ADJUSTABLE SUTURES AND METHODS OF MAKING AND USING SAME

Abstract: A surgical suture is made from materials which, upon the application of at least one source of non-frictional energy, such as may be imparted by using a laser, alter dimension. In essence, these sutures can be made to contract and/or expand after implantation in tissues and/or prosthetic materials. The absorbtion of energy may be enhanced by the addition to the suture material of an energy absorbing substance, and especially a substance that is selected to absorb radiation at the wavelength of a laser used to effect the dimensional change. Preferred sutures are comprised of cross-linked polyolefins. These fibers may also be formed into composite structures, such as a braided structure, to provide a composite suture having selectively alterable component suture elements.

Description: ADJUSTABLE SUTURES AND METHODS OF MAKING AND USING SAME FIELD OF THE INVENTION The present invention relates generally to sutures used to repair tissues whose dimensions may be modified in vivo , a method of repairing tissues using the sutures, and to methods for making such sutures. BACKGROUND OF THE INVENTION Surgical sutures are generally categorized as either absorbable or non-absorbable depending upon whether the suture material is degraded and resorbed by the body. Both categories of sutures are made from natural or synthetic materials. Sutures are further differentiated based on whether the suture is made of a single fiber or filament (monofilament) or multiple filaments that are twisted or braided. Sutures may be provided with a variety of coatings which can serve to minimize friction as the suture is passed through the tissue and to decrease tissue reactivity towards the suture material. The choice of suture for a given surgical procedure is based on the properties of the suture material and the response of the tissue being repaired. To be useful as a suture, the fiber structure must be at least required to be strong enough to carry the applied load, and to maintain substantially its dimensional integrity after implantation. It is well-recognized that the natural response of tissue to injury, even injury resulting from a careful and appropriate surgical technique, is one of extracellular fluid accumulation (edema) in the vicinity of the wound. Thus, sutures which have been appropriately placed and tensioned at the time of surgery may excessively constrict the tissue as edema forms post-operatively. Excessive constriction results in strangulation and necrosis of the tissue. It is often difficult to anticipate at the time of surgery how much edema will form post-operatively. Yet it is not feasible to leave sutures slack at the time of placement in the hope that subsequent edema will ensure an appropriate suture tension because poor initial approximation resulting from the placement of a slack suture can allow for the entry of bacteria and contribute to wound dehiscence. Sutures are sometimes placed in previously inflamed tissue which is edematous at the time of the surgical repair, as a result of tissue inflammation and/or an injection of an anesthetic and/or a hemostatic agent into the wound margins. In this circumstance, the sutures are tensioned to accommodate the edematous tissue. In the immediately post-operative period, the sutures may slacken as the edema resolves. This can likewise result in bacteria entering the wound and poor wound healing. Proper suturing requires that the sutures be tensioned just enough to approximate, but not strangulate, the tissue For example, in skin closure, small bites of tissue with th needle placed at 2 to 3 mm from the skin edges keeps the amount of tissue under tension relatively small, and helps to minimize scarring. Wound edema in the early post-operative period increases the tension on the skin between sutures. This frequently results in permanent skin suture marks, especially if the sutures are allowed to remain for prolonged periods. (S.J. Aston, "The Choice of Suture Material for Skin Closure," J. of Derm . Surg . , 2(1): 57-61, March 1976; incorporated herein by reference.) Proper tensioning of sutures, even in the hands of a skilled surgeon, is difficult, subject to error, and time consuming; it is an empirical art. When a suture is tensioned too tightly, or becomes too tight as a result of tissue edema, the surgeon must cut the suture using a scalpel, scissors, or laser. (Marc F. Lieber anx, "Suture Lysis by Laser and Goniolens," Am. J. Ophth . 95(2): 257-258 1983) . However, removal of a tight suture can result in gaping of the wound and subsequent scarring. Furthermore, additional time is needed during the operation to correct the problem of improper suture tensioning, thereby further extending the duration of the surgical procedure. When a suture is tensioned too loosely, or loosens post-operatively, the suture must be replaced. The replacement of a suture is not only time consuming but may require returning the patient to the operating room. Moreover, although intended to improve wound apposition an reduce scar formation, the replacement of sutures further traumatizes the tissues to be repaired. Previous attempts at overcoming the difficulties or proper suture tensioning have included the replacement of sutures with a heat-shrinkable sleeve for vessel anastomosis. John J. Wozniak, in U.S. Pat. No. 4,470,415, discloses placing a heat-shrinkable sleeve around the vessels to be joined and heating the sleeve with a wand or other suitable heat transmitting applicator. These heat-shrinkable sleeves suffer from a number of disadvantages. Their use is limited to tubular members, an thus are of little value in other anastomoses, such as skin and cataract incision closure. Their placement requires th use of two ferrules which become permanently incorporated into the wound; the ferrules can be made of degradable or non-degradable materials. The use of degradable materials such as collagen and polyglycolate cause an inflammatory response, which may lead to thrombosis and vascular occlusion. The non-degradable materials, such as polyethylene, can lead to foreign body reactions, or can erode into the vessels they are meant to repair, resulting in wound failure, infection, or thrombosis. John F. Krumme, U.S. Pat. No. 4,485,816, discloses another approach to eliminating problems associated with suture repair. Krumme discloses staples made from a material having the intrinsic property of shape memory (e.g. nickel-titanium alloys) that are used in place of sutures. The staples are formed at low temperatures into a shape which expedites entry into the tissue, and are then deforme into a tissue-gripping shape upon subsequent heating. Such staples are disadvantageous because, like conventional suture techniques, once inserted and reformed into a tissue gripping memorized shape, the tension of the staples cannot be adjusted. Although sutures may be deformed reversibly or irreversibly by stretching them under force at the time of surgery, attempts to adjust sutures in this fashion are typically ineffective. All materials may be deformed to some extent without a permanent deformation; e.g., when a force or stress is applied to an object, it deforms reversibly if the stress applied is below the "elastic limit" (which depends upon the composition of the material) and when the stress is removed the object returns to its original dimensions (except for possible hysteresis effects) . On the other hand, if the force applied to the object is greater than the elastic limit, the object will undergo some irreversible deformation to accomodate the applied stress. For example, force may be used to bend a plank of wood, but too great a force will result in some permanent and irreversible deformation of the plank. The same phenomenon occurs in metals, and even in ceramics, which have a very low elastic modulus and thus do not bend very easily. On the other hand, polymeric materials typically have a higher elastic modulus and may be deformed quite often and/or significantly within their elastic limit. If still greater force is applied above the elastic limit, the material will be permanently deformed, and at still higher stresses the material eventually fails to maintain its integrity; this last occurrence is termed the break point. Suture materials generally may be reversibly deformed by elongation up to about 30% of their original length, and they may be irreversibly deformed (i.e., a stress above the elastic limit but below the break point) u to about 70% of their original length. However, it is extremely difficult to adjust a suture's length in a controlled fashion simply by permanently deforming it, especially at ambient temperature. One reason for this difficulty is the challenge of accurately judging the difference in forces needed to deform the suture from those needed to break the suture. Another problem with this method is that irreversible elongation typically degrades the strength of the suture to less than would be desirable for the suture to maintain its integrity. Yet another difficulty is determining the final length of the suture, because some indeterminable combination of reversible and irreversible elongation typically occurs when a suture is stretch to the point of permanent deformation. Therefore, it is not practical to adjust the length of a suture by merely permanent deformation. Because of the difficulties in obtaining proper suture tension both intra-operatively and post-operatively using conventional sutures and alternatives including staples and heat shrinkable sleeves as described above, there remains a need for the development of an easy to use suture having dimensions, particularly the linear dimension, that can be altered after implantation in the tissue or prosthetic material. It is therefore an object of the present invention to provide a suture having dimensions that can be altered afte implantation to relieve or increase tension on the tissue o prosthetic material. It is another object of the present invention to increase or decrease the cross-sectional area of the suture to prevent leakage around the insertion site in the anastomoses of fluid containing structures such as blood vessels, bowel, and meninges. It is a further object of the invention to provide a suture having dimensions that can be altered by the application of energy without damaging the tissue. It is a further object of the invention to provide a method of suturing tissues or prosthetic materials employin a suture having dimensions that can be altered after implantation either at the time of surgery or in the post-operative period. Yet another object of the invention is to provide processes for fabricating sutures capable of shrinkage, elongation, or both, and to provide the sutures so made. SUMMARY OF THE INVENTION The present invention is directed to sutures which are suitable for reapproximation of divided biologic tissues an prosthetic materials, and for the ligation of vascular and other tubular structures. The dimensions of the sutures ca be adjusted after implantation to provide proper tension. The dimension also can be adjusted to prevent leakage around the insertion site in the anastomoses of fluid containing structures such as blood vessels, bowel, and meninges. The sutures in accordance with the present invention can expand or contact so that the size of the suture may be adjusted for a particular application. This dimensional alteration allows for greater control of tissue reapproximation, thereby reducing tissue trauma, and also reducing post-operative scar formation. The expansion or contraction of the suture material of the present invention occurs generally in the axial direction (the length of the suture) and the radial direction (the diameter and circumference of the suture) . The changes in suture diameter are useful for applications, for example, in vascular and bowel anastomoses, where there is frequently leakage of blood or intestinal fluid around the suture site; leakage increases the length of the operation and the potential for post-operative complications such as infection or graft failure. This leakage problem with sutures is particularly common in anastomosis of prosthetic graft material to native tissue. To overcome this problem, a suture material made to impart significant shrinkage upon the application of energy can be inserted and tied in a loose fashion and, for example, the application of photon energy near the insertion site by using a laser will result in the shortening and thickening of the suture, thereby eliminating the leakage. Moreover, the precise control of suture tension afforded by the sutures of the present invention will insure that the suture is well-tensioned. The suture of the present invention is made from any acceptable material which may be processed so that its dimensions can be altered in vivo without damaging the surrounding tissue or prosthetic material. Such sutures ar preferably made from energy sensitive materials which are particularly suited for adjustment after implantation. The preferred suture materials are polyolefins, including polypropylene and mixtures of polyolefins alone or in combination with other compatible polymers such as polyviny acetate. The present invention thus provides a surgical suture comprising a polymeric material sensitive to an activatable source of non-frictional energy effective to change the dimensions of the suture in vivo. By "non-frictional energy" is meant any form of energy other than the energy mechanical imparted axially to stretch or draw a suture in vivo through direct physical contact. For example, the present fibers may be shrunk by using photonic energy (e.g., a laser) , and may be elongated by using tension (frictional energy) in combination with a laser (a source of non- frictional energy) . By activatable is meant that the surgeon has control over the energy source to effect a desired change by intentionally imparting discrete amounts of non-frictional energy. The dimensions of the suture may be altered to axially shrink or elongate, and/or to transversely neck down or swell; generally, changes in the axial dimensions will change the tension under which the sutured tissues are placed, and changes in the transverse dimensions will effectively seal the suture in the tissue through which it passes. In another aspect of the invention, the novel sutures are provided to alter dimensions in response to energy inpu directly from the patient. Although not the preferred modality, heat from the patient's own body can be effectively used to alter the dimension of the suture; more particularly, the suture can be made to shorten directly after implantation, and edematous expansion of the sutured tissue can be accomodated by elongation of the suture, both changes facilitated by the effect of the patient's own body heat on the suture material. These sutures can be made by imparting potential energy to the sutures and/or by preparing the sutures to be dimensionally alterable. A fiber can be stretched and the stretching energy stored as potential energy; the selective application of non-frictional energy can be used to release this stored energy in the form of work done to change the dimensions of the suture. The fiber may be cross-linked to allow for dimensional changes without degrading the basic integrity needed to be useful as a suture. DETAILED DESCRIPTION OF SPECIFIC EMBODIMENTS Energy sensitive materials, which are preferred materials employed in the present invention, are widely use to package foods and in the electronics industry to protect and encapsulate electronic components. The ability to change dimensions upon the application of energy, particularly to shrink, can be imparted to thermoplastic materials by monoaxial or biaxial stretching (Encyclopedia of Polymer Science and Technology, Interscience Publishers, John Wiley & Sons, Vol. 11, 1965 and 1986; incorporated herein by reference). Stretching of a material below the softening temperature orients the polymer chains and crystallites in the direction of stretch leading to changes in the stress-strain characteristics of the material. Both the modulus of elasticity and the ultimate strength are increased by this process, but the elongation at break and dimensional stability with respect to temperature decrease. (See also, Oilman ' s Encyclopedia of Industries Chemistry, Verlaggeselischuft, 1988, and Encyclopedia of Polymer Science and Engineering, Ed. by H.F. Mark et al. (Wiley-Interscience 1986) ; both incorporated herein by reference.) Procedures to orient fibers and similar suture geometries are dependent on the type of polymer being used; such techniques are known in the art and are described in the various references related to polymer technology incorporated herein by reference. In general, a polymer composition may be crystallizable or non-crystallizable. T orient the polymer chains in a fiber, it is preferred that there be as little crystallinity as possible. After orientation, crystallization or heat-stabilizing may be performed. Generally, heat-stabilization is not performed as the goal is to produce a suture which can be adjusted through the application of heat or other energy; however, t control the amount of shrinkage which can be imparted, partial heat-stabilization may be performed. Also, cross- linking of the fiber may be performed to alter the suture properties. To orient noncrystallizable polymers, the polymer is heated to a temperature at which it becomes a viscous liquid, and is then cooled to as close to the glass transition temperature as is practical for stretching. The material is then stretched either at a constant temperature or under a falling temperature gradient to orient the polymer chains, and is subsequently cooled rapidly (i.e., quenched) to below the glass transition temperature. (Encyclopedia of Polymer Science and Technology, op. cit . } see also David J. Williams, Polymer Science and Engineering (Prentice-Hall 1971), incorporated herein by reference.) Examples of non-crystallizable polymer are pol (vinyl acetate) and poly(styrene) . To orient crystallizable polymers, it is preferably to first reduce the amount of crystallinity by heating the polymer to a temperature above its crystalline melt temperature and holding at that elevated temperature until essentially all traces of crystallinity have disappeared. The destruction of crystallinity is preferably because it not feasible to introduce a high level of orientation into highly crystalline structure; in essence, the polymer chai must be free to move into an oriented configuration, and thus the polymer crystals must be melted to free the chain The polymer is then quenched to set the polymer in an amorphous state. If feasible, the material also should be cooled below its glass transition temperature to prevent recrystallization, which can occur at temperatures above t glass transition temperature. If this low glass transitio temperature is impractical, the material may be cooled to temperature at which the crystallization rate is sufficiently low that no appreciable amount of crystallini develops in the material before it is stretched. The resulting amorphous or nearly amorphous material then reheated to as low a temperature as practical above t glass transition temperature and stretched rapidly to orie the polymer chains; a rapid rate of stretching also tends favor orientation. The material can then be quenched to below the glass transition temperature or to a lower temperature above the glass transition temperature to give an essentially amorphous, readily heat-shrinkable material. The immediately previous discussion relates generally to orienting fibers. The novel sutures may also be derived from polymer sheets or films. In such a process, for example using an amorphous, non-crystallizable polymer, a film is provided by melt extruding a polymer melt though a thin, flat die. The film is then cooled to as close to the glass transition temperature as feasible and stretched monoaxially or biaxially at constant temperature or under a falling temperature gradient to orient the polymer chains. The sheet or film may also be formed by such methods as calendering. The resulting sheets may then be cut or split into thin tapes, which may be twisted into a braided structure, and drawn into a fiber geometry. The same considerations as mentioned above for crystallizable polymers are necessary when making fibers from a sheet of a crystallizable polymer, especially decreasing the crystallinity of the sheet by heating above the glass transition temperature and quenching. All oriented fibers or films shrink at a temperature between their glass transition temperatures (T ) and their melting (T m ) or softening points (each often a narrow temperature range rather than a specific temperature point) . At temperatures above the glass-transition temperature the material shrinks. The rate of shrinkage increases with increasing temperature until the fiber temperature is sufficiently high that viscous flow competes with retraction. Above this temperature, less than the theoretical maximum amount of shrinkage takes place. With crystallizable polymers, shrinkage above the glass transition temperature can be modulated (i.e., reduced) by the additional step of reheating the polymer to near its crystalline melt temperature briefly (generally a few seconds for polymers such as poly(ethylene terephthalate)) while simultaneously restraining the polymer from shrinking, and then rapidly quenching as before. If this reheating process is carried out for a sufficiently long time or at a sufficiently high temperature, the polymer will not shrink appreciably when it is again subject to heat or photonic energy. Therefore, for the purpose of this invention is it desirable not to complete the heat treating process but only to reheat while restraining shrinkage for a minimal duration. For example, this heat treatment can be used to increase the temperature at which a suture will shrink, effectively modulating the temperature at which shrinkage is imparted from one which is at or below normal body temperature to one that is above body temperature (e.g., 40°-50° C) . As discussed in the polymer literature (e.g., Plastic Materials , 4th Ed., by J.A. Brydson (Butterworth Scientific, 1982)), the orientation that can be "frozen-in" to the polymer structure depends upon the amount of initial orientation, the average polymer melt relaxation times between the processing/drawing temperature and the solidifying temperature (T for amorphous polymers and somewhere between T g and T m for crystallizable polymers) , and the time available for disorientation as the melt cools from the processing temperature to the solidification temperature. The initial orientation may occur, for example, due to shear stress generated as a polymer melt is extruded through a spinneret. The subsequent orientation caused by drawing the fiber (e.g., stress-induced orientation) is effected by the temperature at which drawing is performed, the rate at whic the temperature is increased to the processing/drawing temperature, the rate of drawing, the rate of quenching, an the final quenched temperature of the polymer. By heating crystallizable polymer above its glass transition temperature, the amount of stress-induced shrinkage achievable can be reduced by the crystallization or recrystallization of this crystallizable polymer at temperatures above T g . Thus, the time and temperature at which drawing is performed may be controlled to minimize crystallinity in the polymeric suture. For example, with amorphous but crystallizable polymers, the heating to the processing temperature and the rate of drawing should be sufficiently rapid to minimize crystallization of the polymer. Typically, the following phenomena exist: drawing at the lowest temperature above T g will give the greatest orientation at a given percent and rate of stretch; the highest rate of stretching will give the greatest orientation at a given temperature and percent stretch; the highest percent stretch will give the greatest orientation at a given temperature and rate of stretching; and the most rapid quench rate will preserve the most orientation induced under the given stretching conditions. Crystallizable polymers may be prevented from shrinking by heat treating, which induces an amount of crystallization into the fiber. Thus, after the fiber is melt-spun, quenched, heated to stretch, and stretched, it is briefly heated to an elevated temperature while being restrained from shrinking, and then quenched as before. While such fibers will shrink, they will require a higher temperature to induce shrinkage (a temperature closer to the heat- stabilization temperature than prior to heat stabilization) and less shrinkage can be achieved than prior to heat stabilization. Orienting is generally done at a temperatu between the glass transition temperature and the melt temperature; crystallization may be induced in some polymer compositions below the glass transition temperature by drawing. The degree of shrinkage can be regulated by the manufacturing process. For example, if the orientation is carried out at a low temperature using a high stretching rate and a rapid quench, nearly all of the stretch put into the fiber is recoverable upon heating. If all other conditions remain the same but the orientation temperature is raised, less of the original stretch is recoverable. Accordingly, the sutures of the present invention can be produced with varying ranges of shrink or stretch, thereby giving the surgeon flexibility in the selection of a suture having a shrinkage desired for a particular application. The polymeric materials used in the present invention are preferably cross-linked, such as by using irradiation o chemical reagents; irradiation is preferred, because chemical reagents tend to leave toxic residues. Cross- linking increases the temperature at which the material becomes a fluid, while still allowing for the material to b stretched or shrunk at its original (pre-cross-linked) melting point; thus, cross-linking the polymers generally enables them to be elongated or shrunk at and even above their original melting point without loosing their structur and ability to function as a suture. In addition, the stress generated from the release of orientation (i.e., the force of shrinkage) of cross-linked polymers is generally greater than thier non-cross-linked counterparts. Such a procedure results in the production of excellent shrinkable and/or elongatable sutures. The polymeric suture compositions useful herein may be cross-linked as taught by Charlesby et al. in U.S. Pat. No. 3,372,100 (incorporated herein by reference). Generally, Charlesby et al. blend a polymer with a multifunctional monomer, form a polymeric structure, and then initiate cross-linking in the structure, such as with an electron beam. Cross-linking also may be accomplished by blending a polymer with one or more multifunctional monomers and a heat-initiated catalyst; the suture can be oriented or relaxed as desired and then heated to initiate the catalyzed cross-linking reaction. Cross-linking and heat shrinking of materials can be accomplished with polyolefins as taught by Baird et al. in U.S. Pat. No. 3,126,680 (incorporated herein by reference) . Polycrystalline materials such as trans-1,4- polyisoprene may be cross-linked as taught by Yang et al. in U.S. Pat. No. 4,596,728 (incorporated herein by reference). Dienes and styrenes may be cross-linked as taught by Charlesby in U.K. Pat. No. 732,047 (incorporated herein by reference) . Materials may be cross-linked as taught by Pinner in U.S. Pat. No. 3,359,193 (incorporated herein by reference) , and as taught by Silverman (mentioned above) . "Cross-linking" and "cross-linked polymers" as used herein are intended to also include ionomers, triblock and multiblock copolymers, and hydrogen-bonding polymers which effectively act as conventionally cross-linked polymers. Illustrative radiation forms that can be used to cross link polymeric materials include electrons (e-beam, preferably having an energy of at least 10 5 electron volts) x-rays, gamma rays (e.g., using Fe 59 or Co 60 ), B-rays (e.g., using Co 60 , C 14 , P 32 , or Sr 90 ) , or ultraviolet radiation (preferably 200-270 nm) . See, e.g., U.S. Pat. No. 3,294,62 (incorporated herein by reference) . Illustrative chemical cross-linking agent-polymer combinations include: formaldehyde for phenolic resins; diisocyanates for polyesters and polyethers; polyamines for fluoroelastomers and epoxide resins; and peroxides for polyesters. Note tha these combinations presume that the existing polymeric matrix includes reactive sites for cross-linking. See, e.g., Brydson, op. cit . ; Malcolm Dole, "History of the Irradiation Cross-Linking of Polyethylene," History of Polymer Science and Technology, Ed. by R.B. Seymour (New York: Marcel Dekker, Inc. 1982); Ency . Poly . Sci . & Tech . , op cit . , Vol. 4; all incorporated herein by reference. In essence, when formulated for shrinkage, the present sutures may be envisioned as having a first configuration and then treated to provide a second configuration alterabl by the selective use of at least one source of non- frictional energy into some configuration physically betwee the first and second configurations. Cross-linking alters the suture to partially define the "first" configuration. See, e.g., Yang et al. For example, a fiber may be made into a suture by first orienting to increase tensile strength, then cross-linking to lock-in a first orientation and increase the effective melt temperature of the polymer, and then streching again to further orient the fiber. Energy can then be applied to the suture in the second configuration in a controlled manner to shrink the suture to some length between the second configuration/length and the first configuration/length at which cross-linking was introduced. Cross-linking may be performed at one or more stages in the manufacturing process to modulate the amount of shrinkage and/or elongation by which the present sutures may be altered. When a material is heated and restrained from shrinking it looses its orientation, but not as rapidly as if free to shrink. During such an orientation loss, the material exerts tension on any device restraining the material; that is, the suture generates a contractive force. The magnitude of this pull is related to the process by which the first configuration was achieved (e.g., some combination of stretching and cross-linking) and provides a measure of orientation level and/or cross-linking, although it does not always correlate well with the amount of shrinkage. Upon the application of energy sufficient to effect a change in the dimensions of the suture, the type of change which occurs to the suture's axial length and diameter is controlled largely by two factors: the conditions present at the time of energy input to effect the dimensional change; and the process by which the suture was manufactured. In order to decrease the axial length and increase the diameter of a suture, it is important that there be as little tension as practical on the suture. Bot ends of the suture should be secure, as is the case when a suture is implanted into a warm blooded animal. If the end of the suture are free, it may kink at the point of energy application, thereby preventing controlled shrinkage, and frequently leading to suture lysis. We have found that the friction between an implanted suture and the tissue in whic it is implanted is sufficient to prevent kinking of the suture when energy is applied to effect a change in dimension. That is, using the same apparatus and technique with an unrestrained suture on a table top and one that is implanted, the table top suture is very likely to kink at the point where energy is applied, but no kinking is observed with an implanted suture made according to this invention. Forceps may be inserted under the ends of the suture to be shrunk to keep it elevated from the tissue and provide some tension to prevent kinking; this mode of operation would tend to minimize possible injury to adjacen tissues caused by the energy applied to the suture. Ideally, the tissues to be sutured should be approximated together in the desired fashion before energy is applied to effect a dimensional change in the suture. The excess suture material to be shrunk is preferably exposed to allow energy application to cause shrinkage; forceps also may be used for this purpose. Alternatively, a suture which canno be exposed directly, such as a suture employed to close a scleral cataract incision that is covered by conjuctiva, ca be shrunk by using energy such as photons in the visual or near infrared region which will penetrate the tissue withou being absorbed, and which are- selectively absorbed by the suture (e.g., by dyeing the suture with a broad band absorber such as black, or an energy absorbing substance which is a selective absorber at the wavelength being used) . If the energy source provides energy to only a small volume, such as a small energy spot produced by a laser, the energy is best applied in a sweeping fashion along at least a portion of the length of the suture. If the sweep rate employed is too slow, thinning and breakage at the point of laser energy application may occur. In essence, use of the present invention requires that a controlled amount of energy be applied to desired portions of the suture to cause dimensional changes at those locale. Applying energy such as heat may first cause the suture to shrink as desired, but an energy input greater than needed to effect the desired size change can have detrimental effects on the patient and/or the suture material. Particularly regarding the suture, excess thermal energy is likely to degrade (e.g.., melt, lyse, char) the suture to the point where it must be replaced; that is, the energy input has degraded the suture to the point where it loses its integrity to function as a suture. In practice, medicine requires the skill of an artisan for many procedures; for example, whether an incision is made with a scalpel or a laser, it is the surgeon who controls the direction and intensity of energy necessary to effect the incision witho unnecessarily damaging the patient's tissues. In the use the present invention, some practice and/or experimentatio may be necessary by the skilled artisan to optimize techniques using the present sutures. Such empiricism to learn and practice new medical procedures is reasonable an customary within these arts. The energy for changing the dimensions of the suture prefereably is applied to the suture as uniformly as possible. For example, a suture ma kink because energy applied to only one part (e.g., half of the circumference) of the suture induces shrinkage in that locale before the energy has dissipated to other parts of the suture to effect a more uniform dimensional change. Th use of a sweeping motion with a small energy spot helps to more evenly distribute the energy input. Upon the application of energy, the suture will contract and its cross-sectional area will enlarge in the locale to which the energy is applied (to conserve mass) . The amount of axial shrinkage and cross-sectional enlargement can be controlled by various factors: the density of the energy employed; the length of time the energy is applied; the amount of slack present in the suture; and the maximum amount of shrinkage obtainable for given suture material (as mentioned, this depends upon the manufacturing process) . Typically upon the application of energy, such as a laser used in a sweeping fashion, the suture will contract an amount equal to the amount of slack present, and will then stop. This is ideal for the adjustment of a loose suture in vivo, as it will allow for shortening of the suture until all the excess slack is removed, and the shrinkage will stop without the production of excess tension as can frequently occur after manual suture placement. As mentioned previously, the tension caused by tissue on an implanted suture helps to prevent the suture from kinking. The tension caused by the tissue also is usually much greater than the contractive force generated by fiber when it shrinks. Accordingly, a suture is easily tensioned by sweeping a laser over some portion of its exposed area until the suture does not appear to shrink more. At the same time, if the tissues are approximated too closely together, sweeping a laser over the suture, in combination with the tension exerted by the tissues, will cause the suture to loosen; the surgeon can control the degree by which the suture loosens by observing both the suture and the approximated tissues. Thus, if a row of sutures according to this invention are implanted in a wound, the surgeon can sweep a laser over each suture to adjust the tension on all of the sutures. Such a method of using the present sutures greatly facilitates suturing because all of the sutures can be adjusted to the same tension. The ability to control multiple sutures would be expected to provide a better tissue approximation with reduced scarrin and faster healing. In order to elongate the axial length and decrease th diameter of the suture, it is important that the suture be held in a slightly taut fashion. The tensioning of the suture is best controlled using a pair of forceps either t hold the tissues together and reduce the tension on the suture, or to spread the suture and/or tissues apart to increase the tension on the suture, thereby allowing the operator to precisely control the tension applied to the suture material. The forceps serve the additional purpose of keeping the suture elevated from the tissues to reduce any potential injury which might occur during the application of energy to cause shortening. Both ends of th suture should be secure, as is the case when a suture is implanted into a warm blooded animal. If a small energy spot is used, such as that produced by a laser, the energy should be applied in a sweeping fashion along the length of the suture, usually at a faster rate than during shrinkage. During stretching, the use of slower sweep rates such as those used during shrinking, may likely result in rapid thinning and breakage at the point of energy application. In essence, we have found that altering the suture to a greater length usually requires exercising a greater degree of control by the surgeon. Once energy is applied in combination with tensioning, the suture will show evidence of elongation and thinning. The rate of thinning is dependent on similar factors used to determine axial shrinkage and cross-sectional enlargement, namely: the density of the energy employed; the length of time the energy is applied; the amount of tension present in the suture; and the maximum amount of stretch obtainable for the given material used. Typically, the suture will stretch at the point of energy application. As the area of supplied energy is swept along the suture, further stretching will occur until the tension is relieved or the entire suture is treated. For instances where the amount of stretch is within the amount possible for the material used, this is an ideal property for the adjustment of a tight suture in vivo, as it will allow for only enough stretching to relieve the excess tension, resulting in a well-tensioned suture. Unlike shrinkage, the amount of stretch is not entirely predetermined by the manufacturing process. As additional energy is applied, stretching can usually be continued, making the suture thinner and thinner in cross-sectional area, until suture degradation occurs. However, in order to maintain reasonable tensile strength in the suture, only a controlled amount of stretching is feasible. This amount is largely controlled by the manufacturing process, and at the expense of the patient the surgeon must not exceed it. It should also be noted in connection with the above discussion regarding elastic and permanent deformation that the suture still has an elastic limit and a break point; the break point may change because a portion of the suture is having energy applied to it (and that region is likely the limitin factor for determining the elastic limit and break point) . It is important to note that materials can be formulated in less oriented fashion, and through the application of energy, the suture can be stretched to increase the orientation. Then by cooling the suture, such as by air or water bath, the suture can be maintained in an elongated condition. Different processes can be used to make different type of sutures. Three processes are briefly illustrated with respect to a starting fiber that is lightly oriented and cross-linked. In the one method, the suture is manufactured to provide the greatest amount of shrinkage possible. This characteristic is imparted during manufacturing through the use of a high degree of stretching (e.g., 400% of the starting length) with rapid quenching to achieve a high degree of orientation and a large change in length. The us of this type of suture is ideal for vascular and bowel anastomoses, as previously described, as well as tissues which are edematous at the time of surgery, such as occurs after trauma or the injection of local anesthetic agents into the wound margin, in which case the suture may slacken as the inflammation decreases post-operatively. In general the amount of shrinkage that may be achieved from a suture manufactured by this method is from about 5 to 75%, preferably from about 40 to 60% of the suture after stretching. In other words, a one-inch suture can be stretched to four inches and then shrunk back to one inch (or any amount between one inch and four inches) . A second method of manufacturing involves the production of a material which can be elongated and/or shrunk through the application of energy at the physician's need. This characteristic is imparted by employing only a part of the total amount of stretch that could be achieved in the fiber (e.g., 200%-300% of the starting length). The use of this type of suture is best suited for microsurgical procedures, or delicate skin closures, in which placement o the suture is difficult and replacement thereof may result in undesirable trauma and scar formation; adjustment of improperly tensioned sutures can be performed at the time o surgery, without the need for replacement and further tissu trauma. An example of a microsurgical procedure for which this is well-suited is cataract surgery. An improperly tensioned suture currently must be replaced, resulting in further damage to the delicate ocular tissues, greater post- operative inflammation, and increased operative time. Moreover, sutures that are well-tensioned at the time of surgery frequently result in undesirable astigmatic refractive errors in the post-operative period. Use of adjustable sutures in this setting provides a significant benefit, as they allow the surgeon to precisely adjust the wound tension and the resulting astigmatic refractive error both intra-operatively and post-operatively. A suture so made may be shrunk about 5 to 50%, preferably from about 15 to 40%, and may be elongated by approximately the same amounts, based on the stretched suture length. Therefore, by stretching the suture some intermediate amount between the starting configuration and the maximum amount of elongation, the stretching energy can be recovered to shrin the suture, and the suture may be further elongated up to the maximum amount of elongation. For example, a one-inch suture can be stretched to about three inches, and afterwards shrunk back to about one inch and/or elongated t about four inches. In a third procedure, sutures can be manufactured to allow for the maximum amount of elongation. This is achieved during manufacturing by using the minimal amount o stretch necessary to impart sufficient orientation so as to provide adequate tensile strength to the suture material (e.g., up to 100% of the starting length; initial stretchin may not be necessary if drawing during spinning imparts sufficient orientation to provide adequate tensile strength) . Use of these sutures is ideally suited for tissues in which significant post-operative edema is expected, such as occurs after rotational skin flaps. In general, the amount of elongation imparted by this method i about 5 to 100%, preferably about 40 to 60%, of the origina length as an amount sufficient to increase the tensile strength, thereby allowing for significant elongation of th suture by the surgeon up to the maximum amount obtainable. For example, a one-inch suture which has sufficient orientation so as to provide adequate tensile strength without additional stretching of the suture material can be elongated up to about two inches in use. Various forms of energy may be imparted to the inventive sutures to effect a dimensional change. Energy is typically applied radiatively, generally using thermal energy or, more preferably, photon energy from a high energy light source, such as a laser. A variety of energy sources can be used to apply energy to the sutures. Specific energy sources include, but are not limited to, ultrasound, energy in the electromagnetic spectrum including monochromatic coherent light, monochromatic non-coherent light, polychromatic coherent light, polychromatic non-coherent light, microwave energy, and electrical energy. The energy may be applied in a continuous or a non-continuous fashion. Thermal energy sources may also include a hot air gun, a warm water bath, electrocautery, or a warm compress. Most preferred are the use of lasers including, but not limited to, Nd:YAG (1064 nm) , frequency-doubled Nd:YAG (532 nm) , helium-neon (594, 632 nm) , helium-selenium (460, 480, 520 nm) , argon (477, 488, 515 nm) , krypton (467, 531, 568, 647 nm) , xenon (526, 597 nm) , dye-laser (400-960 nm) , and diode [e.g., GaAlAs] (810 nm) ; other lasers which emit in the visible and near infrared region are also preferred high energy photon sources. Carbon dioxide (10,600 nm) and THC:YAG (2,100 nm) may also be used, but likely pose a greater risk of tissue damage. Thus, the preferred embodiments include photons as the energy which is applied to the suture. As such, both ionizing and non-ionizing radiation are useful for practicing this invention, althoug non-ionizing radiation is much preferred because of its reduced health risk. As used herein and in the appended claims, the source of "non-frictional energy" is intended t include one or any combination of these exemplary sources. See generally Joseph Silverman, Radiation Processing: The Industrial Applications of Radiation Chemistry. Journal of Chemical Education , Vol. 58, No. 2, pp. 168-173 (Feb. 1981) incorporated herein by reference. As mentioned, it is important to control the amount of energy applied to the suture to avoid degrading the suture. This includes not only the energy applied (such as by laser) for shrinking a suture, but also the mechanical tensioning energy applied in combination with another energy source fo elongating a suture. In practical terms, a suture that is able to undergo a dimensional change of only 5% likely woul be of limited value, and the ability to undergo a dimensional change of 500% likely would be excessive. It i preferred that the sutures of the present invention be capable of undergoing a linear dimensional change of 100-300%, more preferably about 150-250% (i.e., approximately 200%) . A suture material for the apposition of tissues in accordance with the present invention must be non-toxic whe placed in warm blooded animals, and generally should posses a melting point of from about 50° to 300° C, preferably fro about 50° to 150° C, to allow for less intensive energy application and thereby minimize damage to biological tissues during energy application. Examples of suitable suture materials include natural and synthetic polymers. Preferred natural polymers are generally cellulosic, such as vegetable fibers from cotton, linen, and hemp, or proteinaceous, such as wool, silk, and collagen. Synthetic polymers may be based on naturally occuring monomers or polymers, and include materials such as Rayon (regenerated cellulose) , cellulose acetate butyrate, and Azlon (regenerated protein) . Synthetic polymers may be in the form of homopolymers, various types of copolymers including block and graft copolymers, or polymer blends. Exemplary synthetic polymers include: acrylic acid esters such as poly(acrylic acid), poly(aerylamide) , poly(aerylonitrile) , poly(methacrylic acid) , poly(methyl- methacrylic acid) , poly(hydroxyethyl methacrylate) , and the like; polyamides such as Nylon 4, Nylon 412, Nylon 6, Nylon 66, and the like; polyolefin homopolymers and copolymers, either substituted or unsubstituted, such as poly(ethylene) , poly(propylene) , poly(butylene) , poly(tetra- fluoroethylene)s (PTFE) including copolymers such as tetrafluoroethylene-hexafluoroproylene copolymer (e.g., TEFLON-FEP available from DuPont, Wilmington, DE) , poly(vinylidene fluoride), poly(vinyl fluoride) (PVF) , poly(vinylidene chloride) , poly(vinyl chloride) (PVC) , poly(vinyl acetate) , and the like, including poly(dienes) such as poly(isoprene) and hydrogenated derivates (e.g., KRATON 101, a styrene-butadiene elastomer) , poly(styrene) , and derivatives thereof; polyesters including poly(N-vinyl- pyrrolidone) (PVP) and poly(ethylene terephthalate) (PET) ; poly(ester) and poly(ether) derivatives including poly(urea)s, poly(urethane)s, poly(urea-urethane)s, poly(phenylene oxide)s, poly(phenylene sulfide)s, poly(alkylene ketone)s, poly(alkylene sulfone)s, poly(ether sulfone)s, poly(ether ether ketone)s (PEEK), and the like. Still other varied polymer compositions are suitable, including silicone rubber, liquid crystal polymers such as poly(benzoxazole) , and absorbable polymers such as poly(lactic acid) . Specific energy sensitive materials which are known to be biocompatible belong to the general classes of polyethylenes, polypropylenes, polyesters, and poly(methylmethacrylate) . While the foregoing polymer compositions are usually listed above as homopolymers, various copolymers may also be suitable; two preferred copolymers include poly(ethylene/vinyl acetate) (EVA) and poly(ethylene/vinyl alcohol) (EVOH) . The materials may be modified by copolymerization with up to about 40% of one or more comonomers, including, but not limited to, polyesters, poly(vinyl fluoride), polypropylene, polyethylene, and poly(methyl methacrylate) . In all cases, the polymer composition must be non-toxic and biocompatible (e.g. , preferably hypoallergenic) . Preferred fibers are polypropylene fibers. Crystallizable polymers which are not cross-linked, an especially those which have are essentially amorphous, in which shrinkage immediately after implanation is not desired, are preferably chosen from those having a glass transition temperature near and preferably at least 10° C above normal body temperature (i.e., 37° C for humans). Crystallizable polymers which are cross-linked may be chosed from those having a glass transition temperature well below body temperature and a crystalline melt temperature at least 10° C above body temperature because cross-linking can virtually eliminate shrinkage below the pre-cross-linked crystalline melt temperature. Amorphous polymer compositions for the novel sutures may be chosen having a glass transition temperature (T g ) in a desired relationship to the ambient temperature. That is, the amorphous polymer may be chosed with a less than or equal to the normal body temperature of the patient. As such, the suture can be induced to shrink immediately after implantation as a result of the thermal energy imparted from the patient. In contrast, shrinkage immediately after suturing can be avoided by choosing a composition having a T g higher than the normal temperature of the patient. Various basic parameters may be altered to achieve a suture having certain desired properties in addition to capacity for dimensional change. The molecular weight of the polymer may be increased with an accompanying increase in the stiffness and strength of the suture. Likewise, increasing the density of the polymer will result in an increase in the strength and stiffness of the fibrous suture. Still further, the stereoconformation of the polymer can be altered .to impart desired gross and/or surface characteristics to the suture. For example, isotatic and syndiotactic polypropylene provide a polymeric structure that is readily crystallizable, whereas atactic polypropylene is soft, elastic, and may be sticky. The range of polymers useful for making sutures may be enhanced by the addition of one or more energy absorbing substances (i.e., dyes and/or chromophores and/or pigments) to the fiber suture. For this purpose, broad band absorber such as a black dye, or selective absorbers for a particula energy source, may be employed. Preferably, the energy absorbing substance is chosen on the basis of its ability t absorb light energy at the wavelength of a specific laser o other high energy light source. The choice of a laser or other high energy source whose light output is poorly absorbed by biologic tissue, but well-absorbed by the energ absorbing substance in the suture, will ensure minimum collateral damage to adjacent tissue. This would be the case even if the polymer required a temperature of shrinkag that was well above that which causes tissue necrosis, because of the combined rapid rate of energy absorption by the energy absorbing substance in the suture and lack of energy absorption by the adjacent tissue. Example of dye-laser combinations, include, but are no limited to: fluorescein isothiocyanate (absorbance: 490 nm and an argon laser operating at 488-514 nm; green compounds which absorb in the region of 808 n , such as indocyanine green (absorbance when dissolved in water: 770 nm) , and a diode laser operating at 808 nm; various silver compounds including silver nitrate (broad absorbance) and a krypton laser (676 nm) ; dye compounds such as rose bengal and corresponding dye lasers; and logwood black and India Ink may also be utilized to absorb light from any of the aforementioned lasers. Inorganic pigments such as carbon black, iron oxides (yellow, brown, and red, for example) , and chromium oxides (green) are also useful. In general, various energy absorbing substances (specifically dyes and color additives) are disclosed in 21 C.F.R. Ch. I (4-1-91 Edition) , incorporated herein by reference [United States Code of Federal Regulations, Title 21]. Although these Federal Rules limit the range of dyes suitable, for example for intraocular use, all of the biocompatible dyes disclosed therein may be useful with the inventive sutures. For example, food colorings such as canthaxanthin (and other β-carotene derivatives) , carmine, ferrous gluconate, enocianina (grape skin extract) , tagetes extract, drug colorings such canthaxanthin, carmine, and chromium oxide greens, cosmetic colorings such as carmine, β-carotene, dihydroxyacetone, iron oxides, and guanine, and medical device colorings such as carbazole violet, pol (hydroxyethyl methacrylate)-dye copolymers, and the various contact lens dyes are useful in the present invention. It will be appreciated that the wavelength of the high energy photon source may be chosen to minimize the amount of energy absorbed by tissues, and a comparable energy absorbing substance may be chosen to transfer as much of the photon energy from the .source to the suture as possible. The wavelength of the high energy photon source can be chosen so that energy can be imparted to a suture through layers of tissue; that is, for example, a suture can be subcutaneously altered. The patient's own pigmentation wil effect how much of the photon energy is absorbed by the tissues rather than the suture. Because of the efficiency of melanin in absorbing various wavelengths, transcutaneous in vivo alteration of the present sutures is more preferabl performed on patients with less pigmentation (i.e., a lower risk of tissue damage) . In general, no energy absorbing substance is necessary when the energy applied to the suture is infrared radiation. When UV light is used as the energy source, suture compositions including aromatic or resonant structures, such as phenyl or naphthyl groups or ketone or carbonyl groups, generally do not require an energy absorbing substance. Useful energy absorbing substances should not be toxic to the patient. They should be stable when exposed to relatively high levels of energy input; that is, they do not release toxic radicals or by-products, and do not decompose, when exposed to high energy levels. However, in certain instances it may be advantageous to employ an energy absorbing substance which decomposes into non-toxic residues or vapors after exposure to high energy levels for a short period of time. Sutures colored with such energy absorbing substances could be adjusted once, and would not be at risk of further adjustment (e.g., loosening) should the patient be exposed to high energy photons subsequent to the intended adjustment. It is also possible to use a combination of energy absorbing substances to effect desired dimensional changes to the suture. For example, a suture may include one energy absorbing substance which enhances energy absorption at a specific wavelength to promote shrinkage or elongation of the suture, and another energy absorbing substance sensitive to radiation at a different wavelength which, when irradiated, will further cross-link the suture to maintain an existing dimension. As used herein, the ter "energy absorbing substances," including dyes, chromophores, and pigments, is intended to mean some substance that absorbs photon energy, especially at some desired wavelength, to facilitate the dimensional change to the suture. In particular, the combination of an energy absorbing substance in the suture and diode laser may be employed. Delivery of the laser energy is preferably by means of a fiber optic cable. The energy density is preferably between 1 and 40 Watts/cm 2 , more preferably between 5 and 20 Watts/cm 2 , delivered in a controlled manner. The present invention is also applicable to absorbable sutures. Presently existing absorbable sutures may shrink up to 2/3 of their original length when subjected to heating; for example, collagen usually starts to shrink when the temperature reaches about 65° C. Exemplary absorbable suture compositions include collagen, a ino acid polymers and copolymers such as polyglycolide (polyoxyacetyl) and poly(glycolic acid) (e.g., Dexon™) and lactide and glycolide copolymers (e.g., Polyglactin 910), polydioxanone (poly(2-oxyethoxyacetyl) ) , cellulosics, and catgut (usually from sheep intentines) . The proteinaceous or protein-like structure of these sutures means it is likely that energy applied to the suture may denature or "cook" the suture. I is generally only practical to shrink these sutures up to 20% of their original length without such detriments as a significant reduction in tensile strength, excessive rigidity, charring, and dehydration. Absorbable sutures such as poly(lactic acid) and Polyglactin 910 may be formulated to shrink at different temperatures through cross-linking and modulation of the types and amounts of the amino acid monomers employed. Another type of absorbable suture can be comprised of keratin, such as is present in wool. Wool fibers have been shown to supercontract when held in steam and rapidly stretched and relaxed. E.g., W.G. Crewther et al., "Effect of Electrolytes on the Rate of 'Supercontraction* of Wool Fibres," Nature , Vol. 178, No. 4532, pp. 544-5 (Sep. 8, 1956) ; incorporated herein by reference. Existing absorbable sutures do not contain suitable energy absorbing substances to allow their adjustment with photonic energy delivered at wavelengths which are not absorbed by the adjacent tissues. Absorbable sutures may have an energy absorbing substance incorporated therein and/or thereon according to this invention to enhance the absorption of energy from a particular source. The enhance absorption means that the surrounding tissue is less likely to be injured by the applied energy. Of particular value are black dyes, which absorb energy from less expensive lasers such as diode lasers. Thus, absorbable sutures can be shrunk by this invention. As mentioned, the skilled artisan may require some routine experimentation to determine the amount and rate at which energy is applied to the suture to assure that it maintains sufficient integrity to function as a suture after shrinkage or elongation. Thus, even though absorbable sutures may undergo some degradation upon shortening, the suture integrity can be maintain by a controlled application of energy. An energy absorbing substance may be applied to the surface of the novel suture by various coating techniques known. Alternatively, the energy absorbing substance may b incorporated directly into the polymer chain or merely mixed with or dispersed into the polymer melt or solution that is spun or drawn into a suture. Thus, the energy absorbing substance may be dissolved (e.g., a liquid dye) or dispersed (e.g. , a solid dye or pigment) in the polymer, or may be reactively joined pendant to the polymer backbone or to the surface of the suture. The suture also may contain a photodegradant, or be comprised wholly or partially of a photodegradable polymer. A photodegradant will destructively react with the polymer matrix upon exposure to light, thereby decreasing the strength of the suture and allowing additional elongation. The photoinitiated reaction may be oxidative, hydrolytic, or others known. An examplary photodegradant is a single component vinyl ketone polymer, although combinations of initiators and degradants may be used. The photodegradatio products should be non-toxic. Various conventional additives may be added to the suture, subject to the condition that such additives are no toxic (and do not lead to toxic by-products) and do not compromise the integrity of the fiber to the point where it is not useful as a suture. For example, a plasticizer may be added to assure the desired pliability of the suture. A typical additive for implantable devices is a radio-opaque dye to allow visualization of the suture by x-ray photography. Light stabilizers are preferably added such that radiative energy other than specifically desired for altering the suture dimensions does not adversely effect th integrity of the suture and does not undesirably initiate suture shrinkage or elongation. Polyolefins are particularly susceptible to unintended photodegradation. Exemplary light stabilizers include hindered amines and carbon black. Antioxidants may also be employed advantageously; for example, hindered phenols (e.g., Irganox TM) , thi•oesters, and phosphites. Other addi•tives which are commonly employed with polymers, such as coupling agents (e.g., for dispersing an inorganic pigment into a polymer), lubricants (e.g., spin finishes), release agents, elastomers, and pore forming agents (for providing microporous fibers) , may be used. The present sutures may also be formulated to include a releaseable prophylactic or therapeutic agent. To a large extent, useful "drugs" added to the suture depend upon the particular tissue(s) in which the suture is used and the area of the wound. That is, for suturing the skin, it is more likely that an antibiotic would beneficially be incorporated into the suture, whereas it is more likely tha an anticoagulent or angiogenesis factor would be useful for sutures used internally. Thus, the prophylactic or therapeutic agent may include, by way of example, enzymes such as streptokinase, che otherapeutic agents such as methotrexate and 5-fluorouracil, angiogenesis factors, insulin, hormones such as growth factors, estrogen, and progesterone, colony stimulating factors such as granulocyt colony stimulating factor, erythropoitin, anti-inflammatory agents such as steroids or non-steroidal anti-inflammatory drugs (NSAIDs) , anticoagulants and antithrombotics such as heparin and glycosaminoglycans, vasoactive substances such as adrenalin, antibiotics and/or antivirals such as tobramycin and 9-substituted guanine derivatives, and immune system modulators such as interferon. One or any compatible combination of these agents may be used in the present sutures. These agents may be incorporated into the suture material by known techniques, including prior to spinning, and subsequent to suture fabrication by attachment to the surface or by solvent-assisted penetration of the fiber. The present sutures may be fabricated with desired ministructures such as core-shell, islands-in-the-sea, hollow, (microporous)core-(microporous)shell, (microporous)core-(solid)shell, microporous hollow fiber structures, and similar structures. Core-shell fibers generally include a monofilament (the core) surrounded by another polymer (the shell) , and are typically made by co-spinning. An islands-in-the-sea structure is analogous to the core-shell structure but includes a matrix shell portion having a plurality of monofilamentary core fibers. Each of the separate polymer components (e.g., the core, t shell, and separately the matrix and each monofilament in islands-in-the-stream structures) may be formulated with a energy absorbing substance or other additive to achieve desired properties. One important consideration in composite fiber structures is that the separate components be compatible at their interface to avoid physical separation. Likewise, separate suture fibers may be forme into a braided or a woven structure. An illustration of a useful core-shell configuration a porous, water-swellable core polymer surrounded by a fluid-impervious shell polymer such as a polyolefin. Upon ablation of the shell component (after the suture has been implanted) , which process can be enhanced by incorporating an energy absorbing substance into the shell component, th porous core portion would be exposed. Thereafter, water o an aqueous solution can be applied to the implanted suture to swell the core portion, thereby resulting in an increas in its cross-sectional diameter and its length. This aqueous solution may contain a prophylactic or therapeutic agent which is then absorbed into the swellable polymer. Alternatively, the core portion can be fabricated with a pharmaceutical agent incorporated therein, whereby ablation of the shell portion allows for the agent to contact and diffuse into adjacent tissues. A shell-portion also can be created subsequent to spinning or fabrication of the suture by dipping and coating methods presently known. Thus, a suture according to this invention also may be protected from gases and fluids, and swelling can be avoided, by usin a shell or coating of a material impervious to the undesire material. The present invention thus also contemplates the use of a suture-like structure as a drug delivery system, and implantation of such a structure as a method for delivery pharmaceutical agents. A suture according to this invention can be provided with a pharmaceutical agent as described. In one embodiment, a notch (or other functional equivalent to a score) is made proximal from the distal end of the suture such that the distance from the notch to the distal end is the length of the suture-like structure to be implanted. The entire structure is then implanted, for example subcutaneously or intramuscularly, after which the surgeon applies direct pressure on the implanted suture just distal from the notch and the proximal end of the suture can be manipulated to break off the implanted portion at the notch. In another embodiment, by providing a suture in combination with an energy absorbing substance such that it will be sensitive to energy that is not normally absorbed by the tissues, a desired portion of the suture-like delivery system can be provided, for example, by lysing the implanted device with a laser through the skin and other tissues. A preferred embodiment is a suture-like delivery system comprising a drug-impregnated core and a cross-linked shell the shell is preferably comprised of poly(vinyl alcohol). With a core-shell type structure, the shell may be designed to be absorbable or may be selectively ablated by the surgeon to expose the pharmaceutical-impregnated core to th surrounding tissues. The present invention also contemplates sutures that are dimensionally alterable through the use of solvents. Solvent shrinkable polymers have been described, for example, by Patterson in U.S. Pat. No. 3,429,794, incorporated herein by reference. As described by Patterson, certain crystalline polymers which are normally soluble may be cross-linked, subsequently oriented, and the shrunk by contact with a solvent for the non-irradiated polymer. For example, non-irradiated poly(ethylene oxide) is completely soluble in water. However, a partially cross linked and then oriented poly(ethylene oxide) suture will shrink when contacted with water (i.e., the solvent) but will not dissolve. Such sutures are particularly advantageous because no photon or thermal energy is require to effect the change in dimension; accordingly, there is no risk of tissue damage that may insue from using a high energy device. It is also advantageous that a non-toxic, preferrably hypoallergenic solvent can be used to change th suture dimensions without risk to the patient. A suture that is dimensionally alterable by use of a solvent may also be alterable by the use of at least one source of non-frictional energy. For example, if the cross linked, oriented poly(ethylene oxide) suture that is shrinkable by the use of water has been oriented only partially (i.e., drawn to less than the maximum length), th suture is also elongatable (and possibly also shrinkable) b the use of light or thermal energy. Therefore, after implantation such a suture may be shrunk by irrigating with water and, if necessary to reduce the tension, elongated by tensioning and sweeping a laser over the suture. EXAMPLE 1 3 strips of irradiated cross-linked polyethylene plastic (Frost King" Shrink-Fit Window Insulation Kit manufactured by Thermwell Products Co., Paterson, NJ) measuring 5.79 ± 0.07 inches x 1.0 inch were rolled into a cylinder having a diameter of 3/16 inch. The strips were placed into a gas oven and heated at 185° F and for 12 minutes. The materials were removed from the oven allowed to cool and then measured. The results are shown in Table 1. The three samples were then placed into the oven and heated to a temperature of 230° F for 17 minutes. The samples were removed allowed to cool and then measured with the results shown in Table 1. The three samples were again placed into the oven and heated at 300° F for 10 minutes and measured in the same w as described above. As shown in Table 1, the 3 strips showed a decrease i their length based on the amount of exposure to heat. As shown by the results in Table 1, the suture material can be shortened in a controlled amount by the amount of heat applied to the material. TABLE 1 Pre-Heat I 185°F I 230°F I 300°F 5.79 ± 0.07" 5.44 ± 0.06" 4.79 ± 0.07" 1.54 ± 0.09 COMPARATIVE EXAMPLE 1 3 6" strips of polypropylene 0 and 5-0 suture (Prolene manufactured by Ethicon, a division of Johnson an Johnson) were treated and measured in the same manner as Example 1. The results are shown in Table 1A. The results shown in Table 1A indicate that the comparative sutures do not change dimensions at low temperatures, and only show an insignificant reduction in length at temperatures which expose the surrounding tissues to possible damage. TABLE 1A EXAMPLE 2 An irradiated cross-linked polyolefin-containing thermoplastic (manufactured by SPC Technology, Chicago, IL) , dyed black, was fashioned into thin strips, with a 1.0 mm cross-sectional area. The strips were then subjected to heated air of around 150° C, while gentle traction was applied. This resulted in a 25% increase in the length, a commensurate decrease in cross-sectional area, and a more circular cross-sectional profile. The resulting strips had a configuration, and handling characteristics similar to 0 sutures. The tensile strength before break was moderate as compared to 0 polypropylene sutures (Prolene TM manufactured by Ethicon, a division of Johnson and Johnson) The suture material was cut into 6" lengths. The suture was held in a loose fashion, similar to that seen postoperatively in the case of a loose skin suture. Laser energy was applied using a Coherent TH 810 Di•ode Laser (Coherent, Inc., 3270 West Bayshore Road, P.O. Box 10122, Palo Alto, CA 94303) emitting 300 mW, for 1.0 second duration at a repetition rate of 0.2 seconds through an Acculite™ Endoprobe Delivery System with a spot size of 2 mm, and an energy density of 10 Watt/cm . The laser spot was applied in a sweeping fashion along the axis of the suture. The sweep speed was maintained at 1 cm per 5-10 seconds, to prevent suture melting and lysis and boiling of the suture material. When laser energy was applied and the suture was not held in place, a kink occurred at the point of laser energy application, preventing controlled shrinkage, and frequently leading to suture lysis. On the application of the laser energy, the area aroun the spot showed evidence of contraction, and enlargement of its cross-sectional diameter. The amount of axial shrinkag and cross-sectional enlargement were controlled by four factors: (1) the density of the energy employed; (2) the length of time the energy is applied; (3) the amount of slack present in the suture; and (4) the maximum amount of shrinkage obtainable for the given material used. The maximum reduction in length possible for the sutures used in this example was 66%. The suture contracted an amount equal to the amount of slack present in the suture material, and then stopped. This is ideal for the adjustment of a loose suture in vivo, as it will allow for shortening of the suture until all the excess slack is removed, and will stop without the production of excess tension as can frequently occur after manual suture placement. The amount of shrinkage obtained using the suture material described in this example, on exposure to the laser energy density as described above, is shown in Table 2. TABLE 2 As a control, a 6" strip of 0 polypropylene suture (Prolene TN Ethicon) was dyed with black permanent marker (E Marko™, paper Mate) as an energy absorbing substance. On heating the suture, the suture contracted at the site of laser application, and then formed a ball of plastic on either side of the spot. Overheating resulted in suture lysis (i.e., cutting). Shrinkage could not be achieved. I was found that the axial length of existing polypropylene suture cannot be adjusted through dye enhancement in combination with a diode laser in the fashion similar to that used for the suture described in the present invention EXAMPLE 3 The same suture material described in Example 2 was dyed black and fashioned into sutures in the same manner as in Example 2, except that the sutures were not elongated before laser treatment. The suture material was cut into 6" strips. The suture was held in a slightly taut fashion. Laser energy was appli •ed usi•ng a CoherentTM 810 Diode Laser emitting 300mW for 1.0 second duration at a repetition rate of 0.2 seconds through an Acculite™ Endoprobe Delivery System with a spot size of 2 mm. The energy spot was applied in a similar fashion as was described in Example 3. The laser spot was applied in a sweeping fashion along the length of the suture. The sweep speed was maintained at 1/2 to 1 cm per second, in order to prevent suture melting and lysis and boiling of the suture material. During stretching, the sweep rate of the laser was more important than during shrinking. During stretching, the use of slow rates such as those used during shrinkage, frequently resulted in rapid thinning and breakage at the point of energy application. On the application of laser energy, the suture showed evidence of elongation and thinning. The maximum amount of stretch possible without resulting in more than a moderate reduction in strength, was 30%. Additional stretching was possible, but generally resulted in an unacceptable reduction in tensile strength. Typically, on the application of energy in a sweeping fashion, the suture would stretch at the point of energy application. As the laser was swept along the suture, further stretching would occur until the tension was relieved or the entire suture was treated. The amount of stretching obtainable using the suture material described in this example, on exposure to the lase energy density as described above, is shown in Table 3. TABLE 3 EXAMPLE 4 The same suture material described in Example 2 was fashioned into sutures in the same manner as in Example 3. In Example 3, the sutures were elongated through the application of laser energy. In this example, the same sutures were shortened. The suture material was cut into 6 strips. The suture was held in a loose fashion. Laser T « energy was applied using a Coherent 810 Diode Laser emitting 300mW for 1.0 second duration at a repetition rate of 0.2 seconds through an Acculite™ Endoprobe Delivery System with a spot size of 2 mm, and an energy density of 10 Watts/cm 2 . The laser spot was applied in a sweeping fashion along the length of the suture. The sweep speed was maintained at 1 cm per 5-10 seconds. On the application of the laser energy, the area around the spot showed evidence of contraction and enlargement of the diameter. The amount of shrinkage obtained using the suture material described in this example, on exposure to the laser energy density as described above, is shown in Table 4. TABLE 4 This example demonstrates that sutures can be manufactured in a fashion which allows them to either be elongated or shortened, depending on the desired application. Elongation is accomplished by heating the suture when it is under tension. Shortening is accomplished by heating the suture when the suture is loose. EXAMPLE 5 The same suture material as described in Example 2 was treated in the same manner as in Example 2. A 1.5 cm incision was made in freshly harvested rat skin (Bioproducts for Science, Inc., Indianapolis, IN). Water was injected into the tissue adjacent to the incision using a 25G needle to simulate edema. The incision was closed with three sutures, in a well tensioned fashion. The skin around the suture site was then pressed between an absorbable material until the injected fluid was extracted, thereby resolving the "tissue edema". The distance between insertion points of the suture into the skin were measured as was the total length of the suture. The amount of "loose" or "excess" suture was determined by subtracting the distance between the suture insertion points from the total length of the suture. Diode laser energy (810nm) was applied in a similar fashion as described in Example 2, until there was no excess suture, and it was well tensioned. Suture strength was then grossly tested by pulling on the two ends of the wound with forceps, and was found to be similar to the preshrunk strength. The results are shown in Table 5. Total Length in mm = 2 x loop length. "Point-to-Point Distance" is the distance in mm between insertion points. "Excess" is the excess suture length in mm = (Total Length) - (Point-to-Point Distance). On visual examination, there was little evidence of collateral thermal injury or charring of the tissues after the laser adjustment of the sutures. EXAMPLE 6 The same suture material as described in Example 2 was fashioned into sutures in the same manner as in Example 3. A 2.0 cm incision was made in freshly harvested rat skin (Bioproducts for Science, Inc. Indianapolis, IN) . The incision was closed with three sutures, in a well tensioned fashion. The suture length was then measured. An injection of water was made into the tissue surrounding using a 25G needle to simulate tissue edema as can occur post-operatively, making the sutures taut. The bent tips of a pair of forceps were inserted under the suture, and spread using a moderate amount of force. This served to provide control during stretching, and also elevated the suture off the skin surface to prevent collateral thermal injury to th tissues. Diode laser energy (810nm) was applied in a similar fashion as described in Example 2, until the tensio on the suture created by the "tissue edema" was relieved. The skin around the suture site was pressed between an absorbable material until the injected fluid was extracted, thereby resolving the "tissue edema". The length of the suture loop was measured. The amount the suture had been elongated was determined by subtracting the original length from the suture length after "resolution" of the tissue edema. The results are shown in Table 6. TABLE 6 All lengths are in millimeters. On visual examination, there was no evidence of collateral thermal injury or charring of the tissues as a result of the laser adjustment of the sutures. EXAMPLE 7 A sheet composed of a combination of polyethylene and polyvinyl acetate (3M Window Insulator Kit, Household Products Division/3M Company, St. Paul, MN 55133) were cut into approximately 1 mm wide strips, with a thickness of less than 0.1 mm, and a length of 6". A black permanent marker (El Marko TM, Paper Mate) was used as the energy absorbing substance to dye one side of the plastic, resulting in black 6" model sutures. Although similar in width to 0 sutures, these model sutures were much thinner and showed only minimal tensile strength, as compared to 0 polypropylene suture (Prolene TM, Ethicon) . The suture was held in a loose fashion, similar to that used in Example 2. Diode laser energy was applied in a similar manner to Example 2, except that the sweep speed was increased to 2-5 seconds per cm. On the application of the laser energy, the area around the spot showed evidence of contraction. The amount of shrinkage was controlled by the same factors as described in Example 2. The maximum reduction in length possible for the sutures used in this example was 66%. The amount of shrinkage obtained using the suture material described in this example, on exposure to the laser energy density as described above, is shown in Table 7. TABLE 7 EXAMPLE 8 Polyvinyl chloride (PVC) (Sσotchtite'M" 105° C, 3M Company) was used to fashion sutures into strips which were approximately 0.7 mm wide and 0.4 mm thick. These sutures were cut into 6" strips. These sutures were similar to 0 sutures, except that they were rectangular in cross-sectional area. The suture was held in a loose fashion, similar to tha used in Example 2. Diode laser energy was applied in a similar manner to Example 2, except that the sweep speed wa decreased to 10-15 seconds per cm. On the application of the laser energy, the area aroun the spot showed evidence of contraction and visibly swelled in diameter. The amount of shrinkage was controlled by the same factors as described in Example 2. The maximum reduction in length possible for the sutures used in this example was 50%. The amount of shrinkage obtained using the suture material described in this example, on exposure to the lase energy density as described above, is shown in Table 8. TABLE 8 EXAMPLE 9 A sheet composed of polypropylene (Insulating Shrink- Film™, Manco, Inc. , Westlake, OH) was prepared and treated in the same manner as Example 7. The results are shown in Table 9. TABLE 9 The present invention also contemplates composite suture articles such as braided or woven structures. By using a combination of one or more of the novel sutures described above, which can shrink, shrink/elongate, or elongate, a composite suture can be formulated that is dimensionally alterable. Still further, this composite suture may contain one or more suture elements that are not dimensionally alterable, yet the entire suture structure remains dimensinoally alterable. In one embodiment, conventional sutures can be braided or helically coiled about a central suture made dimensionally alterable according to this invention; this central suture may also include an energy absorbing substance that absorbs at a specific wavelength. Especiall if there is some bonding (e.g., heat sealing, adhesive bonding) between the outer coiled sutures and the central suture, although not required, the conventional sutures around the circumference are under compression. After implantation, the surgeon can use a laser at the wavelength for which the energy absorbing substance was chosen to selectively ablate portions of the central suture. The remaining coiled sutures would then uncoil, effectivly lengthening the composite structure in the area in which th central suture was ablated. In yet another embodiment, the helically coiled suture are sutures made according to this invention that are adapted to shrink. As such, these coiled sutures are fabricated with an energy absorbing substance that absorbs energy at a different wavelength than that to which the central suture (and/or the energy absorbing substance in the central suture) is sensitive. Accordingly, after ablation of the central suture to effect elongation of the composite structure, a different laser can be used to shrink the remaining elongated coiled sutures. Therefore, this composite structure can be fine-tuned to the proper tension for approximating the tissues. The surgeon can selectively apply energy to the suture in the composite structure under tension to cause a further tensioning, or, if that suture i also adapted to elongate, the application of energy will cause the structure to elongate. In still other embodiments, various sutures in the composite suture structure can each be fabricated sensitive to a separate wavelength. Accordingly, various sutures in the structure can be dimensionally altered and/or ablated to achieve the desired suture tension. Therefore, by fabricating sutures having different abilities to shrink and/or elongate, and fabricating each suture to be sensitive to a different wavelength, each suture in the composite structure can be selectively altered to achieve the desired tension for the entire composite. In such a structure, some of the suture elements may be under tension and others may be under compression. By selectively altering the dimensions of each suture element, an approximately uniform tensioning of the entire suture structure can be achieved. These composite structures may have absorbable sutures, non-absorbable sutures, or combinations thereof. For example, the heating of collagen in an aqueous environment is known to result in gelation (i.e., a reduction in strength) of the collagen. Additionally, the temperature at which gelation occurs is related to the degree of cross- linking in the collagen fiber. Thus, for example, a highly cross-linked collagen fiber can be tightly coiled around a lightly cross-linked collagen fiber to provide a composite suture. (In this case, the cross-linking effect is similar o the effect that cross-linking has on increasing the crystalline melt temperature of a non-absorbable polymer suture.) After implantation in a aqueous environment, or during irrigation of the implanted suture, energy can be selectively applied to degrade the lightly cross-linked suture; the highly cross-linked suture will remain unaffected and will uncoil, thereby uncoiling and reducing the tension exerted on the approximated tissues by the composite suture structure. Alternatively, a suture element of highly cross-linked collagen can be coiled and then formulated into a casing or shell of lightly cross-linked collagen. Thereafter, heatin the lightly cross-linked collagen will render it gelatinous and more viscous, thereby allowing the coiled collagen to unravel and effectively elongating the suture. Upon cooling, the more viscous lightly cross-linked collagen would become less viscous and harder, and the suture would thereafter be fixed at its new length. Other polymer/polymer combinations employing a similar technique can be envisioned. By combining one or more sutures having selectively alterable dimensions, a composite suture can be provided that is selectively adjustable. Such a composite structure may also include a suture that releases a pharmaceutical agent upon ablation. These composite sutures need not include a dimensionally alterable suture of the type described herein; rather, solely conventional sutures may be used. For example, a conventional suture may be provided with an energy absorbing substance and be used as a central core around which another conventional suture is coiled. In suc an embodiment, the surgeon can selectively apply energy to the implanted composite suture to lyse only the core, whereupon the coiled suture will uncoil and effectively elongate the implanted suture. While such an embodiment ma not be preferred in various situations because a shrinkable suture is not an element of the structure, such a composite structure is nevertheless beneficial. It is most preferred that the sutures of the present invention be packaged in materials that are resistant to energy input that would alter the dimensions of the fiber prematurely. Thus, preferred materials are those which are resistant or impermeable to irradiation (photons, including UV and/or IR) , heat, microwaves, and other forms of radiation useful for effecting a size change in the suture; exemplary materials include aluminum and Mylar. The diameter of the suture may vary along the axial length of the fiber. Needles for sutures may be swaged to one end of the monofilament, braided, twisted, or porous suture suture so obtained. Alternatively, the suture may be packaged without a needle. The suture with or without the needle attached is then packaged in a suture pack, preferably one which is impermeable to photons in the visible and near infrared spectrum (such as aluminum) , and is sterilized for use as a surgical suture. Alternatively, the suture can be sterilized first and then packaged. Generally, gas sterilization or radiation sterilization are preferred to prevent shrinkage which would be associated with heat sterilization; of course, care must be taken with radiative sterilization to avoid premature size alteration or further cross-linking of the polymeric material. The foregoing embodiments and descriptions are meant t illustrate the invention and not to be limiting. Various modifications and additions may become apparent to the artisan upon a perusal of this specification, and such are intended to be within the scope and spirit of the invention as defined by the claims. The theoretical discussions relating polymer and fiber orientation, crystallization, an similar processing is for illustrative purposes only, and the invention is not constrained by the propriety of those theories.

Claims: WHAT IS CLAIMED IS: 1. A surgical suture comprising a polymeric material sensitive to non-frictional energy effective to change the dimensions of the suture in vivo . 2. The suture of Claim 1, wherein the polymeric material elongates and/or shortens upon the application of photon energy. 3. The suture of Claim 1, wherein the polymeric material elongates and/or shortens upon the application of thermal energy. 4. The suture of Claim 1, wherein the suture materia is selected from non-absorbable polymers. 5. The suture of Claim 4, wherein the non-absorbable polymer is cross-linked. 6. The suture of Claim 4, wherein the non-absorbable polymer is selected from the group consisting acrylic acid esters, polyamides, polyolefins, polyesters, copolymers thereof, and compatible mixtures thereof. 7. The suture of Claim 6, wherein the non-absorbable polymers are polyolefins, mixtures of polyolefins, or mixtures of polyolefins and another non-absorbable polymer. 8. The suture of Claim 1, wherein the polymeric material shortens in the axial dimension. 9. The suture of Claim 1 wherein the polymeric material elongates in the axial dimension. 10. The suture of Claim 1, wherein the polymeric material shortens and/or elongates in the axial dimension. 11. The suture of Claim 4, wherein the non-absorbabl polymeric material is a cross-linked polyolefin. 12. The suture of Claim 11 wherein the polyolefin is selected from the group consisting of polyethylene, polypropylene, poly(isoprεne) , and poly(tetrafluoroethylene) . 13. The suture of Claim 11, wherein the polyolefin is cross-linked polypropylene. 14. The suture of Claim 12, wherein the suture material is a combination of cross-linked polyethylene and polyvinyl acetate. 15. The suture of Claim 4, wherein the polymeric material is a crystallizable, non-absorbable polymer. 16. The suture of Claim 15, wherein the polymeric material is essentially amorphous. 17. The suture of Claim 15, wherein the polymeric material is cross-linked. 18. The suture of Claim 1, wherein the polymeric material is absorbable. 19. The suture of Claim 18, wherein the absorbable polymeric material is selected from the group consisting of collagen, amino acid polymers and copolymers, lactide and glycolide copolymers, polydioxanone, and catgut. 20. The suture of Claim 1, further comprising a pharmaceutical agent. 21. The suture of Claim 4, further comprising a pharmaceutical agent. 22. The suture of Claim 11, further comprising a pharmaceutical agent. 23. The suture of Claim 18, further comprising a pharmaceutical agent. 24. The suture of Claim 1, further comprising an energy absorbing substance selected from the group consisting of dyes, chromophores, and pigments. 25. The suture of Claim 4, further comprising an energy absorbing substance selected from the group consisting of dyes, chromophores, and pigments. 26. The suture of Claim 11, further comprising an energy absorbing substance selected from the group consisting of dyes, chromophores, and pigments. 27. The suture of Claim 18, further comprising an energy absorbing substance selected from the group consisting of dyes, chromophores, and pigments. 28. A method of treating tissues and prosthetic materials comprising: A. suturing the tissue or prosthetic material with a polymeric material adapted to undergo a change in dimension upon the application of at least one source of non-frictional energy to the polymeric material; and B. applying energy to the polymeric material sufficient to cause a change in dimension of said suture. 29. The method of Claim 28, wherein the polymeric material is a non-absorbable polymer. 30. The method of Claim 28, wherein the non-absorbabl polymer is cross-linked. 31. The method of Claim 28, wherein the polymeric material further comprises an energy absorbing substance selected from dyes, chromophores, and pigments. 32. The suture of Claim 1 in combination with a radiation resistant packaging material. 33. A surgical suture comprising an oriented, cross- linked, non-absorbable polymer. 34. A method for making a surgical suture comprisin the process steps: A. providing an essentially crystalline non- absorbable organic polymer fiber in a first configuration; B. cross-linking the polymer fiber; C. heating the polymer fiber to essentially its pre-cross-linked crystalline melt temperature to reduce the crystallinity; D. drawing the polymer fiber to a second configuration; and E. quenching the polymer fiber to essentially lock the fiber in said second configuration. 35. The process defined by Claim 34, further comprising an additional step A' of heating the fiber to reduce crystallinity performed subsequent to step A and prior to step B. 36. The process defined by Claim 35, further comprising an additional step A' ' of drawing the fiber performed subsequent to step A' and prior to step B. 37. A method for making a surgical suture comprising the process steps: A. providing an essentially amorphous non- absorbable organic polymer fiber; B. cross-linking the fiber of process step A; and C. drawing the fiber of process step B effective to produce a polymeric fiber in a geometry suitable for use as a dimensionally alterable suture. 38. A surgical suture comprising a cross-linked polymeric material adapted to shrink in vivo upon contact with a non-toxic solvent for the polymeric material when not cross-linked. 39. A composite surgical suture comprising at least two sutures, at least one of said sutures comprising of a polymeric material sensitive to a source of non-frictional energy effective to change the dimensions of the composite suture in vivo . 40. The composite suture of Claim 39, comprising at least two sutures comprised of said energy sensitive polymeric material, and each of said suture materials sensitive to sources of non-frictional energy having different wavelengths. 41. The composite suture of Claim 40, comprising at least two sutures selected from sutures adapted to shrink, sutures adapted to elongate, sutures adapted to shrink and/or elongate, and combinations thereof. 42. The composite suture of Claim 41, comprising at least two sutures adapted to shrink by different amounts. 43. The composite suture of Claim 41, comprising at least two sutures adapted to elongate by different amounts. 44. A drug delivery system comprising a suture-like structure impregnated with a pharmaceutical agent. 45. The system defined by Claim 44, wherein the suture-like structure includes a core-shell configuration having a pharmaceutical agent impregnated in said core and having a shell comprising a cross-linked polymer. 46. A composite surgical suture which comprises at least two sutures arranged in a configuration such that lysis of one of said sutures by the selective application of non-frictional energy is effective to elongate the suture in vivo . 47. A surgical suture comprising a polymeric material having dimensions which change in vivo in response to selective exposure of said polymeric material to at least one source of energy independent of mechanical distortion of said suture in vivo.

Inventors: EATON ALEXANDER M, L ESPERANCE FRANCIS A JR, PURUT LEMIL M, EATON, ALEXANDER, M., L'ESPERANCE, FRANCIS, A., JR., PURUT, LEMIL, M.
Applicants: EATON ALEXANDER M, ESPERANCE FRANCIS A JR L, PURUT LEMIL M, EATON, ALEXANDER, M., L'ESPERANCE, FRANCIS, A., JR., PURUT, LEMIL, M.
Application year: 1992
Main classification: A61B17
IPC codes: A61B17, A61F2, A61L17, D02G3