Abstract:
A tubular mesh implant is provided for fracture fixation. The implant has a rest length between first and second opposite ends, and a central opening defining a rest inner diameter. The diameter of the central opening is reducible over a bone by elongation of the implant and securable to maintain fracture reduction. A method of setting a fractured bone comprises providing the tubular implant having a rest length and a central opening defining a rest inner diameter, introducing the fractured bone through the central opening in the implant, elongating the implant and reducing the inner diameter about the fractured bone, and securing the first and second ends of the implant to the fractured bone.

Description:
BACKGROUND 
       [0001]    1. Field 
         [0002]    The present invention relates generally to the treatment of bone fractures and, more specifically, to implantable devices and methods of their use. 
         [0003]    2. State of the Art 
         [0004]    Traditionally, orthopedic surgeons have accepted nonoperative treatment as the standard of care for fractured clavicles, likely the result of earlier studies showing unsatisfactory outcomes with operative treatment. However, recent studies show significant risks with nonoperative treatment, including chronic pain, weakness, and a higher nonunion rate. Hill, J. M., et al. “Closed Treatment of Displaced Middle-Third Fractures of the Clavicle Gives Poor Results.”  Journal of Bone and Joint Surgery , May 1998: 537-539. In addition, poor operative results in the past may have been related more to the technique used than the concept of treating these fractures operatively. 
         [0005]    Bone screws and hardware used in clavicle fracture surgery may be relatively large and may cause postoperative pain. In addition, such hardware may cause stress shielding that limits transmission of compressive forces through the healed fracture. 
       SUMMARY 
       [0006]    According to a first aspect, a method is provided for setting a fractured bone that comprises providing a tubular implant having a rest length and a central opening defining a rest inner diameter, introducing the fractured bone through the central opening in the implant, elongating the implant and reducing the inner diameter of the implant about the fractured bone, and securing first and second ends of said implant to the fractured bone. 
         [0007]    According to one embodiment, the method includes providing an extensible tubular mesh implant having a rest diameter and a rest length. Unless otherwise specified below, the rest diameter refers to the inner diameter of the implant. The tubular mesh implant is constructed for radial and axial extension and compression. The method further includes introducing the first bone portion through a first end of the implant and introducing the second bone portion through a second end of the implant. Also, the method includes applying an axially directed force to the implant to adjust the diameter of the mesh implant from the rest diameter to a first diameter that is larger than the first and second bone portions. In addition, the method includes releasing the axially directed force on the implant with the first and second bones introduced into the implant, so that the implant applies compressive force to at least one of the first and second bone portions. 
         [0008]    The tubular implant is extensible and compressible in its axial and radial directions. More particularly, the tubular implant is constructed to change its diameter in response to a change in its axial length. In one embodiment, the diameter of the implant is reduced from an initial rest diameter in response to applying an axially tensile force to the implant in an axial direction along the length of the implant. The reduction in the diameter of the implant allows for an implant with a rest diameter that is larger than the diameter of the bone at the fracture site, so that the implant can be stretched axially over and along the length of the bone at the fracture site and reduced in diameter towards the outer surface of the bone. With the tensile load imparted to the implant and the implant stretched axially along the bone, the ends of the implant are secured to the bone on opposite sides of the fracture site so that the load is transferred to the fracture site to compress the bone about the fracture. 
         [0009]    In another embodiment, the inner diameter of the tubular implant is increased from an initial rest diameter in response to applying an axial compressive force to the implant. The implant is constructed so that its diameter decreases towards the initial rest diameter when the compressive force is released. In one embodiment, the initial rest diameter of the implant is smaller than opposing first and second bone portions at a fracture site. An axial compressive force is applied to the implant so that the diameter of the implant is increased from its initial rest diameter to a size that is greater than the diameter of the first and second bone portions so that the first and second bone portions can be introduced into the implant through respective first and second ends of the implant. The first bone portion may be secured to the first end of the implant. Once the first end of the implant is secured, the compressive force on the implant may be released to allow the compressed implant to expand axially and reduce in diameter over the second bone portion until the second end of the implant engages the outer surface of the second bone portion and applies radial compression to the second bone portion. The radial compression retains the second bone portion relative to the implant and, therefore, to the first bone portion. The second end of the implant may be secured to the second bone portion. 
         [0010]    It will be appreciated that the implant may engage the second portion of the bone at a compressed length with respect to its rest length. Therefore, the implant may have a tendency to continue to expand further axially toward the rest length even after the diameter of the implant has reduced onto the second bone portion, thereby tending to displace the second bone portion away from the first bone portion at the fracture site. To mitigate this tendency, an external compressive force may be applied to the first and second bone portions to compress the bone portions together while the axially compressive force on the implant is released and the radial compression is applied to the second bone portion by the implant. The external compressive force may be applied by a surgeon. The imparted external compressive force applied to the bone portions may be retained owing to the radial compression applied to the second bone portion by the implant that retains the first and second bone portions in contact with each other. In addition, a tensile load can be applied to the implant while the bone portions are under compression and while the implant is in the process of being secured to at least the same bone portion to facilitate deploying the implant over the bone. 
     
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         [0011]      FIG. 1A  is an isometric view of an embodiment of a mesh implant in accordance with an aspect of this disclosure. 
           [0012]      FIG. 1B  is an exploded view of a first end of the mesh implant shown in  FIG. 1A . 
           [0013]      FIG. 2A  is a side elevation view of the implant shown in  FIGS. 1A and 1B  extending along axis A-A. 
           [0014]      FIG. 2B  is a side elevation view of another embodiment of an implant in accordance with an aspect of this disclosure. 
           [0015]      FIG. 2C  is a side elevation view of another embodiment of an implant in accordance with an aspect of this disclosure. 
           [0016]      FIG. 2D  is a side elevation view of another embodiment of an implant in accordance with an aspect of this disclosure. 
           [0017]      FIG. 3A  is a view of the implant shown in  FIG. 1A  attached to a clamp. 
           [0018]      FIG. 3B  is a view of an alternate attachment arrangement between the implant and the clamp shown in  FIG. 3A . 
           [0019]      FIG. 3C  illustrates compressing the implant shown in  FIG. 3A  with the clamp. 
           [0020]      FIG. 3D  illustrates the compressed implant of  FIG. 3C  with portions of a fractured bone disposed in an interior of the implant. 
           [0021]      FIG. 3E  illustrates positioning of fasteners with respect to mounting features of the implant of  FIG. 3C . 
           [0022]      FIG. 3F  illustrates the fasteners of  FIG. 3E  introduced through the mounting features securing the implant to a first bone portion. 
           [0023]      FIG. 3G  illustrates the implant secured to the first bone portion and with the clamp of  FIG. 3C  released and detached from the implant. 
           [0024]      FIG. 3H  illustrates the implant secured to both the first bone portion and a second bone portion at respective ends of the implant. 
           [0025]      FIG. 3I  illustrates additional fasteners between the first and second ends of the implant that secure the implant to the first and second portions of the bone. 
           [0026]      FIG. 4  illustrates an embodiment of a workflow for reducing a bone fracture using an implant. 
           [0027]      FIG. 5  illustrates another embodiment of a workflow for reducing a bone fracture using an implant. 
           [0028]      FIG. 6  illustrates another embodiment of a workflow for reducing a bone fracture using an implant. 
           [0029]      FIG. 7A  is an isometric view of an embodiment of a mesh implant in accordance with an aspect of this disclosure. 
           [0030]      FIG. 7B  is an exploded view of a first end of the mesh implant shown in  FIG. 7A . 
           [0031]      FIG. 8  illustrates an embodiment of a workflow for reducing a bone fracture using the implant shown in  FIGS. 7A and 7B . 
           [0032]      FIG. 9  shows an embodiment of an inflatable device for applying compression to a tubular implant. 
           [0033]      FIG. 10A  shows a top elevation view of an embodiment of a clamp for applying compression to a tubular implant. 
           [0034]      FIG. 10B  shows a side elevation view of the clamp of  FIG. 10A . 
           [0035]      FIG. 10C  shows an isometric view of the clamp of  FIG. 10A  viewed from the side and top. 
           [0036]      FIG. 10D  shows another side elevation view of the clamp of  FIG. 10A  from a view rotated ninety degrees about axis B-B with respect to  FIG. 10B . 
       
    
    
     DETAILED DESCRIPTION 
       [0037]      FIGS. 1A and 1B  show an embodiment of a mesh implant  100  in accordance with an aspect of the present disclosure. In  FIGS. 1A and 1B , the implant  100  is shown in what is termed a “rest state”, which will be described in greater detail below. The implant  100  is generally formed as a cylindrical tube, a wall  102  of which is preferably formed of a mesh. The wall  102  of the implant  100  defines an interior space  104  in which a first portion  150  and a second portion  152  of a fractured bone  156  ( FIG. 3D ) are disposed to limit relative movement between the first and second bone portions at a fracture site  156  as the bone  154  heals. To dispose such bone portions  150 ,  152  in the interior  104  of the implant, the implant  100  has first and second open ends  140 ,  142 , which are constructed to receive the respective bone portions  150 ,  152 , as described in greater detail hereinbelow. 
         [0038]    More specifically, the implant  100  is constructed to attach to the bone portions  150 ,  152  when they are disposed in the interior  104  of the implant  100  to provide rigidity and stability to the bone  154  specifically at the fracture site  156  in order to maintain reduction of the fracture and promote healing. The tubular shape of the implant attached to the outer side of the bone acts to change the moment of inertia of the bone to provide increased strain relief to the bone and resistance to bending and torsion loads during healing. 
         [0039]    The implant may be provided with one or more mounting features for securing the implant to the first and second bone portions. For example, as shown in the embodiment shown in  FIG. 1B , three screw fixation loops  118  are provided at each of the first and second ends  140 ,  142  of the implant  100 . The screw fixation loops  118  receive bone screws (not shown, e.g.,  FIG. 3E ) therethrough to fix the respective ends  140 ,  142  of the implant  100  to a bone (e.g., clavicle bone  154 ,  FIG. 3D ). In addition to the designated screw loops  118  shown in  FIG. 1B , screws may be inserted through the mesh wall  102  or other designated openings at positions on the mesh wall  102  between the ends  140 ,  142  of the implant  100 . 
         [0040]    As shown in greater detail in  FIG. 2A , the mesh wall  102  of implant  100  has a plurality of crossing, helical struts  110  that extend at opposing angles with respect to a longitudinal axis A-A. The struts  110  intersect and define open cells  112 , which in  FIG. 2A  are diamond shaped. In one embodiment, the included angle θ between the intersecting struts  110  in the rest state is less than ninety (90) degrees. In  FIG. 2A , the cells  112  are regularly spaced longitudinally and circumferentially along the wall  102  of the implant  100 . 
         [0041]    The number of cells  112  arranged longitudinally along axis A-A may vary based on the length of the implant  100  between its ends  106 ,  108  and the strain rate that is desired for the implant  100 . For example, a greater number of cells may provide a greater resistance to deformation (smaller strain rate) of the implant when subject to the same loads as an implant with relatively fewer cells. 
         [0042]    The struts  110  may be formed having cross sections of various shapes. In one embodiment, the cross sections may be square and may have length and width dimensions of about 0.01 inch. In another embodiment, the cross section of the struts  110  may be rounded. For example, the cross section of the struts  110  may be circular and may have a diameter of about 0.01 inch. Other cross sectional shapes of the struts are possible as well without departing from the spirit and scope of the invention. 
         [0043]    In other embodiments of an implant, the implant may have a mesh wall with struts that define open cells of a different size than shown above. For example,  FIG. 2B  shows an embodiment of an implant  200  that has struts  210  that define an open cells  214 . Specifically, a wall  202  of implant  200  has struts  210  that define equal sized diamond shaped cells  214  arranged circumferentially between first and second ends  206 ,  208  of the implant  200 . 
         [0044]    Referring to  FIG. 2D , the intersections of the struts  210 ″ can be formed as a living hinges  220 ″ that reduce the strain on the stent as the struts bend relative to each other when the implant  200 ″ reconfigures from the rest state to a modified diameter. The hinges  220 ″ shown are in the form of a rounded or curved hinge. Other shapes may be provided. Such hinges  220 ″ may be provided to any of the implants described herein. 
         [0045]    Also, in yet another embodiment of an implant  200 ′ shown in  FIG. 2C , the implant  200 ′ has a mesh wall  202 ′ that includes struts  210 ′ that define equal sized diamond shaped cells  212 ′ arranged circumferentially at the first and second ends  206 ′,  208 ′ of the implant  200 ′ and are spaced between longitudinally extending struts  216 ′ connecting to struts  210 ′. The longitudinally extending struts  216 ′ extend parallel to each other and to the longitudinal axis A-A through the implant  200 ′. 
         [0046]    In one embodiment, the mesh wall (e.g.,  102 ,  202 ,  202 ′) of the implant (e.g.,  100 ,  200 ,  200 ′) is laser cut, such as from a unitary metal tube and may be heat-treated to have a shape-memory or may be super-elastic. The metal tube may be formed of a nickel-titanium alloy that is biocompatible, such as Nitinol. The mesh wall (e.g.,  102 ,  202 ,  202 ′) may be axially and radially elastic relative to the aforementioned rest state in which the implant is not externally loaded with tensile or compressive forces. The mesh wall (e.g.,  102 ,  202 ,  202 ′) may be constructed to recoil or otherwise return to the rest state after being axially or radially extended or compressed. For example, the mesh wall (e.g.,  102 ,  202 ,  202 ′) may be constructed so that axial compression of the implant (e.g.,  100 ,  200 ,  200 ′), caused by an axial compressive load applied to the implant, will impart an increase in hoop stress and strain and cause radial expansion of the implant. With respect to implant  100 , for example, as the implant  100  radially expands, the angle θ increases. 
         [0047]    Also, the mesh wall may be constructed so that axial extension of the implant, caused by an axial tensile load applied to the implant, will reduce hoop stress and strain in the implant and cause radial contraction of the implant. With respect to the implant  100 , for example, as the implant  100  axially expands, the angle θ decreases. Thus, the implant can be constructed so that the radial dimension and the axial dimension will change simultaneously, but in opposite relation. 
         [0048]    The workflow for using an implant to reduce a bone fracture may be based on the configuration of the implant in its rest state. For example,  FIG. 3A  shows an embodiment of an implant  300  whose inner diameter can be increased from its rest state by axially compressing the implant  300  using a clamp  302 . The clamp  302  has hooks  304  that may be attached to the implant  302  through openings  306  in a mesh wall  308  or in specifically designated pockets (recesses) ( 310 ,  FIG. 3B ) that extend from the mesh wall  308 . Such pockets  310  may be useful to dispose the hooks  304  of the clamp  302  outside of the interior  312  of the implant  300  to provide increased clearance for disposing bone portions in the interior of the implant  300 . The clamp  302  may be squeezed to compress the implant  300  to thereby cause the inner diameter of the implant  300  to increase. The inner diameter may be increased to accommodate receiving a bone portion in the interior  312  of the implant  300  that has a diameter that is larger than the rest diameter of the implant  300 . The clamp  302  has interlocking teeth  314  that can be engaged to retain the clamp  302  and the implant  300  in a compressed state. The interlocking teeth can be disengaged to release the clamp  302  to allow the implant  300  to expand axially while contracting radially, toward the rest state, over bone portions disposed in the interior  312  of the implant  300 . If the outer diameter of the bone portions in the interior  312  of the implant is large enough, the implant  300  may engage and lodge itself against the outer surface of the bone portions as the implant recoils, thereby imparting a hoop stress in the implant  300  and a radially directed force to the bone portion. The implant  300  may be attached, such as with fasteners (e.g., bone screws), to bone portions disposed in the interior  312  of the implant  300 . In at least one embodiment, in addition to being compressed to accommodate receiving bone portions into the interior  312  of the implant  300 , the implant  300  may be stretched axially beyond its rest length prior to being attached to the bone portions to impart an additional compressive load onto the bone portions and across the fracture to facilitate maintaining reduction of the bone fracture. 
         [0049]    Also,  FIG. 7A  shows an embodiment of an implant  700  whose inner diameter can be decreased from its rest state by axially stretching the implant  700  using a clamp  702 . The clamp  702  has hooks  704  that may be attached to the implant  700  through openings  706  in a mesh wall  708  or in specifically designated pockets  710  that extend from the mesh wall  708 . The pockets  710  may be useful to dispose the hooks  704  of the clamp  702  outside the interior of the implant to provide increased clearance for disposing bone portions in the interior  712  of the implant  700 . The clamp  702  is squeezed to increase the distance between the hooks  704  so as to axially stretch the implant  700  to cause the inner diameter to contract. The inner diameter may contract so that the mesh wall  708  interferes with a bone portion disposed in the interior  712  of the implant  700  that has an outer diameter that is smaller than the rest diameter of the implant  700 . While the implant is in an at-rest state with a larger diameter, two broken bone portions (e.g.,  150 ,  154 ,  FIG. 3D ) may be received through respective opposite ends  716 ,  718  of the implant  700 . The implant  700  is then axially stretched and attached to those bone portions (e.g.,  150 ,  154 ,  FIG. 3D ), such as with fasteners (e.g., bone screws), to set the implant  700  with respect to those bone portions. The clamp  702  can be subsequently released and detached from the implant  700  to allow the implant to recoil and transfer the imparted tensile load to the bone portions attached to the implant to impart a compressive load to those bone portions to reduce the fracture. 
         [0050]    The implants described herein may be sized according to their rest diameter. Since each implant can be adjusted in diameter and length from its rest diameter, each size of implant may correspond a range of bone diameters that can be accommodated by the respective size of implant. For example, for use on a clavicle bone, an implant designated as a “small” implant may have a 0.256 inch inner diameter in its rest state and may be used to accommodate bones having a diameter of 0.256 to 0.375 inch. Also, an implant designated as a “medium” implant may have a 0.375 inch inner diameter in its rest state and may be used to accommodate bones having a diameter of 0.375 to 0.492 inch. In addition, an implant designated as a “large” implant may have a 0.492 inch inner diameter in its rest state and may be used to accommodate bones having a diameter of 0.492 to 0.614 inch. 
         [0051]      FIG. 4  illustrates a workflow of using the embodiment of the implant shown in  FIG. 3A  to reduce a fracture of a clavicle bone. At block  401 , the implant  300 , in its rest state, is attached to the clamp  302 , as shown in  FIG. 3A . At block  403 , the clamp  302  is squeezed to compress the implant  300 , as shown in  FIG. 3C . The compression of the implant  300  increases its inner diameter. The implant  300  is compressed at least until the inner diameter of the interior  312  is at least large enough to accommodate the ends of the portions  150 ,  152  of the broken clavicle bone  154  at the fracture site  156 , as shown in  FIG. 3D . At block  405 , the right portion  150  of the broken clavicle  154  is introduced into the interior  312  of the implant  300  through an open first end  350  of the implant  300  and the left portion  152  of the broken clavicle  154  is introduced into the interior of the implant  300  through an open second end  352  of the implant  300 , as shown in  FIG. 3D . At block  407 , the right portion  150  of the broken clavicle  154  is secured to the implant  300  using screws  316  that are inserted through loops  318  of the implant  300 , as shown in  FIGS. 3E and 3F . At block  409 , the clamp  302  is released to allow the implant  300  to stretch back towards its rest state. As the implant  300  stretches axially, the inner diameter of the interior of the implant  300  contracts. The implant  300  may stretch back to its rest length if its inside diameter does not interfere with the outside of the left portion  152  of the fractured bone  154 . Otherwise, the implant  300  stretches towards its rest length until its inner diameter contracts to a position on the left bone portion  152  where it begins to radially compress against the outside of the left bone portion  152 , at which point the implant  300  stops stretching. After the second end  352  of the implant  300  stretches as far as it can, as shown in  FIG. 3G , at block  411  the second end  352  is secured to the left portion  152  of the fractured clavicle bone  154  with bone screws  316 , as shown in  FIG. 3H . Optionally, additional bone screws  316  can be inserted through the implant  300  to secure the implant  300  to the portions  150 ,  152  of the bone  154  at positions between the first and second ends  350 ,  352  of the implant  300 , as shown in  FIG. 3I . 
         [0052]      FIG. 5  shows an alternate workflow to that detailed in  FIG. 4 . Blocks  501  to  509  correspond to blocks  301  to  309  of the workflow shown in  FIG. 3 . However, in contrast to the workflow of  FIG. 4 , in the workflow of  FIG. 5 , after the clamp  302  is released at block  509  and the implant  300  is allowed to elongate back toward its rest state, a second clamp  702  ( FIG. 7 ) is attached to the implant  300  at block  511  and the implant  300  is stretched axially beyond its rest length at block  513  prior to the implant  300  being secured to the left portion  152  of the broken clavicle bone  154  at block  515 . Then, the second clamp  702  is released from the implant  300  at block  517 . The additional stretching of the implant  300  beyond the rest length imparts a tensile load to the implant  300 . When the implant  300  is secured to the bone portions  150 ,  152  while it is under tension, the implant  300  transfers the tensile load to the bone portions  150 ,  152  so that a compressive load is imparted to the bone portions  150 ,  152  to maintain reduction of the fracture at fracture site  156 . 
         [0053]      FIG. 6  shows an alternate workflow to that detailed in  FIG. 5 . Unlike the workflow of  FIG. 5 , in the workflow of  FIG. 6 , the implant  300  is secured to both portions  150 ,  152  of the fractured bone  154  only after the implant  300  is stretched beyond its rest length and is positioned across the fracture site  156 , as discussed in greater detail below. At block  601  a first clamp  302  is attached to the implant  300 . At block  603  the implant  300  is compressed. At block  605  the right and left portions ( 150 ,  152 ) of the broken clavicle bone  154  are introduced into the interior  312  of the implant  300  through the first and second ends  350 ,  352  of the implant  300 . At block  607  the first clamp  302  is released so that the implant  300  can stretch on its own along the portions  150 ,  152  of the bone  154 . At block  609  a second clamp  702  ( FIG. 7 ) is attached to the implant  300  and at block  611  the implant  300  is stretched beyond its rest length to impart a tensile load to the implant  300 . At block  613  the stretched implant  300  is positioned across the fracture site  156 . For example, in one embodiment, the stretched implant  300  is centered over the fracture site  156 . At block  615  the implant  156  is secured to the fractured portions  150 ,  152  of the bone  154 . At block  617  the second clamp  702  is released from the implant  300 . 
         [0054]      FIG. 8  illustrates a workflow of using the implant  700  shown in  FIG. 7A  to maintain reduction of a fracture of the clavicle bone  154 . At block  801 , the implant  700 , in its rest state, is attached to the clamp  702 . At block  803 , the right portion  150  of the broken clavicle  154  is introduced into the interior  712  of the implant  700  through the open first end  750  of the implant  700  and the left portion  152  of the broken clavicle  154  is introduced into the interior  712  of the implant  700  through the open second end  752  of the implant  700 . At block  805 , the implant  700  is stretched beyond its rest length. At block  807  the implant  700  is positioned over the fracture site  156 . For example, the stretched implant  700  may be centered over the fracture site  156 . At block  809  the implant  700  is secured to the right and left portions  150 ,  152  of the fractured clavicle bone  154 . At block  811  the clamp  702  is released from the implant  700 . The additional stretching of the implant  700  beyond the rest length imparts a tensile load to the implant  700 . When the implant  700  is secured to the bone portions  150 ,  152 , the implant transfers the tensile load to the bone portions  150 ,  152  so that a compressive load is imparted to those bone portions to promote reduction of the fracture. 
         [0055]    The clamps  302 ,  702  shown respectively in  FIGS. 3A and 7  are shown as attaching to discrete points on one side of axis A-A of the implants  300  and  700 . Owing to such exemplary illustrated attachments, the tensile and axial forces applied are offset from the central axis A-A of the implant, such that those forces tend to impart a bending moment on the implant. To mitigate the tendency of the implants  300  and  700  to bend or buckle, alternate clamping arrangements are possible that more uniformly apply tensile and compressive forces to the implants. For example, a sleeve, ring, or balloon may used around the circumference of the implants to more uniformly apply axial tension and/or radial compression to the implants.  FIG. 9  shows a device  900 , which is similar to a miniature blood pressure cuff, has an inflatable cuff  902  that is used to wrap around and compress the implant by inflating the cuff  902  with a squeeze bulb  904 . Also,  FIGS. 10A to 10D  shows a modified clamp  1000  that may be used to compress the implant radially. The clamp  1000  includes arms that are joined together at respective first ends  1004 . Both arms  10002  have elongated claws  1006  at respective second ends  1008 . The claws each have a curved profile that is constructed to wrap around the outside of an implant. In one embodiment, the claws  1006  have semi-circular profiles, which when compressed against the outside of the implant, apply a radially compressive force to the implant. The claws  1006  define openings  1010  through which bone screws may be introduced to secure the implant to the bones, as described hereinabove. 
         [0056]    There have been described and illustrated herein several embodiments of an implant and a method of using the implant to reduce a bone fracture. While particular embodiments of the invention have been described, it is not intended that the invention be limited thereto, as it is intended that the invention be as broad in scope as the art will allow and that the specification be read likewise. Thus, while particular arrangements of the implant and a mesh have been disclosed, it will be appreciated that other arrangements are possible as well. For example, while the implant has been described in at least one embodiment as including a tubular mesh that may be lasercut, in at least one other embodiment, the implant may include a memory metal braid. In addition, while particular types of metals are used for forming the implant have been disclosed, it will be understood that non-metal materials and alloys of metals can be used. For example, and not by way of limitation, stainless steel. Furthermore, while certain procedures of a workflow have been described in an example sequence, it will be understood that the procedures may be combined or performed in a different sequence. It will therefore be appreciated by those skilled in the art that yet other modifications could be made to the provided invention without deviating from its spirit and scope as claimed.