a stent or catheter or composite of the structural hydrogel and a metal , plastic or other component , and process for producing the same is illustrated herein . the finished device as disclosed is comprised of 100 % hydrogel polymer which is stable and structural in its final composition , not requiring a substrate or scaffold to maintain composition or mechanical characteristics . referring now to the drawings , particularly in fig1 , there is generally indicated the stent of the present invention . as illustrated in fig1 , the body of the stent 1 is displayed , along with the uretral lumen 3 and the outward radial forces 2 . the trumpet or barbell distal end for anchorage with radiopacifier fill 4 is also shown . in fig2 , the path urine travels through the body is shown . how the urine 5 will flow from the kidney , 6 through the anchorage in the kidney , 8 through the ureter , 7 through the anchorage of the ureter 9 and into the bladder 10 . the urine will then flow 12 through the urethra 11 . fig3 displays the process of making the hydrogel stent . in step 1 , the composition of the hydrogel 13 that is desired is passed through the syringe body or reservoir 14 and subsequently through a needle 16 to form the first layer 17 which will be held in place by the mandrel 15 . in step 2 , the process is repeated to form the second layer 20 around the first layer 19 and both held in place by the mandrel . fig4 a the front view of the stent producing process . the adjustable process parameters of temperature , pressure and viscosity 21 and a reservoir of hydrogel in solvent solution 23 then the variable of process parameter flow rate 22 . this will then go through the manifold outlet diameter 24 that allows for stents of various diameters to be created . the length of the stent can also be varied by the distance deposition filament 26 . the mandrel rpm or line speed 25 can be varied and multiple stents can be received by the multiple mandrels 27 . fig4 b shows the side view of the stent producing process . the reservoir of material 28 goes through the outlet id 30 which travels through a set distance 29 of the length of stent where a lead dimension is set 31 . the mandrel 32 will hold a set deposition thickness 35 while rotating a set rpm 33 and coming out of the process at a certain line speed 34 . fig4 c shows the end view of the stent producing process with reservoirs of material a 36 and material b 37 . these two materials then flow through the flow direction valve 38 . a mandrel 39 then holds in place where the deposition 40 will come from . fig4 d shows a side view from the opposite side of 4 b shows the reservoir of material 41 with a material a 42 and material b 43 that make up the inner layer of the stent 44 . fig5 a shows how the second layer will be attached to the first with a mandrel dimension a 45 holding in place the subsequent outer layer 46 around the inner layer 47 with a variable mandrel length 48 and a mandrel dimension b 49 . fig5 b shows the two step process of how the mandrel holds the structure of the stent as it comes through . in step 1 , the variable mandrel diameter 53 with a deposit layer on the mandrel 50 is then dehydrated 51 onto a mandrel 88 . the second step to create a smaller diameter stent is shown in step 2 with a smaller mandrel 54 with a smaller dehydrated stent 52 . fig6 is a graph depicting how much the stent can stretch based on the weight of the load applied to it . fig7 a shows a view of what the end of a finished structural hydrogel device 55 would look like with an embedded weave composition 56 of the final stent . fig7 b shows a cross section of the finished stent with an inner layer 58 , an outer layer 57 a coil form 59 and a hydrogel tip 60 . the flow of fluid through the stent is also shown 61 . fig7 c shows the same cross section with a variable diameter of both the inner layer 63 and the outer layer 62 with the same outward flow 64 . fig7 d shows how a catheter or stent can possibly be filled with medication that will flow into the bloodstream when the bloodstream has a lower concentration than the catheter or stent . the potential inflation of the outer layer 67 of the catheter shaft 66 of a low profile integral balloon 68 is displayed . fig7 e shows a more detailed side view of the potential expansion for drug refilling purposes . the optional inflation 69 with a thin wall of the balloon 70 with an optional drug reservoir 72 is shown more clearly . fig7 f shows an end view of what the catheter or stent will look like when expanded . the increased diameter of the stent 71 with the force that is exerted outwards by the fluid flowing through 73 is displayed . fig7 g shows what the ends of the devices will look like if expanded . a solid core 74 with multiple layers of radiopaque filled hydrogel forming a tip 75 with the layers required by the process 76 . a potential adhesive 77 could also be implemented . fig8 a shows three potential configurations of a 78 , b , 79 and c 80 . these configurations depict different potential forces that may be applied depending on the volume and amount of flow of liquid through the device . fig8 b shows how drugs may be delivered through diffusion 81 if that option is pursued . fig9 a shows an interior cross sectional view of the final device while fig9 b shows what the outside of the final device will look like . fig1 shows the variable diameters of the outer layer with the interior diameter 83 and exterior diameter 84 when the device is fully hydrated 86 . the same is shown for the inner layer with the interior diameter 85 and the exterior diameter 84 when the device is fully hydrated 87 . in the preferred embodiment , a physician skilled in the ability can be expected to implant and retrieve a structural hydrogel device in the same manner as a thermoplastic device . a structural hydrogel ureteral stent or catheter can be implanted trans - uretheraly or percutaneously from the kidney into the ureter considerably smaller in diameter and once wetted immediately lubricous while hydrating , and increasing in corresponding volume . this instant process ideally can be used to fabricate an entity , device or product which exhibits a reversible function , ideally infinitely where the material can be dehydrated and re - hydrated as required . in that sense , the primary mechanism of the process is that the first or inner layer material is deposited fully hydrated and then subsequently dehydrated as a part of the process , see step ( 1 ) fig3 , fig4 a & amp ; b . then a sequential layer is added whereby the solvent in the second layer solution that allows the hydrogel to be in a semi - liquid phase will interact with the dehydrated first or inner layer beneath and a covalent interface will be achieved , see step ( 2 ) fig3 , fig4 a & amp ; b . this material defined as a hydrogel , is in its semi - fluid phase before solidification , and used as a raw material in the disclosed process . furthermore different concentrations of solids or fillers in the hydrogel material can be deposited by for example controlling several reservoirs flowing into one manifold with one unique outlet , see fig4 c & amp ; d . additionally , mandrels used for initial processing , may be removed to create additional effects . for example a larger od mandrel will result in a thinner dehydrated wall when preparing for a concurrent layer . similarly , a smaller od mandrel , no mandrel or a combination of diameters could be used for additional desired effects , see fig5 a & amp ; b . conversely , the disclosed ( reversible dehydration / hydration lamination ) process provides a novel advantageous alternative when designing or fabricating products made from raw materials such as hydrolyzed pan type materials that need to exhibit excellent mechanical characteristics while maintaining low percent solids , see fig6 . one of the most valuable attributes of the disclosed process allows processing from solvent - based hydrogel solutions that result in a structural hydrogel device exceeding the performance of coagulated hydrolyzed pan products and components . therefore the disclosed process exceeds the limitation of materials such as hydrolyzed pan but also includes any formulation that exhibits a reversible function whereby the material can be dehydrated and re - hydrated . in that manner , the disclosed process allows the layering and or lamination of layers in accordance with the disclosed process resulting in a laminated structural hydrogel of predominately low solids and high corresponding aqueous content that will exhibit significant mechanical characteristics such that a stable product can be produced . subsequently , this novel process allows the lamination of subsequent concurrent layers that in a final configuration provide the enhanced mechanical characteristics that result in 100 % structural hydrogel products as well as hybrid versions , see fig7 a , b , c , d , e , f & amp ; g . although one primary advantage of the disclosed process is the ability to adhere one hydrogel layer to another hydrogel layer or other surface material , and that the lamination of such layers together results in and benefit from the compression of the outer layers or at least the integration of the outer layer to the associated inner layer ; one can incorporate or produce a hybrid by for example incorporating a braid or fabric between layers , see fig7 a . therefore the disclosed process results in the revolutionary never before claim of adhering one hydrogel layer to another hydrogel layer , which as disclosed is the primary influence resulting in the superior mechanical and biocompatibility performance characteristics of the as called structural hydrogel product or device . a hybrid device for example utilizing a structural hydrogel distal tip manufactured in accordance with the disclosed process , and adhered to or processed directly onto a conventional metal , tpe / tpu device surface , such as for example a catheter where the hydrogel is not a coating but an integral component , see fig7 b & amp ; c could diminish complications related to implantation . furthermore , a hybrid device utilizing a structural hydrogel design manufactured in accordance with the disclosed process can be engineered with different percent concentrations of solids in a specific layer , or segmented or positioned specifically along the axis of a catheter shaft for example . in this manner radiopaque media can be placed where it is desired , or a denser matrix can be produced in specific layers or segment along the axis , providing a differential gradient that would promote diffusion or conduction enhancing drainage , or providing a specific drug delivery barrier , see fig8 a & amp ; b . otherwise , current processing of hydrolyzed pan and alike hydrogels is limited to only primarily coagulation of freely poured or molded gel , typically into a sheet form where further processed including secondary operations that include many methods of cross - lonking such as exposure to radiation , freeze / thaw methods , and modifications to the polymer chemistry , as well as using hot acid to enhance its hydrophylicity and or primers that are required to attach coatings to an intended substrate . this dangerous , expensive and marginally successful operation is not required with the disclosed process which produces a low solids and therefore correspondingly highly hydrophilic product . thermoplastic extrusion processes are possible with many hydrogel formulae , in order to make them perform like conventional tpe and tpu &# 39 ; s . although thermoplastic extrusion typically results in components and products that exhibit adequate mechanical characteristics , thermoplastic extrusion of for example hydrolyzed pan does not yield a component or product that exhibits a large aqueous content compared to product manufactured from the disclosed process . furthermore , for example extruding hydrolyzed pan requires loading the polymer resin with large amounts of plasticizers , and when radiopacifers are added the end product contains a much higher percent of solid than exhibited by products manufactured with the disclosed process , diminishing the hydrophilicity , and bio - compatibility . the advantages therefore are that the disclosed process which doesn &# 39 ; t require thermoplastic processing ( although it can be extruded or molded ); doesn &# 39 ; t require post processing to enhance hydrophylicity , and isn &# 39 ; t sensitive to variations in the base polymer chemistry can be used to cost effectively derive products which will exhibit a much higher level of aqueous absorption and related bio - compatibility which is paramount and related while exhibiting the required mechanical characteristics , which if not achieved , the device or product application wouldn &# 39 ; t be possible . to achieve this bio - compatibility and in accordance with the benefits of the disclosed process a catheter for example might be produced with several layers whereby the last layer is void of but all previous layers would be filled with radiopacifiers , see fig9 . in this manner human tissue does not come into contact with the radiopaque filler medias as would devices produced of or conventional hydrogels , tpe or tpu &# 39 ; s . also drug delivery systems and attempts to force the change in volume resulting in for example predetermined radial forces can be exhibited by adding or not adding fillers or generally the specification of the percent of hydrogel solids in a given layer or layers as illustrated in fig8 .
the present invention relates generally a manufacturing process which results in a completely hydrogel polymer device that maintains lumen patency which allows for numerous applications . catheters and stents are particular examples , and their composition , mechanical characteristics , and the significantly unique ability to conduct and allow fluids to pass from one end to the other without physiological rejection , inflammation , or manifestation of complications due to implant or otherwise undesirable outcomes when used for ambulatory and or therapeutic interventions is the purpose of the invention .