Title of Invention: BIODEGRADABLE ENDOPROSTHESES AND METHODS FOR THEIR FABRICATION Abstract: The disclosure provides biodegradable implantable devices such as a stent comprising a biodegradable polymeric wherein the polymeric material is treated to control crystallinity and/or Tg. The stent is capable to expand at body temperature from a crimped configuration to a deployed diameter and have sufficient strength to support a body lumen. Detailed Description: CROSS-REFERENCE This application is a continuation of U.S. patent application Ser. No. 14/097,087, filed Dec. 4, 2013, which is a continuation of U.S. patent application Ser. No. 13/539,770, filed Jul. 2, 2012, which is a continuation application of U.S. patent application Ser. No. 13/536,957, filed Jun. 28, 2012, which is a continuation-in-part of U.S. patent application Ser. No. 13/473,354, filed May 16, 2012, which is in turn a continuation application of U.S. patent application Ser. No. 12/016,085, filed Jan. 17, 2008 and issued as U.S. Pat. No. 8,182,890 on May 22, 2012, which in turn claims the benefit of U.S. Provisional Application 60/885,700 filed on Jan. 19, 2007; U.S. patent application Ser. No. 13/536,957 is also a continuation-in-part of U.S. patent application Ser. No. 13/434,555, filed Mar. 29, 2012, which is a divisional application of U.S. patent application Ser. No. 12/016,085, filed Jan. 17, 2008 and issued as U.S. Pat. No. 8,182,890 on May 22, 2012, which in turn claims the benefit of U.S. Provisional Application 60/885,700 filed on Jan. 19, 2007; and U.S. patent application Ser. No. 13/536,957 is also a continuation-in-part of U.S. patent application Ser. No. 12/016,077, filed Jan. 17, 2008, which claims the benefit of U.S. Provisional Application 60/885,700, filed Jan. 19, 2007; U.S. patent application Ser. No. 13/536,957 also claims the benefit of U.S. Provisional Application 61/503,406, filed Jun. 30, 2011; U.S. Provisional Application 61/540,881, filed Sep. 29, 2011; U.S. Provisional Application 61/545,879, filed Oct. 11, 2011; U.S. Provisional Application 61/555,668, filed Nov. 4, 2011; U.S. Provisional Application 61/595,222, filed Feb. 6, 2012; and U.S. Provisional Application 61/645,956, filed May 11, 2012; the content of each of the above-referenced applications are incorporated herein by reference in their entirety. BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates generally to medical devices and methods for their fabrication. In particular, the present invention relates to the fabrication of biodegradable endoprostheses, such as stents, having enhanced strength and controlled persistence after implantation. Stents are generally tubular-shaped devices which function to hold open or reinforce a segment of a blood vessel or other body lumen, such as a coronary artery, carotid artery, saphenous vein graft, or femoral artery. They also are suitable to support and hold back a dissected arterial lining that could occlude the body lumen, to stabilize plaque, or to support bioprosthetic valves. Stents can be formed from various materials, particularly polymeric and/or metallic materials, and may be non-degradable, biodegradable, or be formed from both degradable and non-degradable components. Stents are typically delivered to the target area within the body lumen using a catheter. With balloon-expandable stents, the stent is mounted to a balloon catheter, navigated to the appropriate area, and the stent is expanded by inflating the balloon. A self-expanding stent is delivered to the target area and released, expanding to the required diameter to treat the disease. Stents may also elute various drugs and pharmacological agents. Of particular interest to the present invention, biodegradable stents and other endoprostheses are usually formed from polymers which degrade by hydrolysis and other reaction mechanisms in the vascular or other luminal environment over time. For these reasons, it would be desirable to provide improved endoprostheses and methods for their fabrication. 2. Description of the Background Art Heat annealing and other treatments of filaments and other components used in stents are described in U.S. Pat. Nos. 5,980,564, 6,245,103, and 6,626,939. Heat treatment of polymeric stent coatings is described in International Application No. PCT/US07/81996, which designates the United States. Biodegradable implantable devices and methods of making them are also described in commonly owned U.S. Provisional Patent Application No. 60/668,707, filed on Apr. 5, 2005; U.S. Provisional Patent Application No. 60/885,700, filed on Jan. 19, 2007; U.S. patent application Ser. No. 11/398,363, filed on Apr. 4, 2006; U.S. patent application Ser. No. 12/016,077, filed on Jan. 17, 2008; and U.S. patent application Ser. No. 12/016,085, filed on Jan. 17, 2008, the entire disclosure of each of which is incorporated herein by reference. SUMMARY OF THE INVENTION In an aspect of the invention, improved biodegradable endoprostheses and methods for their fabrication are provided. The stent prostheses may be formed from one or more amorphous, semi-crystalline, or crystalline biodegradable polymers. The use of amorphous polymers is preferable in some cases since they can provide relatively short periods of biodegradation, usually less than two years, often less than one year, frequently less than nine months, and sometimes shorter than six months, or even shorter. In some embodiments of the invention, the polymers are modified or treated to introduce a desired degree of crystallinity. In other embodiments, introducing crystallinity into the polymer increases the strength of the polymer so that it is suitable for use as an endoprosthesis and in some cases without substantially lengthening the period of biodegradation after implantation. In other embodiments, the polymeric material is treated to achieve a desired degree of crystallinity. In other embodiments, the polymeric material is treated to control crystallinity. In an embodiment, treatment comprises a heat treatment of the polymeric material or the tubular body preferably at an initial diameter to a temperature above its glass transition temperature of the polymeric material and below its melting point for a period ranging from a fraction of a second to 7 days. Initial diameter is the diameter of the polymeric material or the tubular body as-formed, or the diameter before patterning, or the diameter after patterning, or the diameter before crimping. The polymeric material or the tubular body in one embodiment may be cooled after heating to a temperature ranging from below ambient temperature to ambient or above temperature over a period ranging from a fraction of a second to 7 days. In a preferred embodiment, the tubular body or polymeric material initial diameter is approximately 1-1.5 times the stent deployment diameter. In one embodiment, the tubular body is treated at diameter below initial diameter, or between initial diameter and crimped diameter. In a further embodiment, the treatment comprises heating the tubular body to a temperature about or below Tg for a period ranging from a fraction of a second to 7 days. In another embodiment, the heat treatment at the below initial diameter comprises heat treatment about or above Tg and below Tm for a period ranging from a fraction of a second to 5 hours, or preferably less than 2 hour, or more preferably less than 60 minutes, or most preferably less than 15 minutes. In another embodiment, the polymeric material or the tubular body after forming is treated comprising heat at temperature about or less than Tg. In another embodiment, the tubular body after forming and excluding patterning is treated comprising heat at temperature about or less than Tg. Durations are similar to above ranges. Other suitable temperatures and times are described herein. In another embodiment, the initial diameter is 0.9-1.5 times the stent deployment diameter, or the stent nominal diameter. The stent nominal diameter is the labeled deployment stent diameter. The stent deployment diameter usually is the deployed diameter of the stent at nominal or bigger diameter. In another embodiment, the initial diameter is smaller than the deployed stent diameter or smaller than the labeled stent deployed diameter. In one embodiment, the stent prosthesis after deployment from a crimped configuration to an expanded diameter in physiologic environment further expands to a larger diameter. In another embodiment, the stent prosthesis after deployment from a crimped configuration to an expanded diameter in physiologic environment further expands to a larger diameter by at least 0.05 mm within 20 minutes. In another embodiment, the stent prosthesis after deployment from a crimped configuration to an expanded diameter in physiologic environment further expands to a larger diameter by at least 0.1 mm within 20 minutes. In another embodiment, the stent prosthesis after deployment from a crimped configuration to an expanded diameter in physiologic environment further expands to a larger diameter substantially apposing the body lumen. The stent prosthesis after deployment from a crimped configuration to an expanded diameter in physiologic environment further expands to a larger diameter substantially apposing the body lumen within 9 months. In another embodiment, the at least some of the struts of the stent prosthesis after deployment from a crimped configuration to an expanded diameter in physiologic environment further expands to a larger diameter substantially apposing the body lumen. In some embodiments, the optional heat treatment of the one or more biodegradable polymeric materials, or the tubular body, the stent material, or the stent may occur at a temperature below Tg, or at about Tg, or at greater than Tg of the one or more biodegradable polymeric materials. In some embodiments, the optional heating may take place at a temperature within 2° C., or within 4° C., or within 6° C., or within 8° C., or within 10° C., or within 12° C., or within 14° C., or within 16° C., or within 18° C., or within 20° C. of Tg of the one or more biodegradable polymeric materials (where “within” may be above or below the Tg). In some embodiments the optional treating, such as heating, may take place for at least about 1×10−12 seconds (s), or at least about 1×10−9 s, or at least about 1×10−6 s, or at least about 1×10−3 s, or at least about 1×10−2 s, or at least about 0.1 s, or at least about 1 s, or at least about 10 s, or at least about 1 minute (min), or at least about 10 min, or at least about 1 hour (h) or at least about 10 h, or at least about 1 day, or at least about 5 days, or at least about 10 days, or at least about 1 month, or at least about 2 months, or at least about 3 months, or at least about 4 months, or at least about 5 months, or at least about 6 months, or at least about 1 year. In some cases, the treating, such as heating, may take place for about 1 min to about 10 min, or about 3 min to about 10 min, or about 5 min to about 10 min, or about 3 min to about 10 min, or about 30 seconds to about 24 hours. In some embodiments, the polymers' crystallinity after modification or treatment is increased by at least 10% of the original crystallinity of the polymer material, preferably by at least 20% of the original crystallinity of the polymer material, preferably by at least 50% of the original crystallinity of the polymer material, and more preferably by at least 100% of the original crystallinity of the polymer material. In other embodiments, the crystallinity of the polymeric material after modification is decreased by at least 10% of the original crystallinity of the polymer material before modification, preferably by at least 20% of the original crystallinity of the polymer material, preferably by at least 50% of the original crystallinity of the polymer material, and more preferably by at least 100% of the original crystallinity of the polymer material, and more preferably by at least 1000% of the original crystallinity of the polymer material. In other embodiments, treatment or modification of the polymeric material has crystallinity that is substantially the same after treatment and before treatment of the polymeric material. In preferred embodiments, polymer materials will have a crystallinity in the range from 10% to 20% after modification as described herein below. In yet other preferred embodiments, polymer materials will have a crystallinity in the range from 1 to 10%, or 10% to 30% after modification. In yet other preferred embodiments, polymer materials will have a crystallinity between 1% and 35% after modification. In yet other preferred embodiments, polymer materials will have a crystallinity between 1% and 40% after modification. As used herein and as known to skilled in the art, “crystallinity” refers to a degree of structural order or perfection within a polymer matrix as known to someone skilled in the art and methods to measure crystallinity as well such as differential scanning calorimetry. In some embodiments, the one or more materials comprising the body, or the stent, or the tubular body may have a controlled crystallinity. In some embodiments, the crystallinity is less than 50%, or less than 40%, or less than 35%, or less than 30%, or less than 25%, or less than 20%, or less than 15%, or less than 10%, or less than 5%. In some embodiments, the one or more materials comprising the body, or the stent, or the tubular body, or the polymeric material may have a crystallinity of about 0% or greater than 0%, or greater than 5%, or greater than 10%, or greater than about 15%, or greater than about 20%, or greater than about 25%, or greater than about 30%, or greater than about 35%, or greater than 40%, or greater than 50%. In some embodiments, the one or more materials comprising the body, or the stent, or the tubular body may have a crystallinity of about 0% to less than 60%, or about 0 to less than 55%, or about 0 to less than 50%, or about 0 to less than 40%, or about 0% to less than 35%, or about 0% to less than 30%, or about 0% to less than 25%, or about 0% to less than 20%, or about 0% to less than 15%, or about 0% to less than 10%, or about 0% to less than 5%. In some embodiments, the one or more materials comprising the body, or the stent, or the tubular body or polymeric material may have a crystallinity of about 5% to about 60%, or about 5% to about 55%, or about 5% to about 50%, or about 5% to about 40%, or about 5% to about 45%, or about 5% to about 30%, or about 10% to about 25%, or about 15% to about 20%. In some embodiments, the polymer or polymeric material after treatment is amorphous, in other embodiments the polymer or polymeric material after treatment is semi-crystalline, yet in other embodiments the polymer or polymeric material after treatment is crystalline. In a preferred embodiment, the polymeric material prior to a treatment is amorphous. In other embodiments, the polymeric material prior to a treatment is semi-crystalline. In a further embodiment, the polymeric material prior to a treatment is crystalline. Crystallinity can be measured by differential scanning calorimetry (Reading, M. et al, Measurement of crystallinity in polymers using modulated temperature differential scanning calorimetry, in Material Characterization by Dynamic and Modulated Thermal Analytical Techniques, ASTM STP 1402, Riga, A. T. et al. Ed, (2001) pp. 17-31. In another aspect of the invention, methods for fabricating biodegradable prostheses are provided. The preferred methods comprise providing a tubular body having an initial diameter as-formed, or before patterning, or after patterning, where the tubular body comprises a biodegradable polymeric material. In one embodiment, the polymeric material comprises one or more polymers, or one or more co-polymers, or a combination thereof. In another embodiment, the polymeric material comprises one or more polymers, or one or more co-polymers, or one or more monomers, or a combination thereof. The polymeric material or the tubular body is treated to control crystallinity preferably to between 1% and 50%, or more preferably to between 1% and 35%. In one embodiment the polymeric material or the tubular body treatment comprises a heat treatment preferably at substantially the initial diameter, preferably when the initial diameter is 1-1.5 times the stent deployment diameter, to a temperature above glass transition temperature of the polymeric material and below its melting point for a period ranging from a fraction of a second to 7 days. The polymeric material or the tubular body in one embodiment may be cooled after heating to a temperature ranging from below ambient temperature to ambient or above temperature over a period ranging from a fraction of a second to 7 days. In a preferred embodiment, the polymeric material or the tubular body initial diameter is approximately 1-1.5 times the stent deployment diameter or stent nominal deployment diameter, or stent labeled deployment diameter. In another preferred embodiment, the initial diameter is approximately 0.9-1.5 times the stent deployment diameter or stent nominal deployment diameter, or stent labeled deployment diameter. In another embodiment, the initial diameter is smaller than the stent deployment diameter or stent nominal deployment diameter, or stent labeled deployment diameter. The stent deployment diameter in a preferred embodiment is typically the diameter of the stent deployed to approximately nominal or labeled stent diameter but can also be the deployed diameter above the stent nominal or labeled diameter. Stent nominal deployed diameter can be accomplished in one example by inflating the deploying balloon to nominal or labeled diameter to deploy the stent to nominal or labeled diameter. In a preferred embodiment, the polymeric material or the tubular body is patterned at substantially the initial diameter and is crimped subsequently to a crimped diameter that is smaller than the initial diameter. In one embodiment, the polymeric material or the tubular body is treated at diameter between initial diameter and crimped diameter. In a further embodiment, the treatment comprises heating the tubular body to a temperature about or below Tg for a period ranging from a fraction of a second to 7 days. In another embodiment, the heat treatment at the below initial diameter comprises heat treatment about or above Tg and below Tm for a period ranging from a fraction of a second to 5 hours, or preferably less than 2 hour, or most preferably less than 60 minutes, or most preferably less than 15 minutes. The patterned stent in one embodiment is crimped in one or more steps and fitted onto a delivery system or crimped onto the delivery system at a diameter that is less than the initial diameter. In another embodiment, the crimped diameter is less than 3 mm, in another embodiment, the crimped diameter is less than 2.5 mm, in another embodiment, the crimped diameter is less than 2.0 mm in a third embodiment, the crimped diameter is less than 1.5 mm, in a fourth embodiment, the crimped diameter is less than 1 mm, in a fifth embodiment, the crimped diameter is less than 0.8 mm. In a preferred embodiment, the stent is capable to expand from the crimped diameter to a deployed diameter preferably at about body temperature (in water or dry) and have sufficient strength to support a body lumen. In a further preferred embodiment, the stent is capable to expand from the crimped diameter to a deployed diameter at about body temperature (in aqueous or water or dry) without fracture and have sufficient strength to support a body lumen. In a further preferred embodiment, the stent is capable to crimp from an expanded diameter, wherein the expanded diameter is larger than the crimped diameter, and expand from the crimped diameter to a deployed diameter at about body temperature (in aqueous or water or dry) without fracture and have sufficient strength to support a body lumen. In some embodiments, sufficient radial strength to support a body lumen is maintained for at least 1 month, or for at least 2 months, for at least 3 months. In some embodiments, the diameter of the scaffold increases after expansion to nominal diameter or between nominal and 1.1 times nominal diameter by 0.1 mm to 0.5 mm between 5 minutes after deployment to an expanded diameter and 1 hour. In other embodiments, the diameter of the scaffold did not substantially decrease over time. In still other embodiments, the diameter of the scaffold did not substantially increase over time. In some embodiments, an expandable stent comprising a biodegradable polymeric material having an initial configuration is provided. The expandable stent at body temperature can be self-expandable from a crimped configuration and further expandable to a second larger configuration. In further embodiments, the polymeric material has been treated to control one or more of crystallinity, Tg, or molecular weight. In some embodiments, the Tg ranges from about 20° C. to about 50° C. In some embodiments, the second configuration is a deployed configuration. In some embodiments, the stent expands to the first and second configurations without fracture and has sufficient strength to support a body lumen. In some embodiments, the first expanded configuration has a transverse dimension of at least 0.35 times, or at least 0.45 times, or at least 0.55 times, or at least 0.55 times, or at least 0.7 times, or at least 0.8 times, or at least 1 times the transverse dimension of the initial configuration. In some embodiments, the stent expands to the first expanded configuration within a period of 24 hours, or 12 hours, or 4 hours, or 2 hours, or 1 hour, or 30 minutes, or 5 minutes or 30 seconds. In some embodiments, the stent is balloon expandable to the second expanded configuration without fracture and with sufficient strength to support a body lumen. In some embodiments, an expandable stent comprising a biodegradable polymeric material having an initial configuration is provided. The expandable stent at body temperature can be expandable from a crimped configuration to a first expanded configuration and self expandable to a second larger configuration. In further embodiments, the polymeric material is treated to control one or more of crystallinity, Tg, or molecular weight. In some embodiments, the expandable stent comprises a substantially continuous tubular body. In some embodiments, the stent expands to the first configuration without fracture and has sufficient strength to support a body lumen. In some embodiments, the stent has a nominal expanded configuration with a transverse dimension and the first expanded configuration has a transverse dimention that is at least 1 times the transverse dimension of the transverse dimention of the nominal expanded configuration. In some embodiments, the first expanded configuration is a deployed configuration. In some embodiments, the stent has a nominal expanded configuration with a transverse dimension and the fierst expanded configuration has a transverse dimention that is 1 time, or 1.1 times, or 1.2 times, or 1.3 times, or 1.35 times, or 1.4 times, or 1.45 times, or 1.5 times the transverse dimension of the transverse dimension of the nominal expanded configuration. Fabricating a biodegradable stent can be accomplished through a variety of ways. In a preferred embodiment, the biodegradable stent is fabricated by forming a tubular body using extrusion, molding such as injection molding, dipping, spraying such as spraying a tube or mandrel, printing such as 3D printing. The tubular body in a preferred embodiment is formed first and then patterned into a structure capable of radial expansion from a crimped configuration preferably at body temperature. The tubular body in another preferred embodiment is formed first and then patterned into a structure capable of radial expansion from a crimped configuration preferably at body temperature and preferably without fracture. The tubular body in another preferred embodiment is formed first and then patterned into a structure capable of being crimped from an expanded configuration to a crimped diameter (at temperature about Tg or less than Tg), and at body temperature capable to be expanded from the crimped configuration preferably without fracture. In another preferred embodiment the polymeric material is patterned first and then forms a tubular body/stent capable of radial expansion at body temperature and/or capable to be crimped preferably at temperature about Tg or less than Tg. In another preferred embodiment, the biodegradable stent is fabricated from a sheet (such as a flat sheet) joined at ends (such as opposite ends) to form a tubular body capable of radial expansion preferably at body temperature and/or capable to be crimped preferably at temperature about Tg or less than Tg, and patterned before and/or after joining Joining sheet ends can be accomplished by a variety of methods such as adhesive, ultrasound, welding, melting the ends, chemical means, or treatment such as heating. The tubular body formed from a sheet can be further treated to control crystallinity and Tg as described in this patent application. The tubular body formed form the sheet has an initial diameter, preferably 1-1.5 times the stent deployed diameter. In other preferred embodiment, the biodegradable stent is fabricated from weaving or braiding polymeric material fibers into a tubular body structure capable of expansion at body temperature and/or capable to be crimped at temperature preferably about Tg or less than Tg. Preferably, weaving or braiding of the polymeric material such as fibers into the initial tubular configuration which is capable of radial expansion at body temperature and/or capable of being crimped from an expanded diameter preferably at temperature about Tg or less than Tg (in aqueous or dry environment) wherein the initial diameter is preferably 1-1.5 times the stent deployed diameter (or the stent nominal diameter, or the stent labeled diameter) and preferably treated at the initial tubular diameter, to achieve controlled crystallinity preferably between 0 and 45%, or more preferably between 0 and 35% and a Tg greater than 37° C. and less than 50° C., or more preferably greater than 37° C. and less than 45° C.) and the stent is capable to expand from a crimped configuration to an expanded configuration/diameter at body temperature and has sufficient strength to support a body lumen, and preferably without fracture. In another preferred embodiment, the stent is capable to be crimped (at temperature preferably about Tg or below Tg), and expand from a crimped configuration to an expanded configuration/diameter at body temperature and has sufficient strength to support a body lumen, and preferably without fracture. In another preferred embodiment, the biodegradable stent is formed using injection molding wherein the polymeric material is loaded inside a mold and the mold is treated once or more to control crystallinity preferably to between 1% and 55% (preferably between 1% and 35%) and treated to control Tg preferably to greater than 37° C. and less than 50° C. (or in another preferred embodiment control Tg to greater than 20° C. and less than 50° C.), or as described within this patent application. The formed patterned tube/stent has an initial diameter, preferably 1-1.5 times the stent deployed diameter, and the treatment can take place before, and/or during, and/or after the molding process and the stent capable to radially expand preferably at body temperature (dry or in aqueous environment). The stent in another embodiment is capable to be expanded from a crimped configuration (which is smaller than the expanded diameter) to an expanded diameter at body temperature and have sufficient strength to support a body lumen, and preferably without fracture. The stent in another embodiment is capable to be crimped from an expanded diameter to a crimped diameter (at temperature preferably about Tg or less than Tg), and expanded from the crimped configuration to an expanded diameter at body temperature and have sufficient strength to support a body lumen, and preferably without fracture. In another preferred embodiment, the biodegradable stent can be fabricated using printing such as 3-D printing wherein the polymeric material is loaded onto the printer and treated to form a patterned tubular body/structure/stent wherein it has an initial diameter, preferably 1-1.5 times the stent deployed diameter, and is treated to control crystallinity and Tg as described within this patent application, and the stent is capable to radially expand at body temperature. The stent in another embodiment is capable to expand from a crimped configuration to an expanded diameter at body temperature and has sufficient strength to support a body lumen, and preferably without fracture. The stent in another preferred embodiment is capable to be crimped from an expanded diameter to a crimped configuration (at temperature preferably about Tg or less than Tg), and expand from the crimped configuration to an expanded diameter at body temperature and has sufficient strength to support a body lumen, and preferably without fracture. Although the preferred embodiment when crimping the stent is at temperature about Tg or less than Tg, crimping the stent can be accomplished at temperature above Tg or within 20° C. above Tg. Although treatment by heat typically ranges from below Tg to below Tm, in some other cases treatment of the polymeric material can be about Tm or above for example when the stent is formed by printing or injection molding. A preferred formation process comprises forming a tube using spraying a polymer or polymeric material comprising one or more polymer, co-polymer- or monomer dissolved in at least one solvent onto a cylindrical mandrel or other structure when the stent prosthesis desired shape is non cylindrical such as oblong shape or other shapes. When the stent prosthesis is not cylindrical, a dimension of the stent may be referred to as “transverse dimension” instead of diameter. Optionally, additives, such as strength-enhancing materials, drugs, or the like, may be dissolved in the solvent or other solvents together with the polymer or polymeric material so that the materials are integrally or monolithically formed with the endoprosthesis tube. Alternatively, methods according to embodiments of the invention may rely on obtaining a pre-formed polymer tube from a supplier or other outside source. In some embodiments, the polymeric tubular body is usually formed as a substantially continuous cylinder free from holes or other discontinuities. In another embodiment, the tubular body has a foraminous wall. In a third embodiment, the tubular body is formed from a continuous tube. In a fourth embodiment, the tubular body comprises a plurality of fibers woven into an expanded diameter, preferably the initial tubular configuration with a diameter preferably of 1-1.5 times the stent deployed diameter and preferably treated at the initial tubular diameter. The polymeric material or the tubular body or deployed stent typically has an outside or inner diameter in the range from 2 mm to 25 mm, preferably 3 mm to 10 mm, or 3.5 mm to 10 mm, and a thickness preferably in the range from 0.01 mm to 0.5 mm, and may be cut into lengths suitable for individual endoprostheses, typically in the range from 5 mm to 40 mm but can also range from 1 mm to 150 cm. In an embodiment, the tubular body may be patterned into a suitable endoprosthesis structure, typically by laser cutting or other conventional processes such as milling, chemical etching, stamping, photolithography, etc. In other embodiments, the stent prosthesis is formed by 3D printing which patterns the tubular body/stent as it is being formed and optionally treated to control crystallinity and Tg to facilitate a stent capable to radially expand at body temperature and support a body lumen and preferably without fracture. In another embodiment, the tubular body comprises a plurality of fibers woven into the initial tubular configuration with a diameter preferably of 1-1.5 times the stent deployed diameter and preferably treated at the initial tubular diameter. In another embodiment, the stent tubular body is formed from a sheet joined at opposite ends and patterned either before or after joining. In some embodiments, as described herein, a biodegradable endoprosthesis (e.g., a stent) is formed from a polymeric tube, wherein the tube is a substantially continuous cylinder. In some cases, the substantially continuous cylinder may be substantially free from holes, gaps, voids or other discontinuities. In other embodiments, the tube may be substantially continues yet include some holes, gaps, voids, or other discontinuities. The tubular body may have an outside diameter in the range from about 2 mm to 10 mm, or about 3 mm to about 9 mm, or about 4 mm to about 8 mm, or about 5 mm to about 7 mm. The tubular body may have a thickness in the range from 0.01 mm to 0.5 mm, or about 0.05 mm to about 0.4 mm, or about 0.1 mm to about 0.3 mm. In certain embodiments, the tubular body or polymeric material, or the stent has an initial diameter. In one preferred embodiment, the initial diameter is 1-1.5 times the stent deployed diameter. In another preferred embodiment, the initial diameter is 0.9-1.5 times the stent deployed diameter. In a further embodiment, the initial diameter is less than the stent deployed diameter. The initial diameter can be the as-formed diameter, or the diameter before patterning, or the diameter after patterning, or the diameter before crimping. In one embodiment, an endoprosthesis (e.g., a stent) is patterned by laser cutting or other method from a polymeric tube that has a (e.g., inner or outer) diameter substantially equal to or smaller than deployed (e.g., inner or outer) diameter of the endoprosthesis. In other embodiments, an endoprosthesis (e.g., a stent) is patterned from a polymeric tube that has a (e.g., inner or outer) diameter, either when the tube is formed or after the tube is radially expanded to a second larger diameter, larger than deployed (e.g., inner or outer) diameter of the endoprosthesis. Patterning a stent from a polymeric tube having a (e.g., inner or outer) diameter larger than deployed (e.g., inner or outer) diameter of the stent can impart advantageous characteristics to the stent, such as reducing radially inward recoil of the stent after deployment and/or improved strength. In certain embodiments, a stent is patterned from a polymeric tube having a (e.g., inner or outer) diameter about 0.85, 0.90, 1.0, 1.05 to about 1.5 times, or about 1.1 to about 1.5 times, or about 1.1 to about 1.3 times, or about 1.15 to about 1.25 times, smaller, same, or larger than an intended deployed (e.g., inner or outer) diameter of the stent. In an embodiment, the stent is patterned from a polymeric tube having a (e.g., inner or outer) diameter about 1.1 to about 1.3 times larger than an intended deployed (e.g., inner) diameter of the stent. For example, a stent having a deployed (e.g., inner or outer) diameter of about 2.5, 3 or 3.5 mm can be patterned from a tube having a (e.g., inner or outer) diameter of about 2.75, 3.3 or 3.85 mm (1.1 times larger), or about 3.25, 3.9 or 4.55 mm (1.3 times larger), or some other (e.g., inner or outer) diameter larger than the deployed (e.g., inner or outer) diameter of the stent. In preferred embodiments, the initial diameter of the formed tube is larger than the crimped diameter (e.g., crimped diameter on a delivery system) of the stent prosthesis wherein the tubular body is expanded to a second larger diameter than the initial diameter before patterning or before crimping to the crimped diameter; or wherein the tubular body remains substantially the same diameter before patterning or before crimping to a crimped diameter; or wherein the tubular body is crimped to a smaller diameter than the initial formed diameter before patterning or after patterning. In another embodiment, the initial diameter of the formed tube is smaller than the crimped diameter of the stent prosthesis wherein the tubular body is expanded to a second larger diameter than the initial diameter before patterning or before crimping; or wherein the tubular body remains substantially the same diameter before patterning or before crimping; or wherein the tubular body is crimped to a smaller diameter than the crimped diameter of the stent prosthesis before patterning or after patterning. In another embodiment, the initial diameter of the formed tubular body is greater than 0.015 inches, or greater than 0.050 inches, or greater than 0.092 inches, or greater than 0.120 inches, or greater than 0.150 inches, in the as-formed diameter, or before patterning diameter, or after patterning diameter, or before crimping diameter. Stent prosthesis intended deployment diameter is the diameter of the labeled or nominal or higher of the delivery system or balloon catheter, or higher. For example when a stent prosthesis is crimped onto a balloon labeled 3.0 mm diameter (e.g., deployed nominal diameter), the stent prosthesis' deployed diameter or intended deployment diameter is 3.0 mm or higher. Similarly, self expandable stent crimped onto a delivery system is labeled a certain deployment diameter. In a preferred embodiment, a stent prosthesis or tubular body or polymeric material has initial diameter (or initial transverse dimension), preferably 1-1.5 times deployed diameter (deployed transverse dimension) or deployed nominal diameter (e.g., deployed nominal transverse dimension), where in the initial diameter (or initial transverse dimension) is as-formed diameter (or transverse dimension), before patterning diameter (or transverse dimension), or after patterning diameter (or transverse dimension), or before crimping diameter (or transverse dimension), and wherein the initial diameter (or initial transverse dimension) is greater than crimped diameter (or crimped transverse dimension). In a preferred embodiment, a stent or tubular body first self-expands by at least 0.35 of initial diameter or transverse dimension, and then expands to second larger diameter or transverse dimension, which may be the deployed diameter or transverse dimension, preferably by balloon expansion. In a further preferred embodiment, the stent or tubular body may expand to 1.0 times or more, or 1.1 times or more, or 1.2 times or more, or 1.3 times or more, or 1.4 times or more, or 1.5 times or more the deployed diameter or nominal diameter (or transverse dimension) at body temperature, without fracturing. In a further preferred embodiment, the stent or tubular body or polymeric material is crimped from an expanded diameter to a crimped configuration, and at body temperature expands to 1.0 times or more, or 1.1 times or more, or 1.2 times or more, or 1.3 times or more, or 1.4 times or more, or 1.5 times or more the deployed diameter or nominal diameter (or transverse dimension), without fracturing. In a further preferred embodiment, the stent or tubular body is crimped from an expanded diameter to a crimped configuration wherein the ratio of expanded diameter to crimped configuration is at least 1.5, and at body temperature the stent expands to 1.0 times or more, or 1.1 times or more, or 1.2 times or more, or 1.3 times or more, or 1.4 times or more, or 1.5 times or more the deployed diameter or nominal diameter (or transverse dimension), without fracturing. In a further preferred embodiment, the stent or tubular body is crimped from an expanded diameter to a crimped configuration wherein the ratio of expanded diameter to crimped configuration is at least 2, and at body temperature the stent expands to 1.0 times or more, or 1.1 times or more, or 1.2 times or more, or 1.3 times or more, or 1.4 times or more, or 1.5 times or more the deployed diameter or nominal diameter (or transverse dimension), without fracturing. In a further preferred embodiment, the stent or tubular body is crimped from an expanded diameter to a crimped configuration wherein the ratio of expanded diameter to crimped configuration is at least 2.5, and at body temperature the stent expands to 1.0 times or more, or 1.1 times or more, or 1.2 times or more, or 1.3 times or more, or 1.4 times or more, or 1.5 times or more the deployed diameter or nominal diameter (or transverse dimension), without fracturing. In a further preferred embodiment, the stent or tubular body is crimped from an expanded diameter to a crimped configuration wherein the ratio of expanded diameter to crimped configuration is at least 3, or at least 4, or at least 5, or at least 6, or at least 7, and at body temperature the stent expands to 1.0 times or more, or 1.1 times or more, or 1.2 times or more, or 1.3 times or more, or 1.4 times or more, or 1.5 times or more the deployed diameter or nominal diameter (or transverse dimension), without fracturing. In a further preferred embodiment, the stent or tubular body is crimped from an expanded diameter to a crimped configuration wherein the ratio of expanded diameter to crimped configuration is at least 2, or at least 2.5, or at least 3, or at least 3.5, or at least 4, wherein the stent at body temperature is expandable from the crimped configuration to the deployed configuration without fracture, wherein the deployed configuration is the nominal or higher deployment diameter. In another preferred embodiment, the stent is balloon expanded to its deployed diameter (or transverse dimension) first and then expands, preferably self expands, to a second larger diameter (or transverse dimension) by about 0.1 mm or more, or about 0.2 mm or more, or about 0.3 mm or more, or about 0.4 mm or more, or about 0.5 mm or more, without fracture. In a further preferred embodiment, the balloon expandable stent or tubular body or polymeric material expands to 1.0 times or more, or 1.1 times or more, or 1.2 times or more, or 1.3 times or more, or 1.4 times or more, or 1.5 times or more the deployed diameter or nominal diameter (or transverse dimension) at body temperature, without fracturing. In a further preferred embodiment, the stent or tubular body is crimped from an expanded diameter to a crimped configuration, and at body temperature is balloon expandable to 1.0 times or more, or 1.1 times or more, or 1.2 times or more, or 1.3 times or more, or 1.4 times or more, or 1.5 times or more the deployed diameter or nominal diameter (or transverse dimension), without fracturing. In a further preferred embodiment, the stent or tubular body is crimped from an expanded diameter to a crimped configuration wherein the ratio of expanded diameter to crimped configuration is at least 1.5, and at body temperature the balloon expandable stent expands to 1.0 times or more, or 1.1 times or more, or 1.2 times or more, or 1.3 times or more, or 1.4 times or more, or 1.5 times or more the deployed diameter or nominal diameter (or transverse dimension), without fracturing. An endoprosthesis (e.g., a stent or a stent delivery system) and/or the polymeric article/material (e.g., a polymeric tube) from which it is formed can be exposed to ionizing radiation such as electron beam or gamma radiation or to ethylene oxide gas (e.g., for purposes of sterilization and/or treatment) as described herein. Such modification or treatment in that it can, e.g., control crystallinity (e.g., degree of crystallinity), control Tg, control molecular weight, control monomer content, and/or enhance the strength of the material (e.g., polymeric material) comprising the polymeric article or the endoprosthesis. In some embodiments, the polymeric article and/or the endoprosthesis are exposed to a single dose or multiple doses of e-beam or gamma radiation totaling about 5 or 10 kGy to about 50 kGy, or about 20 kGy to about 40 kGy of radiation, e.g., a single dose of 30 kGy or multiple smaller doses (e.g., 3×10 kGy doses)], where the polymeric article and/or the endoprosthesis are optionally (cooled to low temperature (e.g., about −10° C. to about −30° C., or about −20° C. to less than ambient temperature) for a period of time (e.g., at least about 1 minute, 20, 30 or 40 minutes) or optionally treated at about ambient temperature) prior to exposure to the single dose or to each of the multiple doses of radiation. In certain embodiments, the polymeric article and/or the endoprosthesis are exposed to a single dose or multiple doses of e-beam or gamma radiation totaling about 10 kGy to about 50 kGy, or about 30 kGy. A polymeric article and/or an endoprosthesis that have been exposed to ionizing radiation or ethylene oxide gas can also undergo one or more other modification treatments (e.g., heating or annealing and/or cooling) described herein. In some embodiments, the tubular body or polymeric material or stent may be formed from at least one polymer having desired degradation characteristics where the polymer may be modified to have the desired crystallinity, Tg, recoil, strength, shortening, expansion characteristics, crimping characteristics, crystallinity, Tg, molecular weight, and/or other characteristics in accordance with the methods of the present invention. Polymers include one or more polymers, copolymers, blends, and combination thereof of: Lactides, Glycolides, Caprolactone, Lactides and Glycolides, Lactides and Caprolactones: examples poly-DL-Lactide, polylactide-co-glycolactide; polylactide-co-polycaprolactone, poly (L-lactide-co-trimethylene carbonate), polylactide-co-caprolactone, polytrimethylene carbonate and copolymers; polyhydroxybutyrate and copolymers; polyhydroxyvalerate and copolymers, poly orthoesters and copolymers, poly anhydrides and copolymers, polyiminocarbonates and copolymers and the like. A particularly preferred polymer comprises a copolymer of L-lactide and glycolide, preferably with a weight ratio of 85% L-lactide to 15% glycolide. In one aspect of the invention, the tubular body or polymeric material or stent material comprises a degradable polymeric material wherein the polymeric material comprises one or more polymers; or one or more co-polymers; or one or more blends of monomers, polymers or copolymers; and combination thereof. In another embodiment, the polymeric material comprises one or more polymer or one or more co-polymer. Additionally, at least one monomer, polymer, or co-polymer of similar material (to the one or more polymer or the one or more co-polymer) is blended with the polymeric material. In another embodiment, a different monomer, co-polymer, or polymer is blended with (the one or more polymer or the one or more co-polymer) the polymeric material. In a preferred embodiment, a biodegradable stent comprising a polymeric material comprising a copolymer of lactide and caprolactone in the ratio by weight ranging from 80-99% lactide to 1-20% caprolactone; wherein the polymeric material further comprises a monomer or polymer including copolymer of one or more of the following: lactide, glycolide, lactide glycolide, caprolactone, and lactide caprolactone; wherein the one or more monomer or polymer total amount is 1 to 100 micrograms per milligram of polymeric material, preferably 5 to 75 micrograms per milligram of polymeric material, more preferably 10 to 50 micrograms per milligrams of polymeric material; wherein the stent is capable to be crimped from an expanded configuration to a smaller crimped configuration, and at body temperature expanded to a deployed configuration, and having sufficient strength to support a body lumen, and without fracture of the stent. In another preferred embodiment, a biodegradable stent comprising a polymeric material comprising a copolymer of lactide and caprolactone in the ratio by weight ranging from 80-99% lactide to 1-20% glycolide; wherein the polymeric material further comprises a monomer or polymer including copolymer of one or more of the following: lactide, glycolide, lactide glycolide, caprolactone, and lactide caprolactone; wherein the one or more monomer or polymer total amount is 1 to 100 micrograms per milligram of polymeric material, preferably 5 to 75 micrograms per milligram of polymeric material, more preferably 10 to 50 micrograms per milligrams of polymeric material; wherein the stent is capable to be crimped from an expanded configuration to a smaller crimped configuration, and at body temperature expanded to a deployed configuration, and having sufficient strength to support a body lumen, and without fracture. In a further embodiment, the one or more monomer and/or polymer does not substantially change the crystallinity of the polymeric material. In a further embodiment, the one or more monomer and/or polymer changes (increases or decreases) the crystallinity of the polymeric material by 5% to 150%, preferably by 10% to 75%, more preferably by 10% to 50%. In a further embodiment, the one or more monomer and/or polymer controls the crystallinity of the polymeric material to between 1% and 55%, preferably between 1% and 35%. In a further embodiment, the one or more monomer and/or polymer does not change the crystallinity of the polymeric material from being between 1% and 55%. In a further embodiment, the one or more monomer and/or polymer does not substantially change the Tg of the polymeric material. In a further embodiment, the one or more monomer and/or polymer changes (increases or decreases) the Tg temperature of the polymeric material by 1 C to 15 C, preferably 1° C. to 10° C., more preferably by 1° C. to 5° C. In yet a further embodiment, the one or more monomer and/or polymer controls the Tg temperature of the polymeric material to between 20° C. and 55° C., preferably to between 35° C. and 50° C., more preferably to between 37° C. and 50° C., most preferably between 37° C. and 45° C. The polymeric material/article and/or the tubular body and/or the prosthesis or device can undergo any of a variety of modification or treatments (e.g., longitudinal extension, longitudinal shrinkage, radial expansion, heating, cooling, quenching, pressurizing, exposure to or humidity, vacuuming, exposure or incorporation or removal of solvents, incorporation of additive, removal of additives, incorporation of or removal of impurities, exposure to radiation, incorporation or exposure or pressurization by gases such as carbon dioxide, or a combination thereof) designed to control or enhance characteristics (e.g., crystallinity, Tg, molecular weight, strength, toughness and degradation, recoil, shortening, expansion) of the article, the tubular body, the polymeric material, and/or the prosthesis or device. The biodegradable implantable device formed from a polymeric article made by spraying, extrusion, dipping, molding, 3D printing, and the like, can have any features of a biodegradable implantable device comprising a body comprising a biodegradable polymer (including homopolymer or copolymer) described herein. In some embodiments, modification or treatment may include heating, and/or pressurizing. In one preferred embodiment, the polymeric material is treated wherein the treatment comprises incorporation of solvents wherein the one or more
{'app_number': None, 'application_number': '<application-reference appl-type="utility">\n<document-id>\n<country>US</country>\n<doc-number>14611043</doc-number>\n<date>20150130</date>\n</document-id>\n</application-reference>', 'doc_number': None, 'publication_number': '<publication-reference>\n<document-id>\n<country>US</country>\n<doc-number>20150374521</doc-number>\n<kind>A1</kind>\n<date>20151231</date>\n</document-id>\n</publication-reference>', 'source_file': './application/2015/ipa151231.xml', 'source_data': 'USPTO-Application'}