novel intramedullary bone stents : intravascular stents are commonly used in arteries to hold the artery open , e . g ., to treat stenosis caused by a buildup of plaque on the walls of the artery . thus , these intravascular stents are designed to maintain patency of the blood vessel . intravascular stents are inserted into the artery in a crimped state and expanded to a larger diameter . see , for example , fig1 , which shows expanding stents used in blood vessels . to date , stents have not been used in orthopedic applications to reduce a fracture site . in accordance with the present invention , and looking now at fig1 , there is shown an intramedullary bone stent 5 . intramedullary bone stent 5 is placed into the intramedullary canal 10 of a bone 15 , bridging the fracture 20 . as the intramedullary bone stent 5 expands , applying hoop stress to the bone 15 , the intramedullary bone stent 5 shortens , reducing the fracture 20 and rigidly holding the bone 15 in the correct position . in one preferred form of the invention , the intramedullary bone stent 5 is formed out of a shape memory alloy ( sma ). an intramedullary bone stent 5 can be superior to current fixation methods because the intramedullary bone stent 5 can have a modulus of elasticity closer to that of bone , does not create regions of stress shielding , and does not impair blood flow at the fracture site . additionally , intramedullary bone stents 5 may be beneficial in treating pediatric patients with open growth plates , where nails , rods , and screws may interfere with bone development at the growth plate . shape memory material ( e . g ., nitinol ) stent : from its earliest use in orthodontic arch wires to its more - recent dominant role in cardiovascular implants such as intravascular stents , endografts , and filters , shape memory materials ( e . g ., nitinol , titanium - niobium , and shape memory polymers ) all possess unique properties that have made it the material of choice for a variety of medical applications . the vast majority of medical applications take advantage of nitinol &# 39 ; s ( niti &# 39 ; s ) unusual superelastic properties . more particularly , while conventional engineering materials typically have an elastic limit much less than 1 % strain , nitinol can experience fully recoverable strains up to 8 %. see fig1 , which shows the stress - strain properties of nitinol , with comparison being made to various materials . this superelastic capability allows a properly designed nitinol component to radically transform its shape during service , fueling the trend toward minimally invasive procedures . for example , a nitinol intravascular stent may be designed to be delivered through a 2 - mm sheath and expand to support a 10 - mm vessel . similarly , an endoscopic instrument may be delivered through a 15 - mm opening , expand to 60 mm to retrieve a specimen , and then collapse to exit through a similarly sized port . in short , if a medical component must be delivered in a compressed state and then become an expanded shape , nitinol is likely to offer design advantages unavailable with other materials . today there are a wide range of intravascular prostheses on the market for use in the treatment of aneurysms , stenosis , and other vascular irregularities . balloon expandable ( i . e ., non - nitinol ) and self - expanding intravascular stents ( i . e ., nitinol ) are well known for restoring patency in a stenosed vessel , e . g ., after an angioplasty procedure , and the myriad usages of coils and stents are known techniques for treating aneurysms . the biocompatibility of nitinol has been well documented . in nitinol , nickel and titanium are distributed in a regular crystal lattice order , exhibiting high atomic bonding forces with mixed covalent and metallic character , thus it is difficult for nickel to leave the bulk material . the surface of niti is well passivated because titanium is more readily oxidized than nickel . niti devices exhibit a ti - based oxide layer which is responsible for the corrosion resistance of this material and acts as an effective barrier to nickel ion release . from a biological point of view , the integrity of the outermost surface layer and its ability to repassivate are crucial importance for the biocompatibility of niti . self - expanding intravascular stents generally are retained in a contracted delivery configuration using a sheath , then the nitinol intravascular stent self - expands when the sheath is retracted . such niti stents commonly have a major drawback in intravascular applications , for example , the intravascular stents may experience large length shrinkage during radial expansion ( referred to as “ foreshortening ”) and may shift within the blood vessel prior to engaging the blood vessel wall , resulting in improper placement . the reason that intravascular stents become shorter during radial expansion is because the angles of the struts within the intravascular stents increase ( from parallel to the centerline of the stent to an angle of 15 °- 60 ° to the centerline of the stent ) when the intravascular stents expand radially , thereby shortening the length of the intravascular stents . in other words , the intravascular stent is made of a series of “ zs ”, and when the intravascular stent is collapsed , the “ z &# 39 ; s ” are flat and look more like dashes . during radial expansion of the intravascular stent , the dashes open to z &# 39 ; s , shortening the intravascular stent . see fig1 , which shows the radial expansion of a nitinol intravascular stent . foreshortening is explained in terms of a deformation in longitudinal direction after expansion of the stent . it is calculated as follows : as seen in the cp stent ™ foreshortening chart shown in fig1 , foreshortening is a consequence of the radial expansion of the intravascular stent . the success of vascular stents in the restoration of blood flow is limited by restenosis . recent data generated from computational fluid dynamics ( cfd ) models suggest that the vascular geometry created by an implanted stent causes local alterations in wall shear stress ( wss ) that are associated with neointimal hyperplasia ( nh ). foreshortening is a potential limitation of intravascular stent design that may affect intravascular stent performance and the rate of restenosis . the angle created between axially aligned stent struts and the principal direction of blood flow varies with the degree to which the intravascular stent foreshortens after implantation . progressive degrees of intravascular stent foreshortening are also associated with strut misalignment relative to the direction of blood flow as indicated by analysis of near - wall velocity vectors , suggesting that foreshortening may predispose the stented vessel to a higher risk of neointimal hyperplasia . additionally , during foreshortening , there can be unfavorable shearing between the stent struts and the vascular wall , potentially causing hemorrhaging . there are dozens of metal and bioresorbable intravascular stent designs on the market today ( see http :// www . nitinol . com / media / reference - library / 009 . pdf ), and intravascular stent designers have been working to overcome the aforementioned foreshortening problem of intravascular stents for many years . see , for example , u . s . pat . no . 6 , 761 , 731 “ balloon - stent interaction to help reduce foreshortening ”. intramedullary bone stent : the present application relates generally to the provision and use of novel intramedullary bone stents to repair a bone fracture and facilitate bone fusion by the intramedullary stent &# 39 ; s radial expansion and axial compression during foreshortening . in one preferred form of the invention , the novel intramedullary bone stents are formed out of shape memory material ( e . g ., nitinol ). thus , in one preferred form of the invention , there is provided an osteosynthetic nitinol intramedullary bone stent implant for disposition within the intramedullary canal of a bone , whereby to span a fracture line , and effect fracture / fusion repair . the novel fracture repair devices , systems , and methods of the present invention also include those for repairing intentional fracture sites , such as but not limited to osteotomies created for reconstructive purposes . bony fusions of surgically resected joints throughout the body are also within the scope of the present invention . such nitinol intramedullary bone stent fracture fixation devices , systems and methods of the present invention help maintain compressive loads across the fracture site for longer periods of time compared to prior devices . the novel bone stent is an intramedullary device . more particularly , the medullary cavity ( medulla , innermost part ) is the central cavity of a bone shaft where red bone marrow and / or yellow bone marrow ( adipose tissue ) is stored ; hence , the medullary cavity is also known as the marrow cavity . located in the main shaft ( cortical bone ) of a long bone ( diaphysis ), the medullary cavity has walls composed of spongy bone ( cancellous bone ) and is lined with a thin , vascular membrane ( endosteum ). however , the medullary cavity is the area inside any bone ( long , flat , etc .) that holds the bone marrow . the clavicle is the only long bone that does not contain a medullary cavity . this area is involved in the formation of red blood cells and white blood cells . see fig1 , which shows the anatomy of the medullary cavity of the femur . the intramedullary bone stent , preferably made of shape memory materials such as nitinol , can be used to support , stabilize and reduce bone fractures ( see fig1 ). the benefits of an intramedullary bone stent appliance include : the intramedullary bone stent uniformly conforms to the intramedullary geometry and uniformly expands and locks , both axially and radially , along the length of the bone , which minimizes or eliminates interfragmentary motion . there is a widely held opinion that interfragmentary sliding ( shear ) motion is detrimental to the repair of bone fractures . in order for a fracture to heal , it needs stability and blood flow . blood brings the components for healing to the fracture site . these include oxygen , healing cells , and the body &# 39 ; s own substances necessary for healing ( e . g ., growth factors ). the blood supply to the injured bone usually comes back on its own during the healing period . the use of an intramedullary bone stent , without screw holes , compressive plates , or invasive nails , allows for a near normal blood supply to the fracture site by reducing or minimizing additional vascular damage . the sustained compressive therapy offered by the intramedullary bone stent can also be osteoinductive , due to its piezoelectric effects on osteoblasts themselves . the intramedullary bone stent is designed to apply compressive forces at the fracture site , by foreshortening and / or training the niti to pull the bone segments in compression . the intramedullary bone stent , however , is “ spring - like ”, and will oscillate and vibrate to some extent , causing mechanical loading to catalyze osteoblast , bone remodeling and fracture healing . in pediatrics , where it is often difficult to use an intramedullary device because of the concern of disrupting the growth plate , a fracture through the growth plate requires perfect reduction , and pinning may be necessary . rotational malalignment in the fingers is a frequent complication and can be easily detected after reduction by flexing all the fingers together . fingers should be immobilized by syndactylization , or “ neighbor strapping ”, with the adjacent finger for a maximum of three weeks . a short forearm cast with an aluminum splint is another alternative . physical therapy might be necessary . in the younger child , more durable immobilization should be used to prevent the child from removing it . open reduction for phalangeal fractures is required for displaced intra - articular fractures and oblique , shortened midshaft fractures . niti intramedullary bone stents can traverse the growth plate with a collapsed intramedullary bone stent diameter comparable to the size of a large needle , minimizing damage to the growth plates . now , using an intramedullary bone stent , the intramedullary fixation becomes feasible in children for the first time . when a conventional bone fracture compression plate made of high modulus 316l stainless steel ( 200 gpa ) relative to cortical bone ( 15 gpa ) is used , this results in stress - shielding the bone under the plate and is believed to cause osteoporosis that weakens the bone under the plate . relieving the bone from carrying a load over an extended period of time is believed to contribute to the development of this type of osteoporosis , also known as osteopenia . when the plate and screws are removed from the healed bone , the bone may re - fracture due to the weakening which resulted from the development of osteoporosis or osteopenia . unlike 316 - l stainless steel and titanium ( ti 6al - 4v ), nitinol has a very similar elastic modulus compared to bone , in the range of 5 gpa to about 70 gpa . the niti intramedullary bone stent material will more naturally load the fracture site because it has a stiffness close to human tissue so that stress shielding does not occur which is a problem with stiff plates and im nails . see fig1 , which is a chart showing the measure of the stiffness or modulus of elasticity of various materials . in addition to niti having a similar modulus of elasticity to bone , the intramedullary bone stent &# 39 ; s stiffness can be designed to have comparable stiffness to bone by changing the dimensions of the intramedullary bone stent , i . e ., strut thickness , strut width , strut angle and strut frequency . fig1 shows struts shaped like a “ z ” that can be used to make up the structure of an intramedullary bone stent of the present invention . thus , in accordance with the present invention , and looking now at fig1 , an intramedullary bone stent 5 is restrained in a radially - contracted , longitudinally expanded condition ( e . g ., within a sheath , not shown ), advanced down the intramedullary canal 10 of a bone 15 so as to span a fracture line 20 , and then the restraint of the intramedullary bone stent 5 is released , so that the intramedullary bone stent radially expands to grip the surrounding bone and longitudinally contracts so as to place the bone fragments in compression , whereby to facilitate healing of the fracture . preferably , intramedullary bone stent 5 is formed out of a shape memory material so that the intramedullary bone stent 5 has a modulus of elasticity similar to that of bone , whereby to minimize stress shielding and thereby enhance bone healing . unlike a conventional intramedullary nail , the force of the expanding ni — ti intramedullary bone stent can be engineered to apply enough radial force to stabilize the fracture yet be somewhat flexible in areas away from the fracture site . see fig1 and 20 , which show the strain and force characteristics for a simple beam of the type used in an intramedullary bone stent . in addition , the expanding radial hoop force can be engineered to overcome the collapse , buckling and / or pinching loads at and near the fracture site . see fig2 , which shows the calculations for the hoop and bending stiffness of an intramedullary bone stent . stent foreshortening to create dynamic interference fit with compressive loads against the fracture site : when an intravascular stent is deployed in an artery or vein , it radially expands and simultaneously shortens , which can cause the intravascular stent to undesirably tear the wall of the artery or vein as the intravascular stent foreshortens . thus , in vascular applications , foreshortening is problematic and undesirable — and much effort has gone into minimizing the negative effects of foreshortening . in the case of the present invention , where an intramedullary bone stent is provided , the struts of the intramedullary bone stent can intentionally be made with barbs or tangs so as to aggressively grip the surrounding bone tissue in order to pull the bone fragments on either side of the fracture together , effectively compressing the bone fracture when stent foreshortening takes place . see , for example , fig2 , which shows a nitinol intramedullary bone stent 5 having integral barbs 25 for gripping the inner wall of the host bone . thus , the present invention advantageously harnesses the foreshortening effect to provide desired compression . the tension applied by the shortening intramedullary bone stent to the bone may better maintain close apposition of the bone fragments , and better establish compression across the fusion zone , during the healing process . in this respect it will be appreciated that bones in contact with each other , and under compressive load , heal together faster than bones held apart . significantly , with the present invention , the novel shape memory alloy intramedullary bone stent is longitudinally stretched ( and radially contracted ) during the insertion procedure , e . g ., by loading the intramedullary bone stent within a constraining sheath . once the intramedullary bone stent is properly positioned within the intramedullary canal ( which is done manually , while being viewed via fluoroscopy ), the shape memory alloy intramedullary bone stent is released from its constraint so as to radially expand and longitudinally contract , whereby to engage the bone fragments on opposing sides of the fracture line and draw them together in compression . this action maintains the target fusion bones in close apposition . the niti intramedullary bone stent offers sustained compression for longer time periods than static , non - adaptive intramedullary devices . unlike plates and screws , the niti intramedullary bone stent will maintain compressive load across the fracture site well after the fracture is healed . the intramedullary bone stent will not compromise blood flow because holes in the bone are not created from screws and or staples , nor will they apply deleteriously localized stresses concentrations in small areas like bone staples and screws do . furthermore , because the intramedullary bone stent is contained wholly within the bone , the niti intramedullary bone stent will not cause tissue scaring like bone screws and staples do . the niti intramedullary bone stent of the present invention can create ample compressive forces on the bone tissue that can stimulate rapid bone regeneration in order to fill in deficient bone fractures or to fix an implant firmly within adjacent bone . to succeed , the niti intramedullary bone stent must be habitable , especially for bone - forming cells ( e . g ., osteoblasts ) such that they can colonize on the strut surfaces and synthesize new bone tissue . additionally , osseointegration is preferred in the spaces between the struts . for successful implants , sufficiently regenerated bone fills the gap between an implant and juxtaposed bone , thus the implant is attached firmly with the surrounding bone . frequently implant materials are not compatible with bone cell responsible for bone formation , but rather they promote the formation of undesirable soft connective tissue . fibrous soft tissue , as opposed to hard bony tissue , has been shown to improperly fix orthopedic implants into surrounding bone which leads to loosening under physiological loading conditions and eventual implant failure . the niti intramedullary bone stent offers surgeons the ability to eliminate traditional device performance issues that can negatively impact the ability to achieve a solid fusion . osteoblast response to mechanical strain : the mechanical environment of a fracture site has been known to play an important role in fracture healing and tissue differentiation for many years . appropriately applied mechanical conditions have been known to accelerate fracture healing and there are many mechanical properties that influence the healing process including strain rate , frequency , magnitude , number of cycles , and number of days of stimulation among others . the majority of investigations into the effects of the local mechanical environment on bone repair actively control the motion at the defect . these devices allow for a prescribed motion at set time points . normally , these devices are powered by an external actuator or through a sliding mechanism that allows a set motion to occur during normal ambulation , which is called dynamization . studies using this model have found that larger fracture gap sizes lead to poorer fracture healing and that gap size plays a significant role in the progression of repair . these studies also showed that small controlled movements in smaller gaps can increase bone formation , callus size and tensile strength . the disadvantages of this model are that the motion is limited to compressive strains and , over time , the motion will decrease as healing progresses and tissues progressively fill the defect , altering the experimental conditions . this same conclusion was drawn in studies applying a variety of different controlled micromotions at many different frequencies , as well as with applied axial dynamization . studies suggest that changing the mechanical environment in a healing fracture provides strong evidence that micromotion plays a vital role in fracture repair ; however , too large of interfragmentary motion disrupts fracture repair . some researchers believe that bone formation occurs in areas of low to moderate tensile strain , cartilage formation occurs under hydrostatic pressure , and fibrous tissue growth occurs in areas of moderate to high tensile strain . and some researchers have hypothesized that small strains and small hydrostatic pressures (& lt ;± 0 . 15 mpa ) lead to direct bone formation , compressive hydrostatic pressures above 0 . 15 mpa lead to chondrogenesis and therefore endochondral ossification , and all other stimuli lead to connective tissue or fibrocartilage formation . niti intramedullary bone stents can be designed to create both compressive and tensile force at the fracture site , being stiff to stabilize but just flexible enough to cause ample hydrostatic pressure (& lt ;± 0 . 15 mpa ) to create direct bone formation at the fracture site . types of stents : there are a number of different types of devices for stenting of body passages . these may be classified into two general categories : expandable meshes , which include self - expanding types and non - self - expanding types , and non - expandable meshes , which are typically made of plastic or polymeric material . the self - expanding meshes can be made of a material , such as nitinol , which changes configuration upon heating to body temperature , and exhibits superelastic behavior . other self - expanding meshes are made of resilient mesh material which can be flexed down into a small diameter tube and held in place in such a configuration until it is released , at which time it expands to a larger diameter configuration . the non - self - expanding meshes are expanded by use of an inflatable balloon which is placed inside the mesh in a small diameter configuration , and then inflated , thereby expanding the mesh to a larger diameter configuration . the balloon is then deflated for removal , leaving the mesh in its expanded configuration . both types of mesh constructs may be applied to the present invention . the expandable mesh intramedullary bone stents can be made from a variety of materials , e . g ., stainless steel . the expandable mesh intramedullary bone stents can be made in a variety of configurations such as a coiled spring , a variety of zig - zag patterns ( including various stents known as “ z ” stents ), braided filament , and other collapsible configurations that can have external barbs and / or hooks to help grip the bone tissue . the struts of the intramedullary bone stents can have ribs or teeth to help dig into the bone during axial compression or shortening of stent to help compress the fracture together . see fig2 , which shows examples of different stent designs . one type of expandable stent comprises a cylindrical member having a slit cut along its length , so that the edges along the length can overlap to allow for compression to a reduced size . a further configuration which may be described as a perforated tube which comprises a generally rigid tube with openings cut therein to allow for radial expansion under force of an expansion balloon or by expansion due to heating . the expandable mesh stents can be braided , woven , knitted , formed , molded , machined or made by other methods known in the art . various mesh designs are disclosed , for example , in u . s . pat . nos . 4 , 512 , 338 , 4 , 503 , 569 , 4 , 922 , 905 , 4 , 733 , 665 , 4 , 950 , 227 , 5 , 089 , 006 and 5 , 061 , 275 . other materials , configurations and methods of manufacture in addition to those described above are known . as used herein , the term “ expandable mesh ” is meant to include , without limitation , self - expanding and non - self - expanding configurations made of any generally rigid or springy material which , when expanded , have an open network or arrangement which would otherwise allow for tissue in - growth , and would not otherwise prevent fluid flow through its walls . several of these prior art mesh stents have been utilized with a polymeric sheath or cover ; however , since these sheaths must be stretched to increase in size , they exert a force that resists expansion , which tends to limit the final expanded size of the mesh . additionally , this resistance may make expansion more problematic . alternatively , the sheath may be folded or bundled over the mesh when it is compressed , so that no force is exerted upon expansion . shape memory alloy ( sma ) stents conform to different shapes of intramedullary canals : the proximal and middle phalanges from 83 pipjs were analyzed set in clear plastic , sectioned in the transverse plane , and measured ( ash and unsworth 1997 ). the medullary canals were marked on the sagittal and frontal planes and shadowgraphs of the intact bones analyzed . it was found that the phalangeal shaft bone was thicker laterally than dorsally and palmarly , and thicker dorsally than palmarly for the proximal and middle phalanges throughout the length the hand and wrist . the shape and size of the transverse cross - section of the medullary canal changed throughout the length of the shaft . the centerline of the medullary canal coincided with the midline of the bone in the frontal plane and was approximately a straight line along the length of the canal . in the sagittal plane it was slightly palmar to the midline , and the angle between the centerline and the baseline of the bone changed along the length of the canal . see fig2 , which shows the medullary canal of a bone in side view , and fig2 , which shows transverse cross - section of phalangeal bones . the problem with using a machined round pin and / or nail to stabilize the fracture is that the round and straight pin or nail will not conform evenly to the bend and change of bore shape in the medullary canal . significantly , the flexible sma intramedullary bone stent of the present invention will conform to the varying geometries of the intramedullary canal . the flexible sma intramedullary bone stent will radially expand until a certain pressure stops the expansion , which allows the intramedullary bone stent to conform to the specific geometry of the intramedullary canal in terms of straightness and roundness . also , if the phalangeal shaft bone is thicker in one area vs . the other area , the sma intramedullary bone stent can be designed to expand more in the thicker section vs . the thinner bone section to allow for uniform strain on the bone tissue . zw stent — radial expansion and axial compression : today many intravascular stents are introduced while held inside a polymer sheath . when the sheath is retracted , the intravascular stents expand . if the intravascular stent is nitinol , it expands superelastically . if the intravascular stent is stainless steel it is expanded with a balloon . either way , when the sheath is pulled away , the intravascular stent radially expands against the artery . as the sheath is incrementally removed , the expanding intravascular stent applies pressure to the artery . this pressure helps to hold the intravascular stent in place while the sheath is further pulled away , which leaves the more radially expanded exposed stent behind . see the images a , b , c in fig2 . in accordance with one preferred form of the present invention , an intramedullary bone stent can be engineered to incrementally expand radially when the sheath is removed and then pull in compression . for example , and looking now at fig2 , there is shown an intramedullary bone stent 30 which has the conventional “ z ” struts 35 that expand radially and , adjacent to the “ z ” struts 35 , there can be “ w ” struts 40 which are normal to the “ z ” s . the z struts 35 radially expand and the w struts 40 pull in compression . so , in addition to the traditional stent foreshortening effect which can be used to compress a fracture , the design of the intramedullary bone stent can be further enhanced so as to increase both radial expansion and longitudinal foreshortening . if desired , the intramedullary bone stent designs can have angular zigzags to help with torsional stability . so , the intramedullary bone stent could have z struts , w struts , and / or off center line zigzags to improve torsional stability . bone stents can be used in the phalanges , metacarpals , carpals , metatarsals , tarsals , humerus , radius , ulna , femur , tibia and fibula , among other bones . see fig2 , which shows various bones where bone stents may be efficacious for fracture fixation . it should be understood that many additional changes in the details , materials , steps and arrangements of parts , which have been herein described and illustrated in order to explain the nature of the present invention , may be made by those skilled in the art while still remaining within the principles and scope of the invention .