 is connected to the patient &# 39 ; s heart by sutures so that blood flow communication is established and maintained . fig3 illustrates another embodiment of the invention , comprising a non - delaminable kink - resistive conduit 208 having a first end 216 , a second end 218 , and a middle portion 214 , for use as an inflow conduit of a ventricular assist device . in one embodiment , the tubular wall 210 comprises a substantially porous ptfe tubular substrate with a layer of fep wrapped around it and substantially non - delaminably bonded thereto by a method of the invention . as will be described , the material and construction of conduit 208 is sufficiently flexible while at the same time being sufficiently able to withstand collapse . a plurality of external reinforcing members 212 comprises a series of coils of a continuous rib having a circular or semi - circular cross - section projecting outward from the fep layer . the reinforcement coils 212 extend generally between first end 216 and second end 218 and are preferably axially spaced apart in middle portion 214 while being more tightly spaced ( even in contact ) at ends 216 , and 218 . the loosely spaced middle portion 214 permits conduit 208 to bend , and the tightly spaced regions 216 , and 218 , provide rigidity in the areas adjacent associated coupling structures . this helps the surgeon in connecting conduit in its proper place . another function of external reinforcing members 212 is to provide “ burst strength ” ( also called “ hoop strength ”) to the conduit . burst strength and hoop strength refer to the ability of the conduit to withstand the force of internal pressure , which is a product of the action of the ventricle and the mechanical pump . the external reinforcing members provide a binding that acts to increase the burst strength . the ptfe tubular substrate may be formed by various means well known in the art , such as , for example , extrusion followed by expansion . external reinforcement members 212 may be formed by various means well known in the art , such as , for example , extrusion . in a particularly preferred embodiment , reinforcement members 212 preferably comprise a monofilament helically wrapped around tubular wall 210 and non - delaminably bonded thereto . the present invention is directed to a method of substantially non - delaminably bonding a substantially non - porous thermoplastic elastomer to a substrate that can be used for the production of valuable products , including non - thrombogenic products . the method comprises the steps of selecting a substantially non - porous thermoplastic elastomer having a melting point substantially below the melting point of the substrate , forming a bilayer comprising a layer of the selected thermoplastic elastomer in contact with a layer of the substrate , heating the bilayer to a predetermined temperature near the melting point of the thermoplastic elastomer but substantially below the melting point of the substrate , maintaining the bilayer at the predetermined temperature for a predetermined period of time , and , allowing the heated bilayer to cool to ambient temperature , whereby the thermoplastic elastomer is substantially non - delaminably bonded to the substrate . the selected thermoplastic elastomer may be a biocompatible polymer . the substrate may be porous or non - porous — for example non - porous eptfe . nonthrombogenic products may be obtained using the method . additional examples of substrates that can be used in connection with the method include eptfe having an internodular distance up to about 300 . mu ., eptfe having an internodular distance up to about 200 . mu ., eptfe having an internodular distance up to about 100 . mu ., eptfe having an internodular distance up to about 50 . mu ., and eptfe having an internodular distance up to about 5 . mu . when the method is applied to substantially porous ptfe , the product obtained may be non - thrombogenic . the selected thermoplastic elastomer may be biocompatible polymer , for example fep . the temperature and times employed in the process are a function of the melting points of the substrate and the thermoplastic elastomer . the inventor believes , but is not certain , that the success of the process in affording a non - delaminable bond rests on the ability of the thermoplastic elastomer to “ wet ” the surface of the substrate . the inventor believes , but is not certain , that this “ wetting ” is one of the factors that makes it possible to form short range van der waals attractive forces to produce adhesion between the surfaces of the elastomer and the substrate . in addition , the inventor believes , but is not certain , that the thermoplastic sealant flows into any existing porosity in the substrate to create a non - delaminable bond . to make both of these phenomena possible , it is necessary for the elastomer to become sufficiently mobile to undertake the “ wetting ” and flowing processes . thus , the elastomer must be heated to a predetermined temperature near its melting point , but substantially below the melting point of the substrate . in the case involving porous ptfe as substrate and fep as thermoplastic elastomer , the porous ptfe has a melting point substantially in the range of 325 . degree . c . to 343 . degree . c . by contrast , the fep has a melting point substantially in the range of 240 . degree . c . to 290 . degree . c . here , the predetermined temperature for the process is between at least about 260 . degree . c . and about 300 . degree . c . more preferably , the predetermined temperature for the process is between at least about 275 . degree . c . and about 285 . degree . c . furthermore , in this case the predetermined time for heating at this temperature is between at least about 10 minutes and about 30 minutes . more preferably , in this case the predetermined time for heating at this temperature is between at least about 15 minutes and about 25 minutes . the substantially non - porous thermoplastic elastomer substantially non - delaminably bonded to the flexible porous tubular substrate in accordance with the method of the invention can be used in a substantially non - porous conduit which comprises a flexible , porous tubular substrate having a first end , a second end , and a middle portion wherein the porous tubular substrate may be made of a biocompatible polymer such as ptfe . the ptfe may be closed structured to resist tissue ingrowth from the exterior of the tubular substrate . in various embodiments , the ptfe further may have a pore size of less than about 20 . mu ., less than about 15 . mu ., or less than about 2 . mu . in this conduit , the water entry pressure for the tubular substrate may be at least about 5 psi ( 0 . 34 atm ). in various embodiments of the conduit , the elastomer may be fep , and the substrate may be made of at least one polymer selected from the group consisting of ptfe , fep , pfa ( perfluoroalkoxy ), pps , pvdf ( polyvinylidene fluoride ), peek , ps / pes , pctfe , and etfe . in further embodiments , the elastomer may be a extruded or skived non - porous tape made from ptfe , fep , pfa ( perfluoroalkoxy ), pps , pvdf ( polyvinylidene fluoride ), peek , ps / pes , pctfe , and etfe , vinylidene polymer plastics , polyethylene , polypropylene , polyesters , polyamides , polyethylene terephthalate , high density polyethylene , irradiated polyethylene , polycarbonates , polyurethanes , polyvinyl chloride , polyester copolymers and polyolefin copolymers . the invention also teaches a method for providing a substantially non - delaminable external kink - resistive supporting structure for the conduit comprising the steps of selecting a thermoplastic polymer monofilament having a melting point up to about the melting point of the elastomer , helically winding the filament around the conduit to form a supported conduit , heating the supported conduit to a predetermined temperature up to about the melting point of the thermoplastic elastomer , maintaining the supported conduit at the predetermined temperature for a predetermined period of time , and , allowing the heated supported structure to cool to ambient temperature . a kink - resistive conduit produced in accordance with the method is shown in fig3 . the polymer monofilament may be a polypropylene , ptfe , or fep monofilament . in a further embodiment of the method , the filament is helically wound around the conduit , wherein the helical winding is wound more tightly at the first end and second ends than in the middle of the conduit , to form a supported conduit as shown in fig3 . in this embodiment , likewise , the polymer monofilament may be a polypropylene , ptfe , or fep monofilament . the substantially non - porous conduits of the invention may be used to form an inflow conduit for an implantable ventricular assist device comprising , in combination the substantially non - porous conduit , wherein the substantially non - porous conduit has a substantially smooth inner surface for enhanced flow - through of blood with a minimum of surface - induced turbulence , a ventricular attachment structure to which said first end of said substantially non - porous conduit connects , and a coupling fitting on the second end of the substantially non - porous conduit . such a conduit may be used to form an implantable ventricular assist device in combination with an implantable pumping portion in flow communication with the inflow conduit , and an outflow conduit in flow communication with the pumping portion . a method for the treatment of congestive heart failure comprises implanting the implantable ventricular assist device described in the foregoing paragraph in a patient in need of such treatment wherein said implantation is effective to ameliorate one or more of the symptoms of the heart failure . the implantable ventricular assist device may be packaged in the packaging material , wherein the device is effective for implantation in a patient afflicted with congestive heart failure , and the packaging material includes a label that indicates that the device is effective for such implantation . still another embodiment of a substantially non - delaminable kink - resistive conduit , is made by selecting a flexible , porous tubular substrate having a first end , a second end , and a middle portion ; selecting a thermoplastic polymer monofilament having a melting point up to about the melting point of the tubular substrate ; winding the filament around the middle portion of the substrate to form a supported substrate ; heating the supported substrate to a first predetermined temperature up to about the melting point of the thermoplastic polymer ; maintaining the supported substrate at the first predetermined temperature for a first predetermined period of time ; allowing the heated supported substrate to cool to ambient temperature ; selecting a substantially non - porous thermoplastic elastomer having a melting point substantially below the melting point of the substrate ; wrapping a layer of the selected thermoplastic elastomer around the cooled supported substrate to form a wrapped supported substrate ; heating the wrapped supported substrate to a second predetermined temperature near the melting point of the thermoplastic elastomer but substantially below the melting point of the substrate ; maintaining the wrapped supported substrate at the second predetermined temperature for a second predetermined period of time ; and , allowing the heated wrapped supported substrate to cool to ambient temperature ; whereby the thermoplastic polymer , the thermoplastic elastomer , and the substrate are substantially non - delaminably bonded to form a substantially non - delaminable kink - resistive conduit . a further embodiment comprises products and a method to make them , comprising forming a supported conduit that is substantially non - delaminable and substantially non - porous . the method involves the steps of selecting a flexible , porous taenoid substrate and a taenoid substantially non - porous thermoplastic elastomer having a melting point substantially below the melting point of the taenoid porous substrate . a taenoid bilayer comprising a layer of the taenoid thermoplastic elastomer in contact with a layer of the taenoid porous substrate is formed and heated to a first predetermined temperature near the melting point of the taenoid thermoplastic elastomer but substantially below the melting point of the taenoid porous substrate and maintaining the bilayer at that temperature for a first predetermined period of time . the bilayer is allowed to cool to ambient temperature to afford a non - delaminable taenoid bilayer which is helically wound around a tubular substrate in a manner whereby the taenoid thermoplastic elastomer layer is in contact with the tubular substrate to form a wound substrate . the purpose of the taenoid bilayer is to impart burst strength to the product of the method . the flexible tubular substrate may be a woven substrate , or an eptfe having an internodular distance up to about 300 . mu . it may be porous or not , but is desirably non - thrombogenic . the thermoplastic non - porous polymer used in the invention is advantageously fep , but other such polymers may be suitable . the wound substrate is heated to a second predetermined temperature up to about the melting point of the taenoid thermoplastic polymer , and maintained for a second predetermined period of time . the heating may be carried out by keeping the tubular substrate on a mandrel heated by resistance wires , infrared heating , or the like heating means . likewise , the mandrel may additionally be provided with cooling means , for example internal passages for refrigerant liquids , as a resource for any required cooling . the heated wound substrate is allowed to cool to ambient temperature , and a substantially non - porous thermoplastic elastomer having a melting point substantially below the melting point of the tubular substrate is wrapped around the cooled supported substrate to form a wrapped substrate . the latter is heated to a third predetermined temperature up to about the second predetermined temperature of the method and maintained there for a third predetermined period of time . the resulting wrapped substrate is allowed to cool to ambient temperature . a thermoplastic polymer monofilament is wound around the wrapped substrate to form a filamented substrate , which is heated to a fourth predetermined temperature up to about the second predetermined temperature and maintained there for a fourth predetermined period of time . after cooling , the tubular substrate , the taenoid bilayer , the thermoplastic polymer monofilament , and the thermoplastic elastomer are substantially non - delaminably bonded to form a substantially non - delaminable substantially non - porous supported conduit . the first predetermined temperature , the second predetermined temperature , the third predetermined temperature , and the fourth predetermined temperature may be each between at least about 260 . degree . c . and about 300 . degree . c ., more preferably between at least about 275 . degree . c . and about 295 . degree . c . the first predetermined time , the second predetermined time , the third predetermined time , and the fourth predetermined time may be each between at least about 10 minutes and about 30 minutes , and more preferably between at least about 15 minutes and about 25 minutes . the flexible tubular substrate may be made of a biocompatible polymer such as ptfe , which may be closed structured to resist tissue ingrowth from the exterior of the flexible tubular substrate . here , the ptfe may have a pore size of less than about 20 . mu . in fact , the flexible tubular substrate may be made of made of at least one polymer selected from the group consisting of ptfe , fep , pfa ( perfluoroalkoxy ), pps , pvdf ( polyvinylidene fluoride ), peek , ps / pes , pctfe , and etfe . the water entry pressure for the flexible tubular substrate may be at least about 5 psi ( 0 . 34 atm ). the porous taenoid substrate , the taenoid thermoplastic elastomer , the tubular substrate , the selected thermoplastic elastomer , and the filament may each be a biocompatible polymer — for example , the thermoplastic elastomer may be fep . the thermoplastic polymer monofilament may be a polypropylene , ptfe or fep or the like monofilament . 82 . an inflow conduit for an implantable ventricular assist device may be fabricated using a supported conduit having a substantially smooth inner surface for enhanced flow - through of blood with a minimum of surface - induced turbulence , attached at one end to a ventricular attachment structure and at the other to a coupling fitting . this may be used to construct an implantable ventricular assist device , further comprising an implantable pumping portion in flow communication with the inflow conduit ; and , an outflow conduit in flow communication with the pumping portion . the completed implantable ventricular assist device may be used for the treatment of congestive heart failure , by implantation of the device in a patient in need of such treatment , wherein the implantation is effective to ameliorate one or more of the symptoms of the heart failure . this device may be packaged together with a label that indicates that the device is effective for such implantation . thus it will be appreciated that the invention provides a new and improved inflow conduit for an implantable ventricular assist device . it should be understood , however , that the foregoing description of the invention is intended merely to be illustrative thereof and that other modifications in embodiments may be apparent to those skilled in the art without departing from its spirit . for example , whereas the invention has been illustrated in connection with an lvad , it may be used with other vad &# 39 ; s . additionally , although the illustrative embodiment has been described in connection with an improved ptfe inflow conduit for an implantable ventricular assist device , a properly supported knitted fabric inflow conduit , such as described in my u . s . pat . no . 6 , 001 , 056 could also be used . on this basis , the instant invention should be recognized as constituting progress in science and the useful arts , and as solving the problems in cardiology and medicine enumerated above . in the foregoing description , certain terms have been used for brevity , clearness and understanding , but no unnecessary limitation is to be implied therefrom beyond the requirements of the prior art , because such words are used for descriptive purposes herein and are intended to be broadly construed . having described preferred embodiments of the invention with reference to the accompanying drawings , it is to be understood that the invention is not limited to those precise embodiments , and that the various changes and modifications may be effected therein by one skilled in the art without departing from the scope or spirit of the invention as defined in the appended claims . for example , the product can have other shapes , or could make use of other plastics . thus , the scope of the invention should be determined by the appended claims and their legal equivalents , rather than by the examples given . all changes that come within the meaning and range of equivalency of the claims are to be embraced within their scope . unless defined otherwise , all technical and scientific terms used herein have the same meaning as is commonly understood by one of skill in the art to which this invention belongs . all patents and publications referred to herein are incorporated in their entirety by reference . all abbreviations for fluorocarbon polymers used herein have the same meaning as is commonly understood by one of skill in the art to which this invention belongs . as an example , ptfe refers to polytetrafluoroethylene . as a further example , fep refers to poly ( tetrafluoroethylene - co - hexafluoropropylene ). as further examples , the following fluorocarbon polymers are commercially available from fluorocarbon company limited , caxton hill , hertford sg13 7nh , uk : pfa ( perfluoroalkoxy ), pps , pvdf ( polyvinylidene fluoride ), peek , ps / pes , pctfe , and etfe . all terms for polymers used herein have the same meaning as is commonly understood by one of skill in the art to which this invention belongs . as an example , the terms “ resin ”, “ polymer ”, and “ elastomer ” may be used synonymously by one of skill in the art to which this invention belongs . all melting points and other physical constants for polymers and other substances as used herein have the same meaning and values as are commonly understood by one of skill in the art to which this invention belongs . for example , typical values for the melting points for the following fluorocarbon resins are : ptfe : 325 . degree . c . to 343 . degree . c . ; fep : 240 . degree . c . to 290 . degree . c . ; pfa : 302 . degree . c . to 310 . degree . c . ; etfe : 254 . degree . c . to 279 . degree . c . ; ctfe : 210 . degree . c . ; and : ectfe : 240 . degree . c . as used herein , a bilaminate structure is a structure comprising two layers . as used herein , a non - delaminable structure is a structure comprising at least two layers wherein the layers cannot be pulled apart or separated from each other without destroying the structural integrity of the individual layers . as used herein , the internodular distance in a sample of expanded ptfe is the mean distance between nodes in the material as seen under a microscope . the microscopic nodes in a sample of expanded ptfe are microscopic areas of condensed polymer . the nodes are separated from each other by microscopic strands of polymer . as used herein , a supported conduit is any tube - like structure incorporating reinforcement elements that act against the bursting and / or collapse of said conduit . as used herein , the term taenoid refers to a coiled , ribbon - like , tape - like , or band - like structure , such as a headband .
a method of non - delaminably bonding a non - porous thermoplastic elastomer to a substrate by heating a bilayer of the elastomer and the substrate for a predetermined time and a product obtained by the method . methods for producing non - delaminable conduits and non - delaminable kink - resistant conduits constructed of biocompatible elastomers and substrates , and products produced by these methods are taught . methods , products , and articles of manufacture relating to non - delaminable monofilament supported kink - resistive conduits that may be used as inflow conduits in left ventricular assist devices for treatment of heart failure are also provided .