of its usable life it is slowly absorbed into the surrounding tissues and metabolized via the tricarboxylic acid cycle and is excreted as carbon dioxide and water if the stent 10 14 23 remains uncovered by urothelium it will slowly disintegrate and be excreted in the urine flow in the first embodiment the stent 10 14 is a tubular shaped member having first and second ends 17 18 17 u2032 18 u2032 and a walled surface 19 19 u2032 disposed between the first and second ends 17 18 17 u2032 18 u2032 the walls are composed of extruded polymer monofilaments woven into a braid like embodiment in the second embodiment the stent 23 is injection molded or extruded fenestrations 24 are molded laser cut die cut or machined in the wall of the tube the stent 10 14 23 is provided as a sterile device that is compressed to a first diameter of between approximately 6 mm to 10 mm and inserted into a reusable delivery tool not shown in the operating room immediately before implantation once the stent 10 14 23 is deployed it self expands outwardly to a variable second diameter conforming to the lumen the size of the lumen together with the elasticity and circumferential pressure of the surrounding tissues determine the stent 39 s final nominal diameter the stents 39 non compressed or resting state diameter is between approximately 12 mm to 18 mm the method for formulation of the stent 10 14 will now be described fig4 the plla and pcl polymers are first dry blended 25 under an inert atmosphere then extruded in a rod form 26 in a preferred embodiment of the present invention granules of plla and pcl are dry blended with a plla pcl ratio.